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INVESTIGATION OF SELECTED POTENTIAL ENVIRONMENTAL CONTAMINANTS: ASPHALT AND COAL TAR PITCH FINAL REPORT ENVIRONMENTAL PROTECTION AGENCY OFFICE OF TOXIC SUBSTANCES WASHINGTON, D.C. SEPTEMBER EPA/ INVESTIGATION OF SELECTED POTENTIAL ENVIRONMENTAL CONTAMINANTS: ASPHALT AND COAL TAR PITCH Ruth P. Trosset, Ph.D David Warshawsky, Ph.D. Constance Lee Menefee, B.S. Eula Binghara, Ph.D. Department of Environmental Health College of Medicine University of Cincinnati Cincinnati, Ohio Contract No.: Final Report September, Project Officer: Elbert L. Dage Prepared for Office of Toxic Substances U.S. Environmental Protection Agency Washington, D. C. Document is available to the public through the National Technical Information Service, Springfield, Virginia NOTICE This report has been reviewed by the Office of Toxic Substances, Environmental Protection Agency, and approved for publication. Approval does not signify that the contents neces- sarily reflect the views and policies of the Environmental Pro- tection Agency, nor does mention of trade names or commercial products constitute endorsement or recommendation for use. - 1 - TABLE OF CONTENTS Executive Summary Introduction Glossary 6 I. PHYSICAL AND CHEMICAL PROPERTIES 8 A. Bituminous Materials 8 B. Asphaltic Materials 11 1. Petroleum Asphalt 11 a. Composition of Crude Oil 11 b. Types of Petroleum Asphalts 12 c. Fractionation of Asphalt 13 2. Native Bitumens 22 a. Native Asphalts 22 b. Asphaltites 23 C. Coal Tar Pitch 24 1. Source 24 2. Physical Properties 29 3. Chemical Properties 30 II. ENVIRONMENTAL EXPOSURE FACTORS: ASPHALT 40 A. Production and Consumption 40 1. Quantity Produced 40 2. Market Trends 40 3. Market Prices 43 4. Producers and Distributors 43 5. Production Methods 44 B. Uses 50 1. Major Uses 50 a. Paving 50 (1) Production and Consumption 50 (2) Materials 52 (3) Process Descriptions 53 b. Roofing 55 (1) Production and Consumption 55 (2) Products and Materials 58 (3) Process Descriptions 59 2. Minor Uses 61 3. Alternatives to the Use of Asphalt 62 TABLE OF CONTENTS (continued) C. Environmental Contamination Potential 63 1. Controlled and Uncontrolled Emissions 63 a. Air Blowing 63 b. Roofing Mills 65 c. Hot Mix Plants 66 d. Paving 68 2. Contamination Potential of Asphalt Transport and Storage 69 3. Contamination Potential from Disposal 69 4. Environmental Contamination Potential from Use 70 5. Weathering and Microbial Degradation 71 III. ENVIRONMENTAL EXPOSURE FACTORS: COAL TAR PITCH 75 A. Production and Consumption 75 1. Quantity Produced 75 2. Market Trends 75 3. Market Prices 75 4. Producers and Distributors 81 5. Production Process 83 B. Uses 85 1. Major Uses 85 2. Minor Uses 87 C. Environmental Contamination Potential 88 1. Emissions from Production 88 a. Coke Ovens and Tar Distilleries 88 b. Graphite Manufacture 88 c. Other Production Processes 91 2. Contamination Potential from Storage, Transport and Disposal 91 3. Contamination Potential from Use 93 4. Weathering 94 IV. ANALYTICAL METHODS 96 A. Sampling 96 - Ill - TABLE OF CONTENTS (continued) B. Methods of Sample Analysis 99 1. Separation Schemes 99 a. Solvent Extraction and/or Precipitation 99 b. Solid-Liquid Extraction c. Distillation d. Chromatography 2. Identification iMethods a. Infrared Spectroscopy (IR) b. Fluorescence and Phosphorescence Spectroscopy c. Mass Spectrometry (MS) d. Nuclear Magnetic Resonance Spectrometry (NMR) e. Ultraviolet Spectroscopy (UV) f. Other Techniques 3. Discussion of Existing and Proposed Analytical Methods C. Monitoring V. TOXICITY AND CLINICAL STUDIES IN MAN A. Effects on Organ Systems 1. Effects of Asphalt a. Effects on the Skin b. Effects on the Respiratory System 2. Effects of Coal Tar Pitch a. Effects on the Skin b. Effects on the Eyes c. Effects on the Respiratory System d. Other Effects B. Effects of Occupational Exposure 1. Exposure to Asphalt a. Refineries b. Other 2. Exposure to Coal Tar Pitch a. Exposure during Production of Pitch b. Exposure during Use (1) Electrodes (2) Patent Fuel (Briquettes) (3) Other - iv - TABLE OF CONTENTS (continued) 3. Combined Exposure to Asphalt and Coal Tar Pitch a. Roofing b. Paving 4. Prevention of Occupational Disease C. Effects of Experimental Exposure to Coal Tar Pitch D. Effects of Experimental and Therapeutic Exposure to Coal Tar Medications VI. BIOLOGICAL EFFECTS ON ANIMALS AND PLANTS A. Effects on Mammals and Birds 1. Poisonings 2. Toxicity a. Coal Tar and Pitch b. Coal Tar Medications 3. Carcinogenicity a. Introduction b. Asphalt c. Tars and Pitches Derived from Coal (I) Coal Tar (2) Heavy Tars or Pitches (3) Coal Tar Pitch (4) Coal Tar Medications (5) Other Coal-Derived Tars B. Effects on Other Animals 1. Fish 2. Invertebrates C. Effects on Vegetation D. Effects on Microorganisms E. In Vitro Studies - v - TABLE OF CONTENTS (continued) Page VII. REGULATIONS AND STANDARDS A. Current Regulations 1. Environmental Protection Agency 2. Department of Transportation 3. Occupational Health Legislation in Various Countries 4. Department of Labor, Occupational Safety and Health Administration (OSHA) a. Coal Tar Pitch Volatile Standard b. Coal Tar Pitch Volatile Standard Contested 5. Department of Health, Education, and Welfare, National Institute for Occupational Safety and Health (NIOSH) a. Criteria Document: Asphalt b. Criteria Document: Coal Tar Products c. Registry of Toxic Effects of Chemical Substances B. Consensus and Similar Standards 1. National Safety Council (NSC) 2. American Conference of Governmental Industrial Hygienists (ACGIH) VIII. TECHNICAL SUMMARY IX. RECOMMENDATIONS AND CONCLUSIONS X. REFERENCES List of Information Sources S. Petroleum Industry 45 II-3 Employment Size of Establishments (SIC ) Paving Materials 51 II-4 The Top Ten Paving Mix Producers: 51 II-5 Suggested Mixing and Application Temperatures for Asphaltic Materials 56 II-6 Employment Size of Establishments (SIC ) Roofing Materials 57 III-l Crude Tar Production and Processing: (Pitch Production 76
- viii - LIST OF FIGURES Number Page Partial Classification of Bituminous Materials 9 Fractionation of Asphalt 16 Stepwise Fractionation of Various Components of Asphalt 20 Origin of Coal Tar Pitch 27 II-l Annual Domestic Sales of Asphalt by Major Markets 42 II-2 Refinery Steps in the Production of Asphalt 47 III-l Crude Coal Tar Produced and Processed in By-Product Coke Ovens 77 III Annual Pitch Production and Sales 78 - 1 - EXECUTIVE SUMMARY Asphalt and coal tar pitch are bituminous materials used as binders, saturants and weatherproof coatings. Although they are similar in certain physical properties, they differ markedly in origin, composition, major uses, and severity of biological effects. Asphalt Petroleum asphalt is the residue, essentially uncracked, from the fractional distillation of crude oil. Small amounts of naturally occurring asphaltic materials are also used. Commercial grades of asphalt are prepared to meet standard specifications based on physical properties. Base stocks of asphalt can be formulated from residues of distillation, solvent deasphalting, or air blowing processes. Liquid (cutback) asphalts are prepared by diluting base stocks with organic solvents. Emulsions of asphalt and water are also used. Since annual asphalt sales in the United States have averaged 31 million tons. Seventy-eight percent of the asphalt is used in paving, 17% in roofing, and 5% in miscellaneous applications, including dam linings, soil stabilizers and electrical insulation. Emissions from airblowing and from manufacture of paving and roofing materials have not been well characterized, but may contain entrained as- phalt droplets, gases, trace metals, hydrocarbons, and large quantities of particulates which may contain polynuclear aromatic hydrocarbons (PAH), several of which are carcinogens. A ninety-nine percent control level of the emissions from asphalt production and processing is possible using currently available thermal - 2 - afterburners (fume incinerators) in conjunction with wet scrubbing units. Installation of paving and roofing materials may be a localized source of air pollution. Emissions can be greatly reduced by maintaining the asphalt heating kettle temperature below °C during roofing operations, and by using emulsions to replace cutback asphalts for paving. Vast surfaces of asphalt covered roads, parking lots, runways and play- grounds are subject to microbial, chemical and physical degradation, which may produce some polycyclic aromatic, heterocyclic, and metallic substances, possibly toxic or carcinogenic, in air, waterways and sediments. Limited animal skin painting and inhalation studies suggest that as- phalt may be, at most, weakly carcinogenic. Other health hazards have not been demonstrated. Few human exposure studies are available. Harmful effects from asphalt cannot be identified in exposures to mixtures of asphalt and the more bio- logically potent coal tar pitch, which have been common in paving, roofing, and weatherproofing operations. It is generally agreed that asphalt is a relatively harmless material to workers under proper working conditions (U.S. National Institute for Occupational Safety and Health, a). Present regulations limit particulate emissions from new asphalt hot mix plants and regulate effluent levels for new and existing paving and roofing point sources using tars and asphalts. The NIOSH recommended standard for occupational exposure to asphalt fumes is 5 mg airborne particulates per cubic meter of air (U.S. National Institute for Occupational Safety and Health, a). Although the OSHA standard on "coal tar pitch volatiles" has been interpreted to include asphalt, the standard has not been successfully enforced. - 3 - Coal Tar Pitch Crude coal tar is a highly cracked product evolved during carbonization of coal. All coal tar pitch commercially available in the U.S. is the distil- - lation residue of by-product coke oven tar. The amount of pitch produced has declined from 2,, tons in to 1,, tons in About 62% of this pitch is used as a binder or impregnant in carbon and graphite products. The largest single carbon product market is for carbon anodes used in primary aluminum manufacture. About 17% of the pitch produced is burned as an open-hearth furnace fuel, and 7% is used for the manufacture of "tar" saturated roofing felt and for certain commercial roofs. A stable market for pitch (10, tons annually) has been its use as a binder in "clay pigeons" for skeet shooting. Pitch bonded and pitch impregnated re- fractory bricks used to line basic oxygen furnaces, blast furnaces and foundry cupolas represent a steadily growing market. Pitch can undergo the same basic processing as does asphalt, namely air blowing, dilution with coal tar solvents, or emulsification with water. Emissions from manufacturing processes using pitch may include large amounts of pitch dust as well as pitch volatiles. Air pollution control measures used for asphalt fumes can also be used to contain emmissions from pitch. Large amounts of volatiles are emitted during the production of prebaked and graphi- tized pitch-containing carbon products, a major use of pitch. During use of such materials, higher levels of emissions are generated by self-burning elec- trodes than by those that have been prebaked or graphitized before use. A large proportion of workers exposed to pitch and sunlight develop moderate to severe acute phototoxic reactions of the skin and eyes. Exposure to pitch and coal tar can cause skin cancer (U.S. National Institute for Occupa- tional Safety and Health, b). Inhalation of fumes and particulates may be - 4 - related to increased incidence of lung cancer. Some cases of cancer of the bladder and certain other organs may be related to exposure to coal tar pitch. Although they do contain carcinogenic PAH, topical medications based on crude coal tar, which have been widely used for the prolonged treatment of chronic skin diseases, do not appear to have caused cancer in humans when properly used. Some attempt has been made to control worker exposure to emissions from coal tar pitch. The present standard for "coal tar pitch volatiles" (other than coke oven emissions) specifies that worker exposure to airborne con- centrations of pitch volatiles (benzene soluble fraction) shall not exceed mg per cubic meter of air (U.S. Department of Labor, ) . The cur- rent interpretation of the coal tar pitch volatile standard covers volatiles from distillation residues not only of coal, but also of other organic ma- terials including petroleum (i.e., asphalt). Because coal tar pitch vola- tiles are considered carcinogenic, the National Institute for Occupational Safety and Health (b) has recommended a standard for occupational ex- posure to coal tar products, including coal tar pitch, of mg cyclohexane solubles per cubic meter of air (the lowest detectable limit). Examination of the literature indicates that the biological effects of asphalt are probably limited. Large quantities, however, are processed and the major uses are in roofing and paving products that are permanently ex- posed to slow degradation in the environment. Coal tar pitch, on the other hand, produces acute effects in a large proportion of exposed workers as well as possible increased risk of cancer of several sites after prolonged ex- posure. The major uses of pitch involve occupational rather than environmental exposure. - 5 - INTRODUCTION Asphalt and coal tar pitch are used in a variety of industrial pro- cesses and manufactured products that utilize their properties as thermoplastic, durable, cementitious, water-resistant materials. The Environmental Pro- tection Agency, Office of Toxic Substances, has requested a preliminary literature investigation of the environmental contamination potential of these two bituminous materials. This noncritical review is intended to serve as a source of information to be used in evaluation of the severity of the environmental hazard and the need for further action concerning these two materials. In this report, "asphalt" is considered to be the residue, essentially uncracked, from the fractional distillation of crude petroleum. Coal tar pitch is defined as the residual product from the distillation of crude coal tar, a cracked material, which is formed during the coking of coal. A survey of the literature since was conducted, referring to older literature when recent information was unavailable. The literature review includes composition and properties; production figures and process descriptions; contamination potential from manufacture and use,' analysis,' toxicity and carcinogenicity to humans, animals, and plants; recommended handling practices; legislation; and standards. Conclusions and recommendations based on the literature are also presented. - 6 - GLOSSARY ASPHALT - A black to dark-brown solid or semisolid cementitious material in which the major constituents are bitumens. Asphalt occurs naturally (asphaltites and native asphalts) or is obtained as the residue, essentially uncracked, from the straight distillation of petroleum. BITUMEN - A mixture, completely soluble in carbon disulfide, of hydro- carbons of natural and/or pyrogenous origin and their nonmetallic deriva- tives . BITUMINOUS MATERIAL - A mixture, containing bitumen or constituting the source of bitumen, occurring as natural (asphaltite, tar sand, oil shale, petroleum) or manufactured (coal tar pitch, petroleum asphalt, wax) material. COAL TAR - A brown or black bituminous material, liquid or semisolid in consistency, obtained as the condensate in the destructive distillation (coking) of coal, and yielding substantial quantities of coal tar pitch as a residue when distilled. COAL TAR PITCH - A black or dark-brown material obtained as the residue in the partial or fractional distillation of crude coal tar. As con- trasted to petroleum asphalt, which is essentially uncracked, coal tar pitch is a highly cracked material. - 7 - COAL TAR PITCH VOLATILES - The fumes from the distillation residue of coal tar. In legal use, this term refers to the volatiles from the distillation residues of coal, petroleum or other organic matter. In this report, use of this term in connection with asphalt fumes has been avoided except in discussion of the legal definitions. CRACKING - A process (e.g., pyrolysis, thermal treating, coking) whereby large molecules (as in oil or coal) are decomposed into smaller, lower boiling molecules, while reactive molecules thus formed are recombined to create large molecules (including PAH) different from those in the original stock. PETROLEUM PITCH - A cracked product resulting from pyrolysis of gas oil or fuel oil tars. Because it shares certain properties with coal tar pitch, it has been suggested as a replacement for it in some applications. This term should never be used to refer to an asphalt product. Petroleum pitch is not included within the scope of this report. Abbreviations: BaP Benzo(a)pyrene BeP Benzo(e)pyrene CTPV "Coal tar pitch volatiles" (see Glossary) PAH Polynuclear aromatic hydrocarbons PNA Polynuclear aromatic compounds, including both hydrocarbons and heterocyclics (use in this report has been avoided) PPOM Particulate polycyclic organic matter - 8 - I. PHYSICAL AND CHEMICAL PROPERTIES A. Bituminous Materials Asphalt and coal tar pitch belong to a group known as bituminous materials. Bitumens are defined as mixtures of hydrocarbons and their norunetallic deri- vatives of natural or manufactured origin, which are completely soluble in carbon disulfide (Hoiberg, a,b). In British and European usage, however, the term "bitumen" is used to refer to the material known in the United States as "asphalt," Among the many ma- terials which may be considered as bituminous, only native and manufactured asphalts and manufactured coal tar pitch, as shown in Figure , will be dis- cussed in this review. Asphalt is a dark brown to black cementitious solid or semisolid material, composed predominantly of high molecular weight hydrocarbons, occurring either as a native deposit or as a component of crude petroleum, from which it is separated as a distillation residue without pyrolysis. The asphalt content of crude oils varies from 9 to 75% (Ball, ), and the nature of the asphalt varies with its parent crude. About 98% of the asphalt used in the United States is derived from crude petroleum (Miles, ). Coal tar pitch is the distillation residue of crude coal tar, which is a pyrolysis product from the high temperature carbonization (coking) of coal. Coal tar pitches, brownish black to black in color and containing at least compounds, range from viscous liquids at ordinary temperature to materials which behave as brittle solids exhibiting a characteristic conchoidal fracture (McNeil, ). msliUation Gas Oil, 'icatinq OiU,ekc. cok« «n o V RESIDUE JNlWE Native A Gmharnite, Manjak Native/ Asphalts Truiidadl fLake SancU Bermurlez Cnke Asphalt .. Oil X Oil Cteosobe. ^{JkrtUjerve, OIL, ebc. FIGURE PARTIAL CLASSIFICATION OF BITUMINOUS MATERIALS - 10 - Because the uses of asphalt and pitch depend largely on physical prop- erties, specifications are based on empirical tests using strictly defined procedures. Most of these tests are covered by standards of the American Society for Testing and Materials (ASTM) () and the American Associa- tion of State Highway Officials (AASHO). The Asphalt Institute (a) presents brief descriptions of tests and methods for asphalt. A few of these tests are as follows: Penetration - a measure of consistency expressed as the distance, in tenths of a millimeter, that a standard needle penetrates under known conditions of loading, time and temperature. Softening point (ring and ball,, R & B) - the temperature at which a standard weight ball sinks below the bottom of a standard ring containing asphalt. Viscosity - a measure of the consistency of asphalt at two set temperatures. Normally, the viscosity-graded asphalt cements are identified by viscosity ranges at 60 and °C.. Sixty degrees is the approximate maximum temperature used in pouring asphalt, and °C is the approximate mixing and laydown temperature for hot asphalt pavements. Flash point - the temperature to which asphalt may be safely heated without an instantaneous flash in the presence of an open flame. Ductility - the distance in air which a standard briquet at 25°C can be elongated before breaking. Solubility - a measure of purity of the asphalt, determined by dissolving the asphalt in trichloroethylene and separating the soluble and insoluble portions by filtration. Water content - generally measured by refluxing asphalt product with - 11 - xylol or high-boiling-range petroleum naphtha and collecting and measuring the water condensate in a trap. Specific gravity - the ratio of the weight of a given volume of bituminous material to that of an equal volume of water at the same temperature, usually reported as 77/77°F. B. Asphaltic Materials 1. Petroleum Asphalt a. Composition of crude oil As indicated in the beginning of this chapter, the asphalt content of crude oil varies (%) and the nature of asphalt varies with its parent crude. Crude oil is a very complex mixture and no single crude oil has ever been completely defined (Rossini and Mair, , ; Rossini et al., ; Altgelt and Gouw, ). The enormous diversity of different crude oils extends from light oils to heavy types found in asphalt lakes. These variations are found not only in the viscosity, but also in the content and length of paraffinic chains, number of aromatic carbon atoms, degree of ring fusion and type and amount of hetero atoms. More than several hundred compounds have been identified in Ponca City (Oklahoma) crude oil. They have been classified into nonpolar and polar materials. The nonpolar group includes straight chain alkanes, (hexane, pentane), branched alkanes .(isooctane), cycloalkanes (butylcyclohexane), and aromatics (propylbenzene and propyltettralin). The polar group in- cludes acids such as naphthenic acids, phenols, alkylthiols, cycloalkylthiols, alkylthiophenes, pyridines, quinolines, indoles, pyrroles and porphyrins. Nickel ( ppm, Berry and Wallace, ) and vanadium ( to weight percent) are the most prominent trace metals that occur in petroleum (Atlas and Bartha, ; Yen, ). Calcium, magnesium, titanium, cobalt, tin, - 12 - zinc, and iron are also metals commonly found in crude petroleum. These metals tend to accumulate in the residue. b. Types of petroleum asphalts Distillation is the primary means for separating crude petroleum fractions. Asphalt is the high-boiling residual fraction. Crude oil may be distilled first at atmospheric pressure to remove the lower boiling fractions such as gasoline or kerosine and then can be further processed by vacuum distillation, leaving a straight-run asphalt. The asphaltic residue may also be processed with liquid propane or butane. Vacuum distillation and propane deasphalting both affect the hardness of the residue. When processed from the same stock, propane deasphalted residue differs little from straight-run residue (Corbett, ; Hoiberg e_t al., ; Hoiberg, a). Straight-run asphalt accounts for 70 to 75% of all the asphalt produced. Airblown asphalts with modified properties as compared to straight run asphalt are produced from the asphalt stock by treatment with air at tempera- tures of to °C. Catalysts such as phosphorus pentoxide, ferric oxide or zinc chloride/used in concentrations from to 3%xreduce the air blowing time. The asphalt undergoes dehydrogenation and polymerization by ester formation and carbon linkage (Smith and Schweyer, ; Haley, ; Corbett, ) during these processes. The presence of dicarboxylic anhydrides in oxidized asphalts has been confirmed by infrared spectroscopy (Petersen et al., ). There is a decrease in the aromatic resin content and an increase in the asphaltene content and hydrogen bonding basicity of airblown asphalt (Harbour and Petersen, ). Air blowing results in a product with a higher softening point for given penetration than straight reduced asphalt, while catalytic air blowing produces a still higher softening point. Air blown asphalt, which accounts for 25 to 30% of asphalts used, is a - 13 - viscous .material that is less susceptible to temperature change than straight run asphalt. Treatment of asphalt at high temperature (°C) and pressure ( psig) produces thermal asphalts, less than 5% of total production of asphalt, which are not commonly available because catalytic cracking for the production of gasoline has largely replaced thermal cracking. Such asphalts are characterized by a relatively high specific gravity, low viscosity and poor temperature susceptibility (little change in consistency with increased temperature). They have a lower hydrocarbon to carbon ratio than, straight run asphalts. Highly cracked residues have infrared spectra similar to those of coal tar pitches CCorbett, ; Hoiberg £t a^., ; Hoiberg, a). The vis- cosity is more susceptible to temperature change in thermal asphalts than in straight run asphalt. An elemental analysis of asphaltic residues (% by weight) shows carbon ranging from 80 to 89%, hydrogen from 7 to 12%, oxygen from 0 to 3%, sulfur from trace to 8% and nitrogen from trace to 1% (Table ). c. Fractionatipn of asphalt The high molecular weight (M.W. ) asphaltene fraction is precipi- table by n-pentane, hexane or naphtha and, despite source, appears constant in composition as determined by carbon-hydrogen analysis. Asphaltenes are solid at room temperature and show some degree of crystallinity by X-ray diffraction. The concentration of asphaltenes to a large extent determines the viscosity of asphalt (Altgelt and Harle, ; Reerink, ; Reerink and Lijzenga, ) . Maltenes, the nonprecipitated fraction, are generally considered to contain resins CM.W. ) characterized by high temperature susceptibility that are either adsorbed on activated clays or precipitated by sulfuric acid TABLE I-l. ELEMENTAL ANALYSES OF ASPHALT FRACTIONS AND NATURAL ASPHALTS Softening Penet point (ring and ball) °C .ration, Elemental analyses, % by wt c,°r ratio, C H S N Oa C/H Petroleum Straight run asphaltenes petrolenes Air-blown asphaltenes petrolenes Highly cracked 50 36 asphaltenes petrolenes Native Trinidad Bermudez 88 87 80 82 .9 .9 .9 5 7 10 10 .9 .9 .7 .8 3 3 6 5 .0 .7 .8 .9 0 0 0 0 .4 .5 .8 .8 1 0 0 0 a Oxygen determined by difference Sources: Hoiberg e_t al^. , - 15 - or a solvent (acetone, isobutyl alcohol, propane). The nonprecipitable maltene fraction consists of oils (M.W. ) which may contain appreciable quantities of wax and are characterized by low temperature susceptibility. The petrolene fraction (M.W. ) boils below °C and is soluble in low-boiling saturated hydrocarbons such as n-pentane. In addition, asphalts may contain saponifiable material and acids, the content of which is determined as percent naphthenic acids in the original crude (Corbett, ; Hoiberg, a; Hoiberg ejt al_., ). Most separations of asphalt into its constitutional components rely on some type of preliminary fractionation (Figure ) prior to the use of gel permea- tion, gas-liquid, paper, gravity fed column or high performance chromatography (Couper, ; Schweyer, ). The fractions obtained are then further analyzed by use of ultraviolet spectrometry, nuclear magnetic resonance, infrared spectros- copy, electron spin resonance, atomic absorption or X-ray diffraction, as de- scribed in Chapter IV. Five principal operations (distillation, extraction, adsorption, precipi- tation and chromatography) are used in various combinations for the fractionation of asphaltic bitumens (Rostler, ; Hoiberg, a; Hoiberg £t al_., ) to produce a variety of fractions that can be classified into a few general groupings (Figure ). However, none of these fractionation methods have provided satisfactory results when used separately. Distillation Distillation is used to concentrate the asphaltenes and maltenes and to separate out the petrolenes. However, this method by itself is not useful as an analytical separation procedure for complex mixtures (Hoiberg,). ASPHALT n-pentane 4- 4 Insoluble So ASPHALTENES MAL luble TENES extraction, precipitation or column chromatography 4, -J' OILS RESINS FIGURE FRACTIONATION OF ASPHALT - 17 - Extraction Carbon disulfide has been used in the separation of asphalt into low boiling petrolenes and a residual fraction, while n-pentane has been used as a means of fractionating asphalt into asphaltenes and raaltenes. However, these types of extractions give only a partial separation of asphalts (Rostler, ). A more complex separation involves the Hoiberg method (Hoiberg and Garris, ) which separates the asphalt stepwise into five fractions: (1) asphaltenes (2) hard resins, (3) waxes, (4) soft resins, and (5) oils. The Traxler-Schweyer method (), a simplified Hoiberg method, consists of stepwise separation into (1) asphaltenes precipitated by n-butanol and (2) a n-butanol-soluble fraction consisting of paraffins and naphthenes. Lastly, the method of Knowles et al. () involves stepwise fractionation into-(l) asphaltenes, (2) soft and hard resins, (3) waxes and (4) paraffinic and naphthenic oils. This last method is valuable because it separates asphalts into waxes, two types of resins and two kinds of oils. Adsorption Fractionation by adsorption has involved charcoal, charcoal and sand, and various kinds of molecular sieves. Early methods consisted of heating mixtures of liquid bitumens with adsorbents such as charcoal and fuller's earth, followed by filtration. They are considered the predecessors of modern chromatographic methods, which use the principles of both solvent extraction and adsorption. Molecular sieves can still be considered to be a relatively new tool which is being incorporated into separation procedures for asphaltic bitumens (Rostler, ; Couper, ). - 18 - Chroma tography A number of fractionation methods have used chromatography, either by itself or in combination with extraction and adsorption methods. Silica gel is used to separate maltenes into resins and oils and maltenes or asphal-- tenes into non-aromatics, aromatics and polar compounds. The Glasgow-Ter- mine method, which also uses silica gel, elutes two pentane fractions and one fraction each of benzene, carbon tetrachloride and ethanol, while the Hubbard-Stanfield method involves (1) precipitation of asphaltenes with n-pentane, (2) elution of oils from alumina with n-pentane and (3) elution of resins from alumina with methanol-benzene mixture. In each of these methods, however, the overlapping of components from each fraction is typi- cal for these chromatographic techniques (Rostler, ). Two elaborate methods have been attempted by Kleinschmidt () and O'Donnell (). The Kleinschmidt method involves (1) precipitation of asphaltenes with n-pentane, (2) elution of the n-pentane soluble fraction from fullers earth to obtain (a) white oils with n-pentane, (b) dark oils with methy- lene chloride/ (c) asphaltic resins with methyl ethyl ketone, ar.d (d) a black residue desorbed with a mixture of acetone and chloroform. The O'Donnell method involves molecular distillation on the basis of molecular size followed by silica gel chromatography to separate saturates, aromatics, and resins. The saturates are dewaxed followed by urea-complex formation to separate long chain paraffins, and the aromatics are separated by alumina chromatography into mono- and di-cyclic aromatics, followed by peroxide oxidation and another chromatography to separate the benzothiophene analogs. - 19 - Precipitation The chemical precipitation methods, use excess amounts of reagents to remove one component or fraction from the complex mixture. One method (Rostler, ) involves the precipitation of asphaltenes by low boiling hydrocarbons, followed by precipitation with sulfuric acid. The Rostler-Sternberg method () in- volves precipitation of asphaltenes with n-pentane and selective precipitation of the nitrogen bases and acidaffins 1 and 2 by use of successive concentrations of H2SC>4 (85%, 98%, fuming (S03)). The applicability of these methods to complex mixtures is still under investigation. A more recent method by Corbett () uses n-heptane, benzene, and methanol-benzene-trichloroethylene as solvents to obtain petrolenes, asphaltenes, saturates, aromatics and polar fractions. All of the methods and combinations described above, as well as others described in reviews (Couper, ; Schweyer, ; Altgelt and Harle, ), have been used in analysis of the complex mixtures of various types of asphalts. Figure shows a composite stepwise fractionation of the various components of asphalt. Techniques such as solvent fractionation, thermal diffusion and sulfuric acid precipitation and chromatography have yielded asphaltic fractions that have been examined using infrared (Petersen et al., ) and ultraviolet specr troinetryr X-ray diffraction, nuclear magnetic resonance, electron spin reson-r ance and:atomic absorption (Couper, ). Little is known at present about polynuclear aromatic hydrocarbons (PAH) in asphalt. Wallcave et al. () have presented average concentrations of PAH in asphalt obtained from various sources (Table ). More work needs to be done in the area of PAH determinations in asphalt. STEPWISE FRACTIONATION OF VARIOUS COMPONENTS OF ASPHALT TABLE * CONCENTRATION AVERAGES OF SEVERAL PARENT PAH IN ASPHALT (ppm) Asphalt Phenanthrene Pyrene Benz[a]- anthracene 1 2 3 4 5 6 7 8 ^35 ' ^ 38 35 Tri- phenylene Chrysene Benzo[a]- pyrene 34 27 Benzofe]- Perylene Benzofghi]- Coronene pyrene perylene - 13 39 w ' 52 15 - Trace Benzofluorenes, fluoranthene, benzo[k]fluoranthene, anthracene, picene and indeno[l,2,3-cd]pyrene are present in trace amounts. Source: Wallcave et al^v - 22 - As indicated previously, some of the metals present in crude oil tend to accumulate in the asphalt. Vanadium, nickel, and iron tend to be concentrated in the asphaltene fraction (Corbett, ), Vanadium chelates have been studied in petroleum asphaltenes (Tynan and Yen, ; Wolsky and Chapman, (). Other metals are bound to polynuclear aromatic compounds containing sulfur, nitrogen and oxygen polar groups as well as naphthenic and paraffinic side chains. During air blowing, these polynuclear aromatics are converted to asphaltenes. Removing the asphaltene fraction from blown asphalt can re- move up to 97% of the organometallics. 2. Native Bitumens Native bitumens include a wide variety of natural deposits ranging in character from crude oil to sand and limestone strata impregnated with bi- tuminous material. Only a few of these materials are classified as asphalts. a. Native asphalts The native asphalts include a variety of reddish brown to black materials of semisolid, viscous-to-brittle character. They can occur in relatively pure form, with 92 to 97% soluble in carbon disulfide and only 3 to 8% mineral con- tent, as is the case for Bermudez (Venezuela) lake asphalt, or in less pure form, wi-ch a carbon disulfide-soluble fraction of 39% and a mineral content of 27%, as is the case for Trinidad lake asphalt (Table ). Trinidad lake as- phalt is dull black and semiconchoidal in fracture, with a penetration of 10 at 30°C and a softening point (R & B) of 85° c. When gas and water are driven off at °c, Trinidad asphalt loses 29% of its weight and the carbon disulfide- soluble fraction increases to 56% while the mineral content increases to 38%. - 23 - Frequently, the bitumen is found in pores and crevices of sandstones, limestones or argillaceous sediments and is known as rock asphalt. The term "tar sands" has been used by geologists to designate sands impregnated with dense, viscous asphalt found in certain sedimentary structures, such as the Athabasca tar sands now being mined in Alberta, Canada (Hanson, ; Broome, ; Camp, ; Breger, ). b. Asphaltites Asphaltites are naturally occurring, dark brown to black, solid, and relatively nonvolatile bituminous substances differentiated from native as- phalts primarily by their high content of n-pentane insoluble material (asphaltene) and their high temperature of fusion, to °C (R & B). Among these are gilsonite, grahamite and manjak, all of which are in the pure state, with close to % carbon disulfide solubility and less than 5% jnineral content. Gilsonite, the native asphaltite most commonly used, is found in western Colorado and eastern Utah. It is black in color with a bright luster, a conchoidal fracture, and a penetration at 41°C of 3 to 8 with a softening point (R & B) of to °F ( to °C). Gilsonite has a car- bon content of 85 to 86%, is soluble in carbon disulfide to 98%, and has a specific gravity of to at 25°C (77°F). Grahamite is found in a single vertical fissure in a sandstone in West Virginia. It has a specific gravity of to at 77°F and a softening point (R & B) of to °F ( to °C), and a high tem- perature of fusion which distinguishes it from gilsonite. Other deposits in the United States, as well as in Mexico, Cuba and certain areas of South America, have yielded bitumens corresponding in general to the graha- mite in West Virginia, and are therefore referred to under this name. - 24 - A third broad category is known as glance pitch or manjak, originally mined in Barbados, West Indies. The specific gravity at 77°F (25°C) is to , with a carbon content of 80 to 85%, a softening point (R s B) of to °F (to °C), a carbon disulfide soluble fraction of 95%, a black color and a bright to fairly bright luster with a conchoidal to hackly fracture. This asphaltite is considered an intermediate between graha- mite and gilsonite because of its specific gravity and fixed carbon (Broome, ; Hanson, ; Hoiberg ejt a^., ; Breger, ). C. Coal Tar Pitch 1. Source Coal can be described as a compact stratified mass of vegetation^ inter- spersed with smaller amounts of inorganic matter, which has been modified chemi- ically and physically by agents over time. These agents include the action of bacteria and fungi, oxidation, reduction, hydrolysis and condensation, and the effects of heat and pressure in the presence of water. The chemical properties of coal depend upon the amounts and ratios of different constituents present in the vegetation, as well as the nature and quantity of inorganic material and the changes which these constituents have undergone (Francis, ). Coal, therefore, has a rather complicated chemical structure based on carbon and hydrogen with varying amounts of oxygen, nitrogen and sulfur. Bi- tuminous coal, from which coal tar pitch is derived, contains a number of PAH, including carcinogenic benzo(a)pyrene (BaP) and benz(a)anthracene (Tye et al., ), and a variety of toxic trace elements such as antimony, arsenic, beryllium, cadmium, lead, nickel, chromium, cobalt, titanium, and vanadium (Zubovic, ). When coal is pyrolyzed, a variety of changes occur: above °C free water evaporates; above °C combined water and carbon dioxide are evolved; above °C bituminous coals soften and melt, decomposition begins, and tar - 25 - and gas are evolved; at to °C most of the tar is evolved; at to °C decomposition continues and the residue turns solid; above °C the solid becomes coke and only gas is evolved; around °C no more gas is evolved and only coke remains; above °C small physical changes occur When coal undergoes carbonization, it passes through two steps of de- composition: onset of plasticity at to °C and advanced decomposition at to °C. Volatile products released at each stage undergo a series of secondary reactions as they pass through the coke before emerging from the retort. The volatiles are separated by fractional condensation or absorption into tar, ammoniacal liquor, benzole, and illuminating or heating gas (McNeil, a). The major reactions in the conversion of primary carbonization products into tars (McNeil, a) areJ 1) cracking of higher molecular weight paraffins to gaseous paraffins and olefins; 2) dehydrogenation of alkylcyclic derivatives to aromatic hydrocarbons and phenols; 3) dealkylation of aromatic, pyridine and phenol derivatives; 4) dehydroxylation of phenols; 5) synthesis of PAH by condensation of simpler structures; 6) disproportionation of PAH to both simpler and more complex structures. The temperature of carbonization and contact time with the hot coke bed and heated walls of the retort will determine the composition of tars, as well as the extent of the reactions. Tars from the different types of carbonization processes vary widely as to their composition and characteristics. - 26 - The term low temperature carbonization refers to pyrolysis of coal to a final temperature of °C. The final solid product is a weak coke with high yields of tar and oil and low yield of gas. High temperature carboni- zation is pyrolysis of coal between °C and °C, with town gas as the product and coke as the by-product at the lower temperature and metallurgical coke as the product and gas as the by-product at the higher temperature CEncyclopaedia Britannica, ) . Coal tar pitch is the residue from the processing of coal tar (Figure ), Pitches or "refined tars" are obtained from the distillation of tars and rep- resent from 30 to 60% of the tar components (McNeil, a) (Table ). Distillate oils (described later) obtained by steam or vacuum distillation of pitch or pitch crystalloids or from coking of pitch are the only fractions from which pure chemical compounds are isolated. McNeil (a) has described the change in composition of tars found as the temperature increases from vacuum distillation or low temperature carboni- zation to high temperature carbonization: (a) The amounts of paraffins and naphthenes decrease and disappear, the naphthenes fading out before the paraffins. (b) The amount of phenolic material falls from about 30% to a small value. (c) The proportion of aromatic hydrocarbons increases from a low figure to over 90%. (d) The proportions of aromatic, phenolic and heterocyclic compounds containing alkyl side chains decrease markedly. (e) The proportion of condensed ring compounds containing more than three fused rings increases. (f) The yield of coal carbonized decreases from 10% to less than 5%. CCM V 'Upper boiliiur point U3O"c I Includes alshamasislamicinstitute.com.pk, toluene, alshamasislamicinstitute.com.pk^lilna, a liv&tflts «hHirfrcenc. and creosote, Auctions. TfiflEDTIK ana toumattmc.. 5. IHC14 FIGURE ORIGIN OF COAL TAR PITCH i N) - 28 - TABLE TYPICAL ANALYSES (PERCENT BY WEIGHT) OF TARS Coke Oven Tar Gas Works Tar Low Temperature Tar (°C) Pitch Creosote Light Oils Heavy Oils £ Source: Encyclopaedia Britannica, - 29 - 2. Physical Properties Coal tar pitch is a black or brownish black shiny material ranging from a viscous liquid at ordinary temperatures (30 to 80°C) to a material which be- haves as a brittle solid exhibiting a characteristic conchoidal fracture (McNeil, a; Lauer, ). At higher temperatures the brittle solid pitch can become a viscous liquid. It has a characteristic "tarry" odor described as a combination of smells of naphthalene and phenol modified by small amounts of pyridine and thiophenol. The residue from the primary distillation can have different viscosity grades depending on how extensively the coal tar is distilled. If the dis- tillation is continued to the desired softening point, the residue is called "straight run" pitch to distinguish it from "cut-back" or "flux-back" pitch, which is a straight run pitch of harder consistency cut back to the desired softening point with tar-distillate oil (McNeil, ). Since pitch is composed of a great number of different compounds, it does not show a distinct melting or crystallizing point. Therefore, pitch is usually characterized by the softening point, which can be determined by one of several standard methods: ring and ball, cube in air, cube in water and Kramer-Sarnow (McNeil, b). Each of these methods represents the tempera- ture at which a given viscosity or softness is attained under specific con- ditions . The softer grades of pitch having softening points (R &. B) below 50°C are usually referred to as base tars or refined tars; other grades are soft pitch (50 to 75°C), medium-hard pitch (85 to 95°C), and hard pitch (above 95°C) (McNeil, S). - _ - 30 - In general, all pitches behave essentially as Newtonian liquids over the range of viscosities which can be measured reliably. The only departure from Newtonian flow in pitches is a slight reduction in viscosity with in- creasing shearing stress found in samples with a high content of toluene in- soluble materials. 3. Chemical Properties It has been difficult to isolate and characterize compounds from this complex bituminous material. It has been estimated that pitch contains five to ten thousand compounds, of which to have been isolated and identi- fied (McNeil, b). Among those identified have been a large number of PAH. Varying amounts of PAH are formed by secondary reactions occurring during carbonization of coal. Coal tar pitch is composed predominantly of carbon (86 to 93%) and hy- drogen (5 to 7%), with small amounts of nitrogen ( to %), oxygen, and sulfur. Nitrogen is usually present in either five- or six - membered rings or as nitrile substituent. Oxygen is present as phenolic and quinone sub- stituents, as well as in four-, five-, or six- membered rings. Sulfur is usually found in five-membered rings (McNeil, ). Analysis for certain metals in coal tar has revealed high concentrations of zinc (over yg/g) and lead (70 to 75 yg/g); concentrations of between 1 and 10 yg/g of iron, cadmium, nickel, chromium, and copper have been found (White, ). Mag- nesium, boron and vanadium have also been identified in coal tar pitch (Liggett, ). Because of the importance of pitch in various industries, a number of studies have been carried out to elucidate its structure. Most specifications for coal tar pitches include limitations of solubility in certain solvents. Different solvents are required for various specifications and the methods used vary among investigators. These differences have made it difficult to compare - 31 - results (McNeil, b). Table indicates several methods which may be roughly equated. The Demann () and Broche and Nedelmann () methods divide the pitch into material insoluble in benzene (a-component), material soluble in benzene but insoluble in petroleum ether (0-component) and material soluble in petroleum ether (5-component). Adam et_ a!U () extend the above methods by separating the benzene extract into soluble and insoluble portions, by add- ing the concentrated benzene extract to 10 times its volume of petroleum ether, and by separating the a-component into pyridine soluble (2) and pyridine in- soluble (C^) fractions. The petroleum ether soluble portion is referred to as "crystalloids" and the petroleum ether insoluble but benzene soluble por- tion is called "resinoids." Crystalloids are also defined as being soluble in hexane or similar aliphatic solvents. Dickinson () modifies the Adam, method by performing a vacuum dis- tillation on the pitch to obtain distillate oils, extracting the residue with benzene and pyridine, precipitating the benzene extract with petroleum ether and extracting the precipitate with n-hexane. Resin A is that part of the pitch soluble in n-hexane or petroleum ether; Resin B is that part of the pitch insoluble in hexane but soluble in benzene and in fractions C^ and C2- A solvent analysis method (Mallison, ) which has been widely used in Europe divides the pitch into five fractions: H-resins, M-resins, N-resins, m-oil^ and n-oils. The method is not a solvent fractionation and the fractions are not further analyzed (McNeil, b). A number of other solvent analysis or fractionation methods that have been used are toluene and tetralin solvents; carbon disulfide, pyridine, benzene, petroleum ether and diethyl ether; pyridine, xylene and decalin; and nitrobenzene and acetone. - 32 - TABLE TERMINOLOGY APPLYING TO ANALOGOUS FRACTIONS AS DETERMINED BY FOUR FRACTIONATION PROCEDURES Adam et al . () ~ Cl C2 Resinoids Crystalloids Dickinson () Cl C2 Resin B + some Resin A Distillate oils + some Resin A Demann () a-Fraction B-Fraction 6 -Fraction Mallison () H-Resins M-Resins N-Resins m-Oils and n-oils Source: McNeil, 19GGL TABLE MOLECULAR WEIGHT AND HYDROGEN TO CARBON RATIO OF MEDIUM-SOFT COKE OVEN PITCH Fraction Wt. range % Reported Av. atomic Solubility mol. wt. H/C ratio Crystalloid Resinoid C2 G! Sol. petroleum ether insol. petroleum ether, soluble benzene insol. benzene to insol. pyridine, quinoline Source: McNeil, b - 33 - To indicate the variability in these separations, the H-resin content is between and % while M-resin content is to % in vertical retort tars. The variations in pitches from coke ovens are H-resins to % and M-resin to %. The same kind of variability holds true for crystalloids (45 to 60%), resinoids (16 to 24%), C2 (5 to 15%) and C^ (3 to 28%) in coke oven pitch. Tars from vertical retorts contain 55 to 70% in crystalloids and less C± and resinoids while low temperature pitch contains less than 1% C± and 7u to 80% crystalloids (McNeil, b). The molecular weight and hydrogen to carbon ratio of crystalloids, re- sinoids, GI and C2 are represented in Table The overall range in mole- cular weight for coal tar is between and The C^ fraction has a much lower H/C ratio. Low temperature processes are found to have higher H/C ratios. A value of has been reported for the crystalloid fraction from continuous vertical retort pitch (Greenhow and Smith, ). The distillate oil fraction has been subjected to many analyses and is the only fraction of pitch from which pure chemical compounds can be isolated by techniques normally used, such as fractionation and chromatographic separation methods. McNeil (b) has listed compounds all boiling above °C (an arbitrary cut off value), most of which are condensed PAH and their hetero- cyclic analogs, from pitch or refined tar which is sufficiently volatile to distill without decomposition. A partial list is shown in Table PAH found in refined coal tar and in high temperature conversion process coal tar are listed in Tables and , respectively. The pitch crystalloids contain the same major components as the dis- tillate oils. They are composed of polynuclear aromatics with an average of 3 to 6 rings and with a molecular weight in the range of to Com- pounds similar to those indicated in Table are: acenaphthene, fluorene, - 34 - TABLE - 35 - TABLE PAH IN COAL TAR PNA Anthracene Benz [a] anthracene Benzo[b] chrysene Benzo [ j ] f luoranthene Benzo [k] f luoranthene Benzo [g , h, i] perylene Benzo [ a ] pyrene Benzo [e]pyrene Carbazole Chrysene Dibenz[a,h] anthracene Fluoranthene Perylene Phenanthrene Pyrene Concentration (g/kg) in coal tar* (1) (2) *Two samples of medicinal coal tar Source: Lijinsky et al_., - 36 - TABLE MAJOR COMPONENTS OF GERMAN HIGH-TEMPERATURE CONVERSION PROCESS COAL TAR Average Component weight percent Naphthalene Phenanthrene Fluoranthene Pyrene Acenaphthylene Fluorene Chrysene Anthracene Carbazole 2-Methylnaphthalene Diphenyleneoxide Indene Acridine 1-Methylnaphthalene Phenol m-Cresol Benzene Diphenyl Acenaphthene 2-Phenylnaphthalene Toluene Quinoline Diphenylenesulfide Thionaphthene m-Xylene o-Cresol p-Cresol Isoquinoline Quinaldine Phenanthridine 7,8-Benzoquinoline 2,3-Benzodiphenyleneoxide Indole 3,5-Dimethylphenol 2,4-Dimethylphenol Pyridine a-Picoline B-Picoline y-Picoline 2,6-Lutidine 2,4-Lutidine Source: Shults, - 37 - phenanthrene, anthracene, pyrene, anthraquinone and chrysene(Hoiberg, a). The more complex part of coal tar pitch (30%), represented by C^, C2 and resinoid fractions, appears to be a continuation of a series formed from less complex, more soluble and more volatile fractions (Table ), and con- sists mostly of ring systems not highly condensed, with the majority of the rings fused to not more than three other rings (McNeil, b). Osmotic pressure measurements have given estimates of to for the molecular weight of resinoids. The oxygen, nitrogen and sulfur content is reported to be 1 to , to , and to atoms per hundred atoms/ respectively, indicating that this fraction is largely hydrocarbons (McNeil, a). The C2 fraction is different from the resinoid fraction and is considered to be a complex mixture of polynuclear compounds with 5 to 20 fused rings. Carbon in the ring is the most abundant element but oxygen, nitrogen and sulfur are also present in lesser amounts. There is a fair amount of substitution, primarily methyl and hydroxy groups, the degree of methylation increases with molecular weight, and the ring structure is not highly condensed. The Cj fraction, pyridine insoluble material, is a black infusible powder partly soluble in quinoline, appearing to have a molecular weight range of to This C± fraction is highly variable and depends on the type of coal and the means of production. It is thought to consist of dis- persed particles that vary from one to two micrometers in diameter. The particles absorb variable amounts of high molecular weight tar resins. Therefore quino- line extracts more of the resins from the dispersed material than does pyri- dine (McNeil, a; Koiberg, a). - 38 - TABLE PREDOMINANT STRUCTURES IN COKE OVEN TAR Boiling Average range percent Major components (°C) of tar Single 6-membered rings Benzene Toluene Xylenes 3 Fused 6,5-ring systems Indene Hydrindene Coumarone 12 Fused 6,6-ring systems Naphthalene Methyl naphthalenes 8 Fused 6,6,5-ring systems Acenaphthene Fluorene Diphenylene Oxide Source: McNeil, a - 39 - The preliminary separations described in this section are necessary precursors to chromatographic techniques, such as gel, gas-liquid, thin layer, gravity fed column, and high performance liquid. The chromatographic methods, in conjuction with other analytical tools used to characterize and identify the compounds in pitch, will be described in detail in Chapter IV. - 40 - II - ENVIRONMENTAL EXPOSURE FACTORS: ASPHALT A. Production and Consumption 1. Quantity produced Asphalt sales in the United States have increased from an estimated ten million tons in to somewhat over 34 million tons in (Asphalt Insti- tute, b). Asphalt, which constitutes 9 to 75 weight-percent of crude petroleum, represented percent of United States crude oil refinery yield in , only a slight increase since (Table II-l) (Nelson, ). Currently, paving represents seventy-eight percent of the asphalt market, roofing seventeen percent, and miscellaneous uses five percent (Figure II-l) (U.S. Bureau of Mines, ). The consumption of cutback and emulsified asphalts has changed little since , but the use of asphalt cements, which accounts for eighty percent of asphalt consumed, has increased steadily to over 22 million tons (U.S. Bureau of Mines, ). Exports of asphalt were 61 thousand tons in , 62 thousand tons in , 75 thousand tons in , and 58 thousand tons in Imports of asphalt, including native asphalts, amounted to million tons in , 2 million tons in , and less than 1 million tons in (U.S. Bureau of Mines, ). 2. Market trends Between and , annual U.S. asphalt production increased from 20 thousand tons to 3 million tons (Asphalt Institute, b). Annual production is * expected to increase from the current level of 30 million tons to over 40 million tons by (Predicasts, ). Under circumstances of diminished oil supplies, asphalt will be too valuable to use as a paving binder1, and will probably be replaced by Portland -'Personal communication, Walter Hubis, Gulf Mineral Resources, Denver, Colorado. - 41 - TASLE II-l UNITED STATES ASPHALT PRODUCTION AS PERCENT OF PETROLEUM REFINERY YIELD YEAR % ASPHALT 3,3 * * * * *Estimate Source: Nelson, - 42 - FIGURE II-l. ANNUAL DOMESTIC SALES OF ASPHALT BY MAJOR MARKETS 28 26 24 22 C/) £18 lie 12 10 8' 64 0 PAVING A ROOFING MISCELLANEOUS / A i i i i I i i i i I i i i i YEARS Source: U. S. Bureau of Mines, - 43 - cement-concrete, its only current competitor. The roofing market will con- tinue to receive its share of asphalt because no competitive substitute is available (Gerstle, ). With approximately six billion tons of asphalt covering roads, runways and parking lots of the United States, there may be a trend toward recycling aged asphalt. According to methods specified by Mendenhall ()t asphalt- aggregate mixtures can be reheated and rejuvenated without impairing the penetration characteristics or weakening the material. 3. Market prices In , the price of asphalt was nineteen dollars per ton. Until the early 's, the price per ton fluctuated between seventeen and twenty-one dollars. Between and , the price increased to twenty-eight dollars per ton and is expected to continue increasing (Krchma and Gagle, ). 4. Producers and distributors On January 1, , there were crude oil refineries in the United States with a combined distillation capacity of million barrels per day. Of these, refineries produced asphalt (U.S. Bureau of Mines, ). Economic considerations dicatate whether a petroleum residue will be processed as an asphalt product, heavy fuel oil or petroleum coke, or burned as fuel (Lewis, ). The period of greatest asphalt consumption occurs from July through October, with August as the month of greatest usage. Because production usually cannot meet demand during the peak season, asphalt is often stock- piled at the refinery or at bulk terminals which have been established to facilitate distribution to sites of paving and roofing material manufacture (Lewis, ). Asphalt is shipped from the refinery or bulk terminal by truck, barge or rail car. ' - - 44 - 5. Production methods Ninety-eight percent of asphalt used in the United States is derived from crude oil (Miles, ) , although not all crudes are good, or even adequate, sources of asphalt. In general, if a crude contains a residue (fraction boiling above °C (°F)) that has an API gravity below 35 and a Watson characterization factor of less than (alshamasislamicinstitute.com.pk naphthenic than paraffinic), it may be adequate for asphalt manufacture (Gary and Handwerk, ). The following information concerning processes for the recovery and refining of asphaltic residues is based on discussions by Jones (), Gary and Handwerk (), Corbett (), Ball (), Broome (), Sterba (), Thornton (), Oglesby () and the Asphalt Institute (, b). The United States petroleum industry makes 2, products, of which are asphalts (Table II-2) (Mantell, ). Asphalts from different crude oil stocks may vary inherently in properties such as temperature susceptibility (the amount of change is viscosity with change in temperature). Properties such as durability may also be altered appreciably by processing treatment and addition of fluxing oils or blending stocks. In the refining of petroleum, crude oil is first distilled at atmospheric pressure at temperatures up to ° to °C (° to °F) in order to separate it into intermediate fractions of specific boiling ranges. After lower boiling fractions such as gasoline, kerosine, and diesel oil are removed, the remaining "reduced" crude, or straight-run residue, is further distilled under vacuum to separate gas oil and lubricating oil sidestreams. The residue withdrawn from the vacuum tower may become propane deasphalting stock or be mixed with additional atmospheric residue for further distillation under vacuum. Sidestreams from this third distillation may be used as catalytic cracking feedstocks, while the - 45 - TABLE II PRODUCTS MANUFACTURED BY U.S. PETROLEUM INDUSTRY Class Number Asphalts Carbon blacks 5 Chemicals, solvents, misc. Cokes 4 Distillates (diesel fuels & light fuel oils) 27 Fuel gas 1 Gasolines 40 Gas turbine fuels 5 Greases Kerosines 10 Liquefied gases 13 Lubricating oils 1, Residual fuel oils 16 Rust preventives 65 Transformer and cable oils 12 Waxes White oils Source: Mantell, - 46 - asphaltic residue is removed from the tower bottom. Steam may be used during any of these distillation steps in order to improve vaporization and minimize coke formation in the apparatus. Propane deasphalting is a process for removing resins or asphaltic components from a viscous hydrocarbon fraction in order to recover lube or catalytic cracking stocks. The charge for solvent deasphalting is derived from atmospheric or vacuum distillation bottoms that are low in asphalt content. The process consists of a countercurrent liquid-liquid extraction under temperatures and pressures determined by the nature of the charge stock. The deasphalted oil solution is withdrawn from the tower top and the propane solvent is stripped and recycled. Asphalt may be subjected to some form of thermal cracking which breaks heavy oil fractions into lighter, less viscous fractions by applying heat and pressure in the absence of a catalyst. Coking, or delayed coking, is a severe form of cracking, at temperatures exceeding °C (°F), which con- verts a heavy residue into a weak coke suitable for use in the manufacture of carbon electrodes but not in metallurgical blast furnaces. Visbreaking, at temperatures ranging from ° to °C (° to °F), is a relatively mild treatment that results in little boiling point reduction but greatly lowered viscosity. Neither coking nor visbreaking yields asphaltic residues as does "thermal cracking," a process now supplanted by catalytic cracking for the production of gasoline (Corbett, ). Thermal asphalts result from a cracking process in which a heavy oil stock is heated to ° to °C (° to °F), then discharged into a reaction vessel under pressures up to psig. The cracked products are distilled, leaving an asphaltic resi- due '(Figure }. 1 alshamasislamicinstitute.com.pk-< 2 3 OLA. MK toa -M^ U9UIDASIHAUS Cbp iS5*- (MC) > CMLJLSlFft) MHIflTS FIGURE II REFINERY STEPS IN THE PRODUCTION OF ASPHALT - 48 - Straight-run asphalts may be "air-blown" in order to produce specification products with reduced volatile content and increased melting point (relative to the straight-run stock). The stock is preheated to Vto °C (°to °F) and air is forced through the hot flux at rates ranging from 15 to 50 cubic feet per minute per ton of asphalt charge. Air blowing is occasionally done in the presence of phosphorus pentoxide, ferric chloride or zinc chloride in order to shorten blowing time. The addition of the essentially non-recoverable "catalyst" in concentrations from to 3 percent results in a product with higher penetration for a given softening point. High ductility and improved temperature susceptibility are other advantages which lead to the use of "catalytic asphalts" in a variety of specialty base stocks. Asphalt cements make up eighty percent of the current asphalt market (U.S. Bureau of Mines, ). These are penetration grade asphalts derived from re- sidua of either vacuum distillation or propane deasphalting. They'may be air blown and may represent a mixture of base stocks. Asphalt cements, cut back with a petroleum solvent, axe either rapid-curing or medium-curing asphalts. Road oils (slow-curing) are the least uniform of the liquid asphalts and may in fact be directly distilled rather than cutback. Asphalt emulsions are normally produced from penetration asphalt cements. Depending on their intended use, asphalts may be liquefied in various ways (Oglesby, ; Day and Herbert, ; Mertens and Borgfeldt, ). Blending of cutback asphalts and emul- sified asphalts is not necessarily a refinery process (Figure II-2). Diluting an asphalt cement with a lighter petroleum distillate yields a product with lower viscosity. Upon evaporation of the solvent, the cured asphalt has approximately the same penetration grade as its parent asphalt ce- ment. The base stock may be directly blended or stored in tanks which range - 49 - in size from 25, to , barrels. The stock is delivered to a blend tank and mixed with a measured volume of diluent- Rapid-curing cutbacks (RC) contain a diluent (gasoline or naphtha type) with a boiling range of ° to °C (° to °F). The base asphalt will vary from 70 to penetration in order to leave a cured asphalt of penetration. The least viscous grade (RC) can be poured at room tempera- ture. Middle-curing cutbacks (MC) use a kerosine type diluent with a boiling range of ° to °C (° to °F). This cutback is more versatile than the others, with good wetting properties on fine aggregates and a moder- ate evaporation rate. The base asphalt will vary from 70 to penetration to leave a cured residue of to penetration. MC and MC can be poured at room temperature. MC can contain as much as 40 percent by volume diluent. The most viscous grade, MC, may have as little as 18 percent solvent and usually must be warmed before use. Slow-curing asphalts (SC), often referred to as "road oils," may be refined directly to grade rather than consisting of an asphalt cement plus diluent. They are the least uniform in composition. Heavy diesel fuel, overhead gas oils or cycle stocks from other processes may be used as solvents. The lightest grade (SC) has the consistency of light syrup. The heaviest grade (SC) will scarcely deform at room temperature, and is slightly less viscous than the softest asphalt cement ( to penetration). Aqueous emulsions in which the asphalt content is 55 to" 70 percent by weight are another form of liquefied asphalt. The three emulsion grades - rapid-setting, medium-setting, and slow-setting - can be applied at normal temperatures. The asphalt cures by evaporation of the water rather than of a petroleum solvent, thus avoiding hydrocarbon emissions. Emulsions can be - 50 - applied on wet aggregates and generally are ready to resist traffic damage sooner than cutbacks. The equipment needed for mixing and application is simpler and less expensive than that required for other asphalt products. Before , anionic emulsions vrere the only type commercially available. Saponified fatty and resinous acids or saponified tallow derivatives were the emulsifying agents used with an asphalt cement of to penetration. Cationic emulsions, using a quaternary ammonium compound as an emulsifying agent^ are now available and can be used with a wide variety of mineral ag- gregates. They adhere well to wet aggregates, and can be used under condi- tions of high humidity or low air temperatures. B. Uses Asphalt is a readily adhesive, highly waterproof, durable thermoplastic material, resistant to the action of most acids, alkalis and salts. These properties are utilized in a wide variety of applications. 1. Major uses a. Paving CD Production and consumption The Standard Industrial Classification (SIC) category SIC includes establishments manufacturing asphalt (in some cases, coal tar) paving mixtures as well as blocks of asphalt, coal tar, or creosoted wood. Of these , had seventy-five percent specialization (defined as the ratio of all primary products to the total of primary plus secondary products). About 10, production workers are classified under SIC (U.S. Bureau of Census, ) (Table II-3). The top ten paving mix producers according to production figures are listed in Table II The value of all paving mixtures and blocks shipments classified under SIC was $ million in , $ million in and $ million in The amount of asphalt of less than penetration consumed in by - 51 - TABLE II EMPLOYMENT SIZE OF ESTABLISHMENTS (SIC ) PAVING MATERIALS Total Establishments with an average of 1 to 4 employees 5 to 9 10 to 19 20 to 49 50 to 99 to to to to 2, 34 13 2 1 1 Source: U. S. Bureau of Census, TABLE II THE TOP TEN PAVING MIX PRODUCERS: Producer and home state The General Crushed Stone Co., Pa. L.M. Pike & Sons, Inc., N.H. The Interstate Amiesite Corp., Pa. Asphalt Products Corp., S.C. Broce Construction Co., Okla. Associated Sand & Gravel Co., Inc., Wash. Ajax Paving Industries, Mich. Western Engineering Co., la. Dickerson, Inc., N.C. Highway Materials, Inc., Pa. Plant mix tonnage 1,, 1,, 1,, , , , , , , , Source: Roads and Streets, - 52 - the paving industry was 4,, tons with a delivered cost of $ million. In , 5,, tons were consumed at a cost of $ million (U.S. Bureau of Census, ). (2) Materials Currently, ninety-four percent (over million miles) of the paved surfaces, in the United States are bituminous (Oglesby, ). These bituminous surfaces range from dirt surfaces lightly sprayed with liquid asphalt to high- grade asphalt cement pavements. A finished paving mix consists of about six percent asphalt cement and ninety-four percent mineral aggregates. In addition to asphalt cement, a variety of cutback and emulsified asphalts are used to treat or finish roads (See Section II.A for descriptions of asphalt cements, cutbacks and emulsions) Approximately million tons of mineral aggregates are consumed annually for all aspects of highway construction. Slag, broken stone, gravel and sand, the aggregates most commonly used, constitute 75% by volume of a finished paving mix. Because aggregates vary greatly in composition, strength, porosity and surface roughness, specifications and tests have been developed to insure cer- tain minimum standards (Oglesby, ). Experimental pavements using asphalt-rubber mixtures have been laid in many states. Rubber enhances the coefficient of friction, improves the stability of paving mixtures, and reduces temperature susceptibility and brittleness, as well as imparting greater elasticity and extending pavement life (Oglesby, ). Other experimental pavements have been laid using an epoxy resin and asphalt binder which is resitant to wear, heat and the solvent effects of fuel (Hoiberg, ) . - 53 - (3) Process descriptions Hot mix plants General information in the following section was obtained from Oglesby (). Although road surfaces can be treated with either hot or cold applied asphalt, hot treatments are the most common. It is estimated that there are pav- ing plants of all sizes in the United States; plants with a capacity of tons per hour of finished mix are common near most large cities (Puzinauskas and Corbett, ). Asphalt is loaded at the refinery or bulk terminal at elevated temperatures into steam heated tank cars, trucks or drums and transported to the hot mix plant. The asphalt, stored in large heated underground tanks, can be pumped directly to the platform on which finished asphalt-aggregate mixtures are produced. The mineral aggregates are sent through the drier, a firebrick lined steel cylinder, to drive off moisture and heat to a mixing temperature of ° to °C (° to °F). The hot aggregates are segregated by size through shaking screens. In batch-mixing processes (the most common), aggregates and the asphalt binder are mixed by revolving blades in pug mills that can reach capacities of sixteen tons or more. The finished mix is deposited into waiting'trucks and taken to the job site. High capacity plants use a process whereby hot binder is introduced directly into the drier, thus insuring continuous output of finished product. Exposure of the binder to drier conditions does not seem to accelerate its aging, and the problem of dust from fine aggregates is substantially reduced. - 54 - Cold mix plants Cold mix plants are similar to hot mix plants in operation, except that the aggregates are cooled before being coated with a naphtha liquefier. The coated aggregates are mixed with hot asphalt binder to form the finished pav- ing product. Such cold mix products are not in common use. Paving In the past, all placing and leveling of hot asphalt was performed manually. Self-propelled finishing machines have largely supplanted manual operations, although small jobs, especially patching operations in cities, still rely on hand equipment. The hot aggregate-asphalt mixture, which is transported to the job site in dump trucks, is unloaded, spread and tamped, usually with one machine. Final tamping is done by large, smooth-wheeled rollers. Road mix processing, still used on side roads, is performed with a single machine that picks up aggregates, either freshly laid or pulverized from the old surface, mixes them with asphalt cement and spreads the new pavement. Surface treatment Road surfaces are treated with a pressurized distributor truck ( to gallon capacity) from which liquid asphalt is forced through a spray bar approximately twenty feet long. Several types of surface treatments may be used: 1) Dust palliatives: light slow-curing road oil or slow-setting emulsions applied at 79°C U75°F). 2) Prime (tack) coats: light medium-curing cutbacks or light road tar or slow-setting emulsions. 3) Armor coats on macadam or low quality concrete: varies with surface - 55 - 4) Seal coats: Hand or crushed stone mixed with a slow-setting road oil applied to damp pavement. Slow-setting emulsions are sprayed on to rejuvenate surfaces. Proper temperatures of application, as well as ambient temperature, are fundamental to good asphalt performance. State highway departments specify minimum air temperatures for laying asphalt ranging from 0°C (32°F) to °C (60°F), the usual being °C (40°F). (Table II-5) . b. Roofing (1) Production and consumption In , there were plants in classification SIC ; which includes establishments that manufacture asphalt and coal tar saturated felts in roll or shingle form, as well as roofing cements and coatings (U.S. Office of Management and Budget, ). Of the total , had seventy-five percent or more specialization (U.S. Bureau of Census, ). (Specialization is defined as the ratio of all primary products to the total of primary plus secondary products). There were 11, production workers classified under SIC in (U.S. Bureau of Census, ) (Table II- | KiB/s, done.
Resolving deltas: % (1/1), done.
Tapped formulae ( files, M)
Command (Confirm):$ brew tap
Result:==> Auto-updated Homebrew!
Updated Homebrew from 03ee to 6e
Updated 1 tap (homebrew/core).
==> Updated Formulae
abcm2ps cake git-imerge libyaml plowshare tor
agedu discount haskell-stack mas pod2man
==> Deleted Formulae
aget sgfutils
homebrew/core
homebrew/python
homebrew/science
Command (installing hdf5 and opencv):$ brew install hdf5 opencv
Result:==> Installing hdf5 from homebrew/science
==> Installing dependencies for homebrew/science/hdf5: autoconf, automake, libtool
==> Installing homebrew/science/hdf5 dependency: autoconf
==> Downloading alshamasislamicinstitute.com.pk
######################################################################## %
==> Pouring alshamasislamicinstitute.com.pk
==> Caveats
Emacs Lisp files have been installed to:
/usr/local/share/emacs/site-lisp/autoconf
==> Summary
🍺 /usr/local/Cellar/autoconf/ 70 files, M
==> Installing homebrew/science/hdf5 dependency: automake
==> Downloading alshamasislamicinstitute.com.pk
######################################################################## %
==> Pouring alshamasislamicinstitute.com.pk
🍺 /usr/local/Cellar/automake/ files, M
==> Installing homebrew/science/hdf5 dependency: libtool
==> Downloading alshamasislamicinstitute.com.pk
######################################################################## %
==> Pouring libtool_alshamasislamicinstitute.com.pk
==> Caveats
In order to prevent conflicts with Apple's own libtool we have prepended a "g"
so, you have instead: glibtool and glibtoolize.
==> Summary
🍺 /usr/local/Cellar/libtool/_1: 70 files, M
==> Installing homebrew/science/hdf5
==> Downloading alshamasislamicinstitute.com.pk
######################################################################## %
==> autoreconf -fiv
==> ./configure --prefix=/usr/local/Cellar/hdf5/ --enable-production --enable-debug=no --with-zlib=/usr --with-szlib=/usr/local/opt/szip --enable-stat
==> make
==> make install
🍺 /usr/local/Cellar/hdf5/ files, M, built in 3 minutes 37 seconds
==> Installing opencv from homebrew/science
==> Installing dependencies for homebrew/science/opencv: cmake, eigen, ilmbase, openexr, pkg-config
==> Installing homebrew/science/opencv dependency: cmake
==> Downloading alshamasislamicinstitute.com.pk
######################################################################## %
==> Pouring alshamasislamicinstitute.com.pk
==> Caveats
Emacs Lisp files have been installed to:
/usr/local/share/emacs/site-lisp/cmake
==> Summary
🍺 /usr/local/Cellar/cmake/ 2, files, M
==> Installing homebrew/science/opencv dependency: eigen
==> Downloading alshamasislamicinstitute.com.pk
######################################################################## %
==> Pouring alshamasislamicinstitute.com.pk
🍺 /usr/local/Cellar/eigen/ files, M
==> Installing homebrew/science/opencv dependency: ilmbase
==> Downloading alshamasislamicinstitute.com.pk
######################################################################## %
==> Pouring alshamasislamicinstitute.com.pk
🍺 /usr/local/Cellar/ilmbase/ files, M
==> Installing homebrew/science/opencv dependency: openexr
==> Downloading alshamasislamicinstitute.com.pk
######################################################################## %
==> Pouring alshamasislamicinstitute.com.pk
🍺 /usr/local/Cellar/openexr/ files, M
==> Installing homebrew/science/opencv dependency: pkg-config
==> Downloading alshamasislamicinstitute.com.pk
######################################################################## %
==> Pouring pkg-config_alshamasislamicinstitute.com.pk
🍺 /usr/local/Cellar/pkg-config/_2: 10 files, K
==> Installing homebrew/science/opencv
==> Downloading alshamasislamicinstitute.com.pk
==> Downloading from alshamasislamicinstitute.com.pk
######################################################################## %
==> cmake .. -DCMAKE_C_FLAGS_RELEASE=-DNDEBUG -DCMAKE_CXX_FLAGS_RELEASE=-DNDEBUG -DCMAKE_INSTALL_PREFIX=/usr/local/Cellar/opencv/_3 -DCMAKE_BUILD_TYPE
==> make
Last 15 lines from /Users/USERNAME/Library/Logs/Homebrew/opencv/make:
[ 15%] Building CXX object modules/video/CMakeFiles/opencv_alshamasislamicinstitute.com.pk
cd /tmp/opencvtnphw6/opencv/macbuild/modules/video && /usr/local/Homebrew/Library/Homebrew/shims/super/clang++ -DCVAPI_EXPORTS -I/tmp/opencvtnphw6/opencv/modules/video/perf -I/tmp/opencvtnphw6/opencv/modules/video/include -I/tmp/opencvtnphw6/opencv/modules/calib3d/include -I/tmp/opencvtnphw6/opencv/modules/features2d/include -I/tmp/opencvtnphw6/opencv/modules/highgui/include -I/tmp/opencvtnphw6/opencv/modules/imgproc/include -I/tmp/opencvtnphw6/opencv/modules/flann/include -I/tmp/opencvtnphw6/opencv/modules/core/include -I/tmp/opencvtnphw6/opencv/modules/ts/include -I/tmp/opencvtnphw6/opencv/macbuild/modules/video -I/tmp/opencvtnphw6/opencv/modules/video/src -I/tmp/opencvtnphw6/opencv/modules/video/test -I/tmp/opencvtnphw6/opencv/macbuild -isystem /usr/local/include/eigen3 -fsigned-char -W -Wall -Werror=return-type -Werror=address -Werror=sequence-point -Wformat -Werror=format-security -Wmissing-declarations -Wmissing-prototypes -Wstrict-prototypes -Wundef -Winit-self -Wpointer-arith -Wshadow -Wsign-promo -Wno-narrowing -Wno-delete-non-virtual-dtor -Wno-unnamed-type-template-args -Wno-array-bounds -Wno-aggressive-loop-optimizations -fdiagnostics-show-option -Wno-long-long -Wno-semicolon-before-method-body -fno-omit-frame-pointer -msse -msse2 -mavx -DNDEBUG -DNDEBUG -isysroot /Applications/alshamasislamicinstitute.com.pk -fPIC -o CMakeFiles/opencv_alshamasislamicinstitute.com.pk -c /tmp/opencvtnphw6/opencv/modules/video/src/alshamasislamicinstitute.com.pk
[ 16%] Building CXX object modules/video/CMakeFiles/opencv_alshamasislamicinstitute.com.pk
cd /tmp/opencvtnphw6/opencv/macbuild/modules/video && /usr/local/Homebrew/Library/Homebrew/shims/super/clang++ -DCVAPI_EXPORTS -I/tmp/opencvtnphw6/opencv/modules/video/perf -I/tmp/opencvtnphw6/opencv/modules/video/include -I/tmp/opencvtnphw6/opencv/modules/calib3d/include -I/tmp/opencvtnphw6/opencv/modules/features2d/include -I/tmp/opencvtnphw6/opencv/modules/highgui/include -I/tmp/opencvtnphw6/opencv/modules/imgproc/include -I/tmp/opencvtnphw6/opencv/modules/flann/include -I/tmp/opencvtnphw6/opencv/modules/core/include -I/tmp/opencvtnphw6/opencv/modules/ts/include -I/tmp/opencvtnphw6/opencv/macbuild/modules/video -I/tmp/opencvtnphw6/opencv/modules/video/src -I/tmp/opencvtnphw6/opencv/modules/video/test -I/tmp/opencvtnphw6/opencv/macbuild -isystem /usr/local/include/eigen3 -fsigned-char -W -Wall -Werror=return-type -Werror=address -Werror=sequence-point -Wformat -Werror=format-security -Wmissing-declarations -Wmissing-prototypes -Wstrict-prototypes -Wundef -Winit-self -Wpointer-arith -Wshadow -Wsign-promo -Wno-narrowing -Wno-delete-non-virtual-dtor -Wno-unnamed-type-template-args -Wno-array-bounds -Wno-aggressive-loop-optimizations -fdiagnostics-show-option -Wno-long-long -Wno-semicolon-before-method-body -fno-omit-frame-pointer -msse -msse2 -mavx -DNDEBUG -DNDEBUG -isysroot /Applications/alshamasislamicinstitute.com.pk -fPIC -o CMakeFiles/opencv_alshamasislamicinstitute.com.pk -c /tmp/opencvtnphw6/opencv/modules/video/src/alshamasislamicinstitute.com.pk
[ 16%] Building CXX object modules/video/CMakeFiles/opencv_alshamasislamicinstitute.com.pk
cd /tmp/opencvtnphw6/opencv/macbuild/modules/video && /usr/local/Homebrew/Library/Homebrew/shims/super/clang++ -DCVAPI_EXPORTS -I/tmp/opencvtnphw6/opencv/modules/video/perf -I/tmp/opencvtnphw6/opencv/modules/video/include -I/tmp/opencvtnphw6/opencv/modules/calib3d/include -I/tmp/opencvtnphw6/opencv/modules/features2d/include -I/tmp/opencvtnphw6/opencv/modules/highgui/include -I/tmp/opencvtnphw6/opencv/modules/imgproc/include -I/tmp/opencvtnphw6/opencv/modules/flann/include -I/tmp/opencvtnphw6/opencv/modules/core/include -I/tmp/opencvtnphw6/opencv/modules/ts/include -I/tmp/opencvtnphw6/opencv/macbuild/modules/video -I/tmp/opencvtnphw6/opencv/modules/video/src -I/tmp/opencvtnphw6/opencv/modules/video/test -I/tmp/opencvtnphw6/opencv/macbuild -isystem /usr/local/include/eigen3 -fsigned-char -W -Wall -Werror=return-type -Werror=address -Werror=sequence-point -Wformat -Werror=format-security -Wmissing-declarations -Wmissing-prototypes -Wstrict-prototypes -Wundef -Winit-self -Wpointer-arith -Wshadow -Wsign-promo -Wno-narrowing -Wno-delete-non-virtual-dtor -Wno-unnamed-type-template-args -Wno-array-bounds -Wno-aggressive-loop-optimizations -fdiagnostics-show-option -Wno-long-long -Wno-semicolon-before-method-body -fno-omit-frame-pointer -msse -msse2 -mavx -DNDEBUG -DNDEBUG -isysroot /Applications/alshamasislamicinstitute.com.pk -fPIC -o CMakeFiles/opencv_alshamasislamicinstitute.com.pk -c /tmp/opencvtnphw6/opencv/modules/video/src/alshamasislamicinstitute.com.pk
[ 16%] Building CXX object modules/video/CMakeFiles/opencv_alshamasislamicinstitute.com.pk
cd /tmp/opencvtnphw6/opencv/macbuild/modules/video && /usr/local/Homebrew/Library/Homebrew/shims/super/clang++ -DCVAPI_EXPORTS -I/tmp/opencvtnphw6/opencv/modules/video/perf -I/tmp/opencvtnphw6/opencv/modules/video/include -I/tmp/opencvtnphw6/opencv/modules/calib3d/include -I/tmp/opencvtnphw6/opencv/modules/features2d/include -I/tmp/opencvtnphw6/opencv/modules/highgui/include -I/tmp/opencvtnphw6/opencv/modules/imgproc/include -I/tmp/opencvtnphw6/opencv/modules/flann/include -I/tmp/opencvtnphw6/opencv/modules/core/include -I/tmp/opencvtnphw6/opencv/modules/ts/include -I/tmp/opencvtnphw6/opencv/macbuild/modules/video -I/tmp/opencvtnphw6/opencv/modules/video/src -I/tmp/opencvtnphw6/opencv/modules/video/test -I/tmp/opencvtnphw6/opencv/macbuild -isystem /usr/local/include/eigen3 -fsigned-char -W -Wall -Werror=return-type -Werror=address -Werror=sequence-point -Wformat -Werror=format-security -Wmissing-declarations -Wmissing-prototypes -Wstrict-prototypes -Wundef -Winit-self -Wpointer-arith -Wshadow -Wsign-promo -Wno-narrowing -Wno-delete-non-virtual-dtor -Wno-unnamed-type-template-args -Wno-array-bounds -Wno-aggressive-loop-optimizations -fdiagnostics-show-option -Wno-long-long -Wno-semicolon-before-method-body -fno-omit-frame-pointer -msse -msse2 -mavx -DNDEBUG -DNDEBUG -isysroot /Applications/alshamasislamicinstitute.com.pk -fPIC -o CMakeFiles/opencv_alshamasislamicinstitute.com.pk -c /tmp/opencvtnphw6/opencv/modules/video/src/video_alshamasislamicinstitute.com.pk
[ 16%] Linking CXX shared library ../../lib/libopencv_alshamasislamicinstitute.com.pk
cd /tmp/opencvtnphw6/opencv/macbuild/modules/video && /usr/local/Cellar/cmake//bin/cmake -E cmake_link_script CMakeFiles/opencv_alshamasislamicinstitute.com.pk --verbose=1
/usr/local/Homebrew/Library/Homebrew/shims/super/clang++ -fsigned-char -W -Wall -Werror=return-type -Werror=address -Werror=sequence-point -Wformat -Werror=format-security -Wmissing-declarations -Wmissing-prototypes -Wstrict-prototypes -Wundef -Winit-self -Wpointer-arith -Wshadow -Wsign-promo -Wno-narrowing -Wno-delete-non-virtual-dtor -Wno-unnamed-type-template-args -Wno-array-bounds -Wno-aggressive-loop-optimizations -fdiagnostics-show-option -Wno-long-long -Wno-semicolon-before-method-body -fno-omit-frame-pointer -msse -msse2 -mavx -DNDEBUG -DNDEBUG -isysroot /Applications/alshamasislamicinstitute.com.pk -dynamiclib -Wl,-headerpad_max_install_names -compatibility_version -current_version -o ../../lib/libopencv_videodylib -install_name /tmp/opencvtnphw6/opencv/macbuild/lib/libopencv_videodylib CMakeFiles/opencv_alshamasislamicinstitute.com.pk CMakeFiles/opencv_alshamasislamicinstitute.com.pk CMakeFiles/opencv_alshamasislamicinstitute.com.pk CMakeFiles/opencv_alshamasislamicinstitute.com.pk CMakeFiles/opencv_alshamasislamicinstitute.com.pk CMakeFiles/opencv_alshamasislamicinstitute.com.pk CMakeFiles/opencv_alshamasislamicinstitute.com.pk CMakeFiles/opencv_alshamasislamicinstitute.com.pk CMakeFiles/opencv_alshamasislamicinstitute.com.pk CMakeFiles/opencv_alshamasislamicinstitute.com.pk CMakeFiles/opencv_alshamasislamicinstitute.com.pk ../../lib/libopencv_imgprocdylib ../../lib/libopencv_coredylib
cd /tmp/opencvtnphw6/opencv/macbuild/modules/video && /usr/local/Cellar/cmake//bin/cmake -E cmake_symlink_library ../../lib/libopencv_videodylib ../../lib/libopencv_videodylib ../../lib/libopencv_alshamasislamicinstitute.com.pk
[ 16%] Built target opencv_video
make[1]: *** [modules/highgui/CMakeFiles/opencv_alshamasislamicinstitute.com.pk] Error 2
make: *** [all] Error 2
READ THIS: alshamasislamicinstitute.com.pk
If reporting this issue please do so at (not Homebrew/brew):
alshamasislamicinstitute.com.pk
These open issues may also help:
opencv: fix stable on sierra and with xcode 8 sdk alshamasislamicinstitute.com.pk
opencv: fix build with vtk alshamasislamicinstitute.com.pk
OpenCV install fails on MacOS Sierra () at 16% alshamasislamicinstitute.com.pk
opencv: alshamasislamicinstitute.com.pksfiedLinkError alshamasislamicinstitute.com.pk
opencv modify libstdc++ to libc++ alshamasislamicinstitute.com.pk
brew install opencv --with-ffmpeg fails alshamasislamicinstitute.com.pk
OpenCV 3 macOS Sierra QTKit not found build issue alshamasislamicinstitute.com.pk
Cannot build OpenCV with Java alshamasislamicinstitute.com.pk
Brew install opencv fails at 99% alshamasislamicinstitute.com.pk
OpenCV Java Link Problem alshamasislamicinstitute.com.pk
OpenCV and OpenCV3 fail to build with ximea camera support alshamasislamicinstitute.com.pk
opencv fail to build with ffmpeg or vtk alshamasislamicinstitute.com.pk
opencv failed to build against QuickTime on alshamasislamicinstitute.com.pk
Installing OpenCV attempts to reinstall gcc alshamasislamicinstitute.com.pk
ISBN (hardback : alk. paper)
Command (Installing pyenv):
$ brew install pyenv
Result:
==> Using the sandbox
==> Downloading alshamasislamicinstitute.com.pk
==> Downloading from alshamasislamicinstitute.com.pk
######################################################################## %
==> Caveats
To use Homebrew's directories rather than ~/.pyenv add to your profile:
export PYENV_ROOT=/usr/local/var/pyenv
To enable shims and autocompletion add to your profile:
if which pyenv > /dev/null; then eval "$(pyenv init -)"; fi
==> Summary
🍺 /usr/local/Cellar/pyenv/ files, M, built in 10 seconds
Command (Installing Anaconda):
$ pyenv install --list DDC /dc23 LC record available at alshamasislamicinstitute.com.pk Visit the Taylor & Francis Web site at alshamasislamicinstitute.com.pk and the CRC Press Web site at alshamasislamicinstitute.com.pk
Preface Owing to their higher chemical and impact resistance in addition to their superior mechanical and thermal properties, biopolymers have become “the material of choice” in healing therapies. A wide range of different polymers are available for multiple medical applications; so much so that it is expected that the use of glass and metals in therapeutic devices will decline over the next few years while the use of polymers will increase. Although this subject has long been an important area of research for biochemists and physicists, engineers, pharmacists and physicians are now taking a keen interest in it. Polymers’ versatility and, the scientist’s ability to engineer and customize their physical, chemical and biological properties to match the requirements of the varied and specific medical applications are the keys to their increasing use. Applications, just to name a few, include medical tubing, controlled drug delivery and wound management (e.g., adhesives, sutures, lubricants and surgical meshes), orthopedic devices (screws, pins, and rods), dental materials (filler after a tooth extraction) and tissue engineering. This book has been devised so as to offer an overview of currently “hot” topics in this field. We, as editors of this book, have selected reputed scientists whose research and ideas have significantly contributed to progress in this area. Recognizing that there are different approaches to biopolymers is not enough. Experiments have been the centerpiece of the scientific method since Galileo. However, the power of modern computers has made computational approaches a key aspect in all kind of scientific research. This diversity needs to be preserved and promoted. Given that different approaches emphasize different aspects and offer different perspectives allows us to have a fuller, more balanced understanding of the complex entity called biopolymers. Especially in the long term, a discipline that contains a variety of different approaches can cope with a changing world better than others characterized by only a single way. For this reason, in this book, we have made special emphasis to both disciplines are reflected. The different classes of advanced materials based on biopolymer systems including biopolymer nano-fibers and nano-tubes, smart nano-assemblies for drug and gene delivery, ordered supramolecular systems as well as novel composite materials based on nanoparticles and biopolymers, are covered in the book. In the first nine chapters of this monograph a detailed account of the present status of biopolymers it is provided and highlighted the recent developments made by leading research groups.
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Biopolymers for Medical Applications
Since the requirements of medical applications are variable, there is no ideal biopolymer. Therefore, new materials are developed based on the desired properties for very specific purposes. This means that in addition to materials, processing techniques and computational tools are inherent in this process. Thus, the book is completed with five chapters featuring concepts of modeling and simulation of biological systems, drug-target interaction analysis via perturbation theory, guided self-assembly by structural DNA nanotechnology, dynamic examination of molecular drug-protein binding and selective imprinted xerogels. In chapters ranging from 10 to 14, the recent advances of mathematical and theoretical models, applied to find an accurate representation of the complexity of biological systems, have been highlighted. It shows how reasonably simple mathematics can be combined with different models to draw exciting conclusions. Interconnections are made between diverse biological examples and a variety of discrete and continuous equation models. On the other hand, the constant progresses in both computer power and algorithm design, makes highly promising the future of computer-aided drug design; thus, with every passing day molecular dynamics simulations, the science of simulating the motions of a system of particles, play an increasingly important role. The three final chapters of this book discusses the atomistic computer simulations of biopolymers (i.e., a protein), receptors and their associated small-molecule ligands that can act in drug discovery, including the identification of cryptic or allosteric binding sites, the enhancement of traditional virtual-screening methodologies, and the direct prediction of small-molecule binding energies. The limitations of current simulation methodologies, comprising the high computational costs and approximations of molecular forces required were also discussed. The variety of topics covered in this book aims to provide a comprehensive overview of the field of biopolymers for medical applications. Besides its usefulness for academics and industrial researchers, the book is of humanistic inspiration, revealing the special sensitivity of authors who have made a great effort to uproot the palisades that traditionally separate advanced professionals from those unfamiliar with these subjects. Indeed, we hope to convince the latter of the many new research opportunities in this field. Last, but not least, the fact that we are writing this preface is, without any doubt, due to the cooperation, support, and understanding of all the contributors who invested a considerable amount of time in helping this book to reach fruition. We have been privileged to coordinate the efforts of many talented scientists. Juan M. Ruso and Paula V. Messina
Contents Preface 1. Biopolymers in Regenerative Medicine: Overview, Current Advances and Future Trends Juan M. Ruso and Paula V. Messina
v 1
2. Application of Natural, Semi-Synthetic, and Synthetic Biopolymers used in Drug Delivery Systems Design Javier Sartuqui, Noelia L. D’Elía, A. Noel Gravina and Luciano A. Benedini
38
3. Polysaccharide Based Biomaterials Narendra Reddy and Divya Natraj
66
4. Biopolymers in the Prevention of Dental Erosion Javier Sotres
5. Drug Carriers by Liposomes Physically Coated with Peptides Qiufen Zhang, Cuicui Su, Nan Wang and Dehai Liang
6. Biopolymers for In Vitro Tissue Model Biofabrication Aleksander Skardal
7. Medical Application of Polyampholytes Kazuaki Matsumura, Robin Rajan, Sana Ahmed and Minkle Jain
8. Biomedical Applications of Recombinant Proteins and Derived Polypeptides Francisco Javier Arias, Sergio Acosta-Rodríguez, Tatjana Flora and Sofía Serrano-Dúcar
9. Cellulose Nanofibers for Biomedical Applications Marité Cardenas and Anna J. Svagan Modelling and Simulation of Biological Systems in Medical Applications S. Balaji
viii
Biopolymers for Medical Applications
High-Order Perturbation Theory Models of Drug-Target Interactomes for Proteins Expressed on Networks of Hippocampus Brain Region of Alzheimer Disease Patients Francisco J. Romero-Durán, Edgar Lopez-Castro, Xerardo García-Mera and Humberto González-Díaz
Structural Modeling for DNA and RNA Bindings to Breast Anticancer Drug Tamoxifen and Its Metabolites H. A. Tajmir-Riahi, P. Bourassa and T. J. Thomas
Dynamic Analysis of Backbone-Hydrogen-Bond Propensity for Protein Binding and Drug Design C. A. Menéndez, S. R. Accordino, J. A. Rodriguez Fris, D. C. Gerbino and G. A. Appignanesi
Molecular Dynamics Simulations and Comparison of Two New and High Selective Imprinted Xerogels Riccardo Concu, Manuel Azenha and M. Natalia D. S. Cordeiro
Index
1 Biopolymers in Regenerative Medicine: Overview, Current Advances and Future Trends Juan M. Ruso1 and Paula V. Messina2,* Introduction Overview An ambition of regenerative medicine is the in vivo restoration or, alternatively, the in vitro generation of a complex functional organ consisting of a scaffold made out of synthetic or natural materials that has been loaded with living cells (Melek , ; Terzic and Nelson ). Mammalian cells respond in vivo to the biological stimulus from the surrounding environment, which is structured by nanometer-scaled components. Consequently, materials intended for the reconstruction of the human body have to reproduce the correct signals that guide the cells towards a desirable behavior (Patel ), in this sense, polímeros are currently investigated. Exciting advances based on application of the self-assembled biocompatible polymeric scaffolds for regeneration of tissues and organs were systematically explored and described in detail in the literature (Niaounakis ; Kalia and Avérous ;
Soft Matter and Molecular Biophysics Group, Department of Applied Physics, University of Santiago de Compostela, Santiago de Compostela, , Spain. 2 Department of Chemistry, Universidad Nacional del Sur, , Bahía Blanca, Argentina. INQUISURCONICET. * Corresponding author: [emailprotected] 1
2 Biopolymers for Medical Applications Imam et al. ; Atala and Allickson ; Dutta and Dutta ). Their effectiveness in providing supports for cell growth and development in various tissues and enhancing or mimicking an extracellular matrix (ECM) has been carefully analyzed (Nedovic and Willaert ; Hunt and Grover ). Clinical results showing the benefits of such treatments, as well as their limitations are explored and novel polymer formulas, for coating implants, stents, and other medical devices, have been developed (Plackett ; Jagur‐Grodzinski ; Tseng et al. ; Weber et al. ; Mani et al. ; Jung et al. a; Jung et al. b; De Vicente et al. ; Ferreira et al. ; Schwarz et al. ). Furthermore, the application of these polymeric materials in tissue engineering of cartilage and bones are explored (Stevens ; Bessa et al. ; Yilgor et al. ; Beltrán et al. ). An innovative and transiently evolving biotechnological subfield, the synthetic biology, attempts to insert enhanced functionality and response to biomaterials by the use of recombinant polymer biotechnology to include genetic units that are not typically present on them (Hammer and Kamat ). Consistently, synthetic membranes from bio-inspired block co-polypeptides developed into another emerging area of interest (Bellomo et al. ). This chapter offers a structural synopsis of biopolymers and discusses their physicochemical characteristics, organization—properties relationship, applications, and limitations. The classification of polymers is briefly mentioned and their chemical structures are provided. Biopolymers that are hydrolytically labile and erode (biodegradable polymers) as well as those that are bio-inert and remain unchanged after implantation (non-degradable polymers) are considered. Some synthetic derivatives of natural materials are briefly discussed where appropriate. It is the authors’ intention to provide a thorough general idea of the biopolymers’ applications to regenerative medicine. This chapter tends to be a guide for further reading on most biopolymer classifications and properties.
The basics: biopolymer definition and classification There is no a general consensus in literature and patents about the exact definition of the generic terms degradable, biodegradable, bio-based, compostable, biopolymer, and bioplastic; they appear to have multiple and overlapping meanings. We have presented here a brief description of each definition highlighting their differences. For more information consult Niaounakis (). Degradable is a general term used to describe all polymeric materials that disintegrate by a range of physical and chemical processes, while biodegradable is a term focused on the polymer’s functionality, that is, “biodegradability”. This term is applied to those materials that will degrade, within a specific period of time and environment, under the action of microorganisms such as molds, fungi, and bacteria. According to the withdrawn standard ASTM D (ASTM Internationa, ), the terms biodegradable polymers specifically refer to polymers that are “capable of undergoing decomposition into carbon dioxide, methane, water, inorganic compounds, or biomass in which the predominant mechanism is the enzymatic action of microorganisms that can be measured by standard tests, over a specific period of time, reflecting available disposal conditions.” On the other hand, the Japan Bioplastics Association
Biopolymers in Regenerative Medicine 3
(JBPA) defines the term biodegradability as the characteristics of material that can be microbiologically degraded to the final products of carbon dioxide and water, which, in turn, are recycled in nature (Niaounakis ). Biodegradation should be differentiated from disintegration, which simply implies the breakdown of a material into small and separate fragments. Biodegradable polymers can be certified according to any of the following legally binding international standards: ISO , EN , EN , ASTM D (Niaounakis ). As a consequence of this classification, a polymer may be degradable but not biodegradable. Bio-based is a word focused on the origin of raw materials, and it’s applied to polymers obtained from renewable resources. In practical terms, a bio-based polymer is not per se an ecological polymer; this is subjected to a variety of concerns, including the material origin, the production method, and finally how such material is disposed at the end of its useful life. Accordingly to these classifications, not every bio-based polymer is biodegradable, e.g., bio-based polyethylene or polyamide 11; and not every biodegradable polymer is bio-based, e.g., poly(ε-caprolactone) or poly(glycolic acid); nevertheless some polymers fall into both categories, such as polyhydroxyalkanoates (PHA)s. Currently, there are no standards to certify a “bio-based product”. However, the bio-based content of a product can be quantify by measuring the bio-based content of materials via carbon isotope analysis, ASTM D (ASTM International b). Compostable polymers were circumscribed to the ASTM D (ASTM International ), that stated “a plastic which is capable of undergoing biological decomposition in a compost site as part of an available program”. Nevertheless, this definition obtained considerable disapproval, and in January , the ASTM removed the standard ASTM D (ASTM International ) and substituted it for the standard ASTM D() (ASTM International a); posteriorly it was withdrawn, with no replacement. To be called compostable, a polymer should meet one of the following international standards: ASTM Standard D (ASTM International a) or CEN standard EN (for compostable plastics), D or EN (for compostable packaging) (ASTM International b), and ISO The ISO-Standard not only refers to plastic packaging but to plastics in general. The biodegradation and/or disintegration rate, in addition to toxicity are the points that make the difference between biodegradable and compostable polymers. All compostable polymers are biodegradable by default, but not vice versa. Definitely, two different criteria point out the definition of a biopolymer: the source of the raw materials, and the biodegradability of the polymer. As a consequence, a biopolymer is a polymer derived from renewable resources, as well as a biological and fossil-based bio-degradable polymer (Niaounakis ). Based on its capacity to be chemically consumed by bacteria, fungi, or other biological means, biopolymers can be divided into two wide groups: biodegradable and non-biodegradable biopolymers. Alternatively, biopolymers can be classified on their origin as being either bio-based or fossil fuel-based. The central categories for distinguishing among the different types of biopolymers are mentioned below (Niaounakis ): i. Bio-based biodegradable biopolymers. ii. Non-Biodegradable bio-based biopolymers. iii. Biodegradable biopolymers made from fossil fuels.
4 Biopolymers for Medical Applications The biopolymers belonging to (i) can be biologically generated by microorganisms, plants, and animals, or chemically synthesized from biological starting materials (e.g., corn, sugar, starch, etc.). Examples of biodegradable bio-based biopolymers are: (1) synthetic polymers from renewable resources such as poly(lactic acid) (PLA); (2) biopolymers produced by microorganisms, such as PHAs; (3) and those that are biosynthesized by various routes in the biosphere, such as starch or proteins. The biopolymers corresponding to (ii) can be produced either from biomass or from renewable resources and are non-biodegradable. Examples of non-biodegradable bio-based biopolymers are: (1) synthetic polymers from renewable resources such as specific polyamides from castor oil (polyamide 11), specific polyesters based on biopropanediol, biopolyethylene (bio-LDPE, bio-HDPE), biopolypropylene (bio-PP), or biopoly (vinyl chloride) (bio-PVC) based on bio-ethanol (e.g., from sugar cane), etc.; (2) naturally occurring biopolymers such as natural rubber or amber. The biopolymers of the last item (iii) are produced from fossil fuel, such as synthetic aliphatic polyesters made from crude oil or natural gas, and are formally biodegradable and compostable. Some examples of biodegradable biopolymers made from fossil fuels are: Poly(ε-caprolactone) (PCL), poly(butylene succinate) (PBS), and selected aliphatic-aromatic co-polyesters. All of them can be degraded by microorganisms (Niaounakis ). Biopolymers and bio-plastics are often considered synonymous, while they are different materials. Biopolymers are polymers that fit the definition given above and the bio-plastics are the plastics that are created by using biopolymers. According to the European Bioplastics e.V., a plastic material is defined as a bio-plastic if it is either bio-based, biodegradable, or contains both properties (Niaounakis ). On the basis of this classification, a material is considered a bio-polymer if it is comprise of any biodegradable polymer (e.g., polymers of type i or iii) or of any bio-based polymers (e.g., polymers of type i or ii). A particular case is the bio-polyethylene derived from sugarcane, designated as “green polyethylene”; it is non-biodegradable, but emits less greenhouse gases when compared to fossil-based polyethylene, and accordingly, is classified as a biopolymer (Niaounakis ). In general, polymers can also be classified on basis of their response to heat as thermoplastics, thermosets, or elastomers (Raquez et al. ); and by their composition as blends (Paul ), composites (White et al. ; Saheb and Jog ), or laminates (Powell ); these classifications can be extended to biopolymers. Currently, the level of bio-based thermoset biopolymers exceeds the volume of bio-based thermoplastic biopolymers (Mohanty et al. ). Biopolymer blends are mixtures of polymers from different origins such as the commercial product Ecovio® (BASF AG), which is a blend of PLA and poly(butylene adipate-co-terephthalate) (PBAT) (Ecoflex®, BASF AG). An extra group is constituted by the bio-composites; these are biopolymers or synthetic polymers reinforced with natural fibers (Mohanty et al. ), such as sisal, flax, hemp, jute, banana, wood, and various grasses, and/or fillers and additives. Novel bio-composites are based on a biodegradable matrix polymer reinforced with natural fibers (Mohanty et al. ).
Biopolymers in Regenerative Medicine 5
Biomaterials chronology and biopolymers Originally, the selection of materials for their use as medical implants was dependent on those already available off the shelf (Hench and Polak ). Early implantable materials include metals such as gold that were used in dentistry over 2, years ago (Langer and Tirrell ). The term “biomaterials” was first introduced within the last 50 years (Atala et al. ). Practically at the same time, and aided by the hasty industrial expansions of polymer synthesis, the assessment of synthetic polymers for biomedical applications was initiated. Polymethylmethacrylate, PMMA, was used in dentistry in the s and cellulose acetate was used in dialysis tubing in the s. Dacron was used to make vascular grafts; polyether urethanes, the materials used in ladies’ girdles, were used in artificial hearts; and PMMA and stainless steel were used in total hip replacements (Langer and Tirrell ). The elaboration of plastic contact lenses, utilizing primarily PMMA, started around (Efron ), and the first data on the use of nylon as a suture was reported in (Atala et al. ). At the end of World War II, a wide variety of polymeric materials were available to inspiring surgeons to break new grounds in replacing diseased or damaged body parts. Materials such as silicones, polyurethanes, Teflon, Nylon, methacrylates, blends with titanium, and stainless steel were available for surgeons to overcome medical problems. Inspired by the idea to restore lost organ or tissue functionality, health and dental experts, made use of minimal regulatory controls to elaborate and improvise replacements, bridges, conduits, and even organ systems based on such materials. Those early implants made from the available industrial materials were frequently incompatible with the host tissue, generally due to their insufficient purity. From the beginning, alterations of the host tissue in reaction to the materials presence became ostensible. Additives such as plasticizers, un-polymerized reactants, and degradation products were evaluated as possible causes, leading to a conscious
Second-generation materilas; materials bio-active. Goal : biodegradable shape memory polymers with programable surface.
t-generation materials; bio-inerts. Goal : reaction-interaction. Prototypical material of first-generation : silicone rubber. PGA as biodegradable suture. y implantable materials "of the self" . PMMA · sed in dentistry; plastic contact lenses; dialysis tubing from cellulose acetate; Nylon sutures; vascular grafts of Dacon; hip replacements from PMMA plus stainless steel.
Fig. 1: Participation of biopolymer in the biomaterials evolution.
Third-generation materials; regeneration reneration
ofiunctional tissues. Goal: induction of response, reabsorbable specifical cellular response . resorbable scaffolds made from bio-polymers bio-polimers that involves molecular tailoring of GFs, adhesive amino-acids sequences or gene expression activation.
6 Biopolymers for Medical Applications exploration of polymer features for biomedical applications and biocompatibility testing. With an emerging knowledge of the immunological system and the understanding of the possible foreign body reaction, a first generation of materials was developed during the s and s (Ratner et al. ). The first-generation materials were designed as bio-inert. The main objective was to create a material that would match the mechanical properties of the replaced tissue, and would not allow protein adsorption and cell adhesion, in order to reduce the possible immune response and rejection. The elastomeric polymer, silicone rubber was widely used as a prototypical material of the first generation (Teck Lim et al. ). In the early s, research shifted from materials that exclusively exhibited a bio-inert tissue response to materials that actively interacted with their environment. The secondgeneration biomaterials are specifically designed to be “bioactive”. This means they should elicit specific and desired cellular responses, like cell adhesion, proliferation and differentiation into a specific cell type, e.g., bone cells that will form a new bone tissue and thus integrate the implant strongly into the surrounding natural tissue (Hench and Polak ). The reaction of the cells should be controllable by the physical and chemical properties of the material surface. An additional advance in this second generation was the development of biodegradable materials that exhibited controllable chemical breakdown into non-toxic degradation products, which were either metabolized or directly eliminated. Biodegradable synthetic polymers were designed to resolve the interface problem, since the foreign material is ultimately replaced by regenerating tissues and eventually the regeneration site is histologically indistinguishable from the host tissue. Since the s, a biodegradable suture composed of polyglycolic (PGA) acid has been in clinical use (Atala et al. ; Ratner et al. ). Many groups continue to search for biodegradable polymers with needed properties such as strength, flexibility, a chemical composition conducive to tissue development, and a degradation rate consistent with the specific application (Zhou et al. ; Shih and Lin ; Evans et al. ). Polymeric materials with novel properties such as shape-memory and programmable and interactive surfaces that control the cellular microenvironment are also under investigation (Han et al. ; Brosnan et al. ; McCloskey ). Other biopolymers’ applications rapidly emerged, thus providing versatile technologies for regenerative medicine, for example, as fracture fixation assistances, as drug delivery devices or as transports of signaling molecules or genetic code information. Biopolymers-based systems can permit delivery of drugs, active proteins, and other macromolecules (Jonker et al. ; Pal et al. ; Estrada and Champion ; Srichana and Domb ) localized the site where the drug is needed. Despite considerable clinical success of bio-inert, bioactive, and resorbable implants, there is still a high long-term prostheses failure rate and need for revision surgery (Atala et al. ; Ratner et al. ). Artificial biomaterials cannot respond, unlike living tissue, to changing physiological loads or biochemical stimuli so improvements of first- and second-generation biomaterials have been incomplete. To overcome these limitations, a third generation of biomaterials that involves molecular tailoring of resorbable polymers for specific cellular responses is being developed. By immobilizing specific biomolecules, such as signaling molecules or cell-specific adhesion peptides or proteins, onto a material it is possible to mimic the extracellular matrix (ECM) environment and stimulate the specific response of cells at
Biopolymers in Regenerative Medicine 7
a molecular level and activate specific gene expression that regulates regeneration and the self-healing process. One of the most advanced strategies in the present research on tissue engineering is the construction of tridimensional (3D) porous scaffolds made of resorbable biopolymers that should be seeded with the patient’s own cells or even stem cells (Weiss and Calvert ; Rezwan et al. ; Stoddart et al. ). Upon implantation into the body, the polymeric scaffolds will provide the cells the necessary support during self-healing process and should be gradually degraded, as they will be continuously replaced by new bone; finally it will disappear completely. Biomimetic surfaces prepared on basis of biopolymers are promising tools to control cell adhesion, implant integration, cell differentiation, and tissue development (Dalsin et al. ; Cheng et al. ; Kim et al. ). Constantly expanding knowledge of the basic biology of stem cell differentiation and the corresponding signaling pathways as well as tissue development provides the basis for novel molecular design of scaffolds. It is rather important that the engineered scaffold will be designed to be steadily remodeled in vivo and to resemble the histological and mechanical properties of the surrounding tissue. Due to this paradigm shift, mechanically labile hydrogels, especially injectable systems that can be used to directly encapsulate cells, have gained great importance as a basis for biomimetic cell carriers (Yu and Ding ; Nicodemus and Bryant ; Wu et al. ; Jiang et al. ). In spite of the great advances attained, in the case of polymer-based devices for bone tissue replacement, their potential use is still very limited due to their insufficient mechanical properties as load-bearing implants. These materials need further improvements, e.g., strong mechanically resistant reinforcement with fibrous or particulate component and loading with bioactive molecules which would accelerate the formation of regenerated, mineralized, and fully functional bone tissue. The subsequent sections will provide a synopsis on the biopolymers impact on the third-generation materials, focusing on their translational potential evidenced by preclinical studies outcomes.
The Role of Biopolymers in Translational Medicine Novel tissue engineering (TE) strategies are developed with the aim to overcome the socio-economic and health burden of different tissues injuries and improve the life of patients worldwide (Ratner et al. ). In the last decades, a pool of multiple techniques and methodologies for biomaterials fabrication has been described in an attempt to address and explore the major functional architectural and compositional cues of native tissues (Atala and Allickson ; Chaikof et al. ; Song et al. ; Hook et al. ; Hassan et al. b). The search for improved and tissueoriented implantable units has extended the knowledge on biomaterials’ potential and highlighted the interest for multimodal scaffolds with novel structures and physicalchemical features (Hassan et al. a; Hassan et al. b; Ruso et al. ; D’Elía et al. ; Gravina et al. ; Ruso et al. ). The multifunctional or multimodal properties of these scaffolds result from the combination of different topographies that are not typically available in a given material, increasing their potential role in regenerative medical strategies (Gravina et al. ; D’Elía et al. ; Gravina et al. ; Hassan et al. a; Hassan et al. b; M Ruso et al. ). Polymers
8 Biopolymers for Medical Applications play a pivotal role to the construction of 3D templates and to the attainment of synthetic ECM environments for tissue regeneration (Sartuqui et al. ; Stevens and George ; Hong and Stegemann ; Geckil et al. ; Tsang and Bhatia ). Figure 2 shows the increasing interest in the study of polymeric materials and their application in tissue engineering; there is a particular emphasis on the development of musculoskeletal tissue’s substitutes. Among the common materials applied to regenerative medicine, the interest on polymers in the last ten years corresponds to the 60% of the researchers’ reports, Fig. 3. Biopolymers can be obtained from both synthetic and natural resources (Atala and Allickson ; Imam et al. ; JagurGrodzinski ; Kalia and Avérous ; Niaounakis ; Niaounakis ). Since each group possesses distinct advantages and limitations, a wide variety of composite materials and interpenetrating networks have been utilized to achieve desired results. Synthetic polymers are versatile to tailoring a wide range of degradation rates, structural features and mechanical properties, representing a reliable mine of new-fangled materials. The composition of the synthetic polymers can be designed to minimize the immune response and combine the best properties together. Synthetic polymers have been described by their degradation by hydrolysis of the ester bonds under physiological conditions and to avoid problems of immunogenicity, that are compelling arguments for achieving the purpose and pursuing the approaches of TE and regenerative medicine (Atala and Allickson ). Nevertheless, the majority of synthetic polymers are hydrophobic, which presents a major drawback for the migration of viable cells into the scaffold core. Examples of synthetic and popular
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Biopolymers in Regenerative Medicine 9 4%1%
• Polymers • Composites • Ceramics D Bioactive Glass • Metallic Foams Fig. 3: Application of different materials to regenerative medicine in the last 10 years. Data Base: Scopus, October
biodegradable synthetic polymers include poly(ethylene glycol) (PEG)/poly(ethylene oxide) (PEO), Poly(ethylene-covinylacetate) (EVA), poly(α-hydroxy acids), especially poly(lactic acid) (PLA), poly(glycolic acid) (PGA) and their co-polymers, poly(εcaprolactone) (PLGA), poly(propylene fumarate), poly(dioxanone), polyorthoesters, polycarbonates, polyanhydrides, and polyphosphazenes. Particularly interesting are PLA and PGA polyesters which have been extensively used in biodegradable implants, tissue engineering, and drug delivery systems, see Tables 1 and 2. Natural polymers have been presented as an interesting option to the currently used synthetic materials due to a higher biodegradability rate and non-cytotoxicity (Atala and Allickson ). They are taken from native sources, exhibit similar properties to soft tissues; and their synthesis often involves enzyme-catalyzed, chain growth polymerization reactions of activated monomers, which are typically formed within cells by metabolic processes. Within this group are included collagen, gelatin, dextran, agarose/alginate, hyaluronic acid, cellulose, and fibrin gels (see Tables 1 and 2). Although they have to be purified to avoid foreign body response after implantation, natural polymers are widely used in regenerative medicine. They have a wide range of mechanical, chemical, and physical properties, are resistant to biochemical attack, and as a consequence of their versatility and flexibility they can be easily processed and shaped. Moreover, they are inert towards host tissues after implantation and are available at a reasonable cost. Independent of their origin, polymers lack properties to stimulate biological functions, such as osteo-conductivity and cell bioactivity. As a consequence, hybrid variants of these materials have emerged through synthetic designs (Bourgeat-Lami et al. ) and genetic engineering of peptide-based biopolymers (Atala and Allickson ). Biodegradable polymers have been selected for the drug delivery system as they do not need surgery to be removed after releasing of the drugs and can be excreted by the body itself. Examples of biomedical applications using biopolymers include heart valves, vascular grafts, artificial hearts, breast implants, contact lenses, intraocular lenses, components of extracorporeal oxygenators, dialyzers and plasmapheresis
NH2
O
OH
OH
O HO
O HO O
OH
O
OH
NH2
O
NH
O
n
O n HO
*
OH
NH2
O OH
HO
O OH
O
m
O HO
O O
OH OH
n
O
1 →4 linked β-D-mannuronic acid (M) and α-L-guluronic acid (G) residues
O
OH
Alginic Acid/ Sodium Alginate
Characteristics
Alginic Acid or its sodium salt, Sodium Alginate, is an anionic polysaccharide disseminated in the cell walls of brown algae. G residues associate with divalent cations to form ionic crosslinks.
Chitosan is a linear polysaccharide obtained from deacetylation of chitin (main component in the exoskeletons of crustaceans’ shells) and is a material structurally similar to GAGs, being degradable by enzymes in humans.
Hyaluronic acid (HA) is a glycosaminoglycan (GAG) present in all vertebrates. HA is a major component of connective tissues and plays an important role in lubrication, cell differentiation, and cell growth.
Natural-Based Biopolymers
Randomly distributed b-()-linked D-glucosamine and N-acetyl-D-glucosamine
HO HO
OH
O HO
Chitosan
*
O
Hyaluronic Acid
Name
Table 1: Regular natural- and synthetic-based biopolymers involved in regenerative medicine.
10 Biopolymers for Medical Applications
Agarose
O
O
OH
OH
OH O
HO
O
O
OH
O
O
n OH
n
OH
OH
OH
O
O
carrageenan
CH2OH
poly-(R)hydroxybutyrate (P3HB)
O OH
OH OH
O
PHAs are linear polyesters produced in nature by bacterial fermentation of sugar or lipids.
Agarose is a natural-based polysaccharide obtained from agar.
It is extracted from red seaweeds; carrageenan displays close similarities with mammalian GAGs.
Gelatin
Gelatin is an irreversibly hydrolyzed form of collagen. Table 1 cont
Collagen is the central structural protein in the extracellular space in animals’ Monomeric and crosslinked 3D triple helical structures. Many types, type I consists of two connective tissues; it is the most abundant protein in mammals, representing about 25%–35% of the whole-body protein content. identical α1 chains and one α2 chain
O
Collagen
H
O
Poly(hydroxyalkanoates) (PHAs) /
H
OH
O
CH2OH -O2SO
carrageenan
OH
Carrageenan
Biopolymers in Regenerative Medicine 11
Insoluble polymer found in non-mineralized tissues. Bundles form intermediate filaments that make up hair (α-keratins) and nails (β-keratins). Monomers form stable left-handed superhelical structures to form filaments. Silk is a natural protein fiber mainly composed of fibroin and is extracted from the cocoons of the Bombyxmori silkworm. Foams, sponges, films, and hydrogels are formed from the silk solution.
Keratin
Silk
Glycoprotein secreted by fibroblasts
Fibronectin
This binds integrins, transmits mechanical cues from the environment to the cell and binds other ECM proteins such as collagen and fibrin.
It is formed by the action of the protease thrombin that cleaves fibrinogen which causes the latter to polymerize, generating soft gels. Gelation kinetics is controlled by the ratio of thrombin to fibrinogen, calcium concentration, and temperature.
It is a fibrous, non-globular protein involved in the clotting of blood
Fibrin
Characteristics Elastin is the elastic component in soft tissues that allows tissue to return to normal shape following stretch or pinch. Formed by crosslinking smaller tropoelastin polymers using lysyl oxidase to form mesh-like structures.
Name
Natural-Based Biopolymers
Elastin
Table 1 cont.
12 Biopolymers for Medical Applications
H
OH
H
O
OH
H
CH2OH
n = -
OH
H
Starch H O
H H OH
H
O
OH
H
CH2OH H O n
H
H
OH
H
CH2OH
OH
H
O
OH
H
Table 1 cont
Starch is a polysaccharide consisting of a large number of glucose units joined by glycosidic bonds and produced by green plants as an energy store. It is quite abundant in nature and is an almost unlimited source and low-cost associated raw material.
Biopolymers in Regenerative Medicine 13
n
*
O
O
Poly(lactic acid) (PLA)
*
O
m
*
H
n *
OCOCH3
n O
Polylactic acid (PLA) is thermoplastic, aliphatic polyester, produced from non-toxic renewable feedstock, naturally occurring organic acid, or made by fermentation of sugars obtained from renewable resources such as sugarcane.
Poly(ethylene-covinylacetate) (PEVA) is the copolymer of ethylene and vinylacetate. It is a polymer that approaches elastomeric (“rubber-like”) materials in softness and flexibility.
H
Poly(ethylene-covinylacetate) (PEVA)
Characteristics PEG, PEO, or POE refers to an oligomer or polymer of ethylene oxide. The three names are chemically synonymous, but historically PEG is preferred in the biomedical field, whereas PEO is more prevalent in the field of polymer chemistry.
Name
Synthetic-Based Biopolymers
Poly(ethylene glycol) (PEG)/Poly(ethylene oxide) (PEO)
Table 1 cont.
14 Biopolymers for Medical Applications
O n OH
HO
O O
Poly(propylene fumarate) (PPF)
*
Poly(ε-caprolactone) (PCL)
H
O
O
O
O
; HO
O
n
*
O
n
Polyglycolic Acid (PGA)/Poly l-glycolic Acid (PLGA)
O
OH
x O
O y
H
PPF can be cross-linked via radical polymerization by itself or with crosslinkers such as methylmethacrylate, N-vinyl pyrrolidinone (NVP), and biodegradable macromers of PPF-diacrylate or poly(ethylene glycol)diacrylate.
Polycaprolactone (PCL) is a biodegradable polyester with a low melting point of around 60°C and a glass transition temperature of about −60°C.
PGA and PLGA are synthesized by means of ring-opening copolymerization of two different monomers, the cyclic dimers (1,4-dioxane2,5-diones) of glycolic acid and lactic acid.
Biopolymers in Regenerative Medicine 15
Natural-Based
Biomaterial Form
Soluble, cationic in acidic conditions, and insoluble in neutral and basic conditions. Hemostatic stimulates osteo-conduction and wound healing. Shape-ability to fit the defect site, degradability. Degradation through ionic exchange with surrounding media. Variations in local mechanical properties controlled by concentration of calcium ions. Slow degradation profile and the low mechanical properties, 3D scaffolds exhibiting soft and flexible structure suitable for chondrocyte maintenance and MSC differentiation. Thermally, pH and cation concentration responsive material, in expensive and easy to manipulate. Effectiveness in maintaining the proliferative and chondrogenic potential of encapsulated cells.
Alginic Acid/ Sodium Alginate
Agarose
Carrageenan
Hydrogel
3D Scaffolds, hydrogels.
Soft gels, composite materials, electrospun fibers.
3D Scaffolds, hydrogel, membrane, nano-particles.
Minimal immune response and 3D Scaffolds, chemotactic combined with the hydrogels, adequate agents. Osteo-inductive electrospun and angiogenesis in combination fibers, nano-and with GFs. micro-gels.
Properties
Chitosan
Hyaluronic Acid
Biopolymer
Skeletal tissues regeneration, cell delivery system.
Skeletal tissues regeneration, efficient system for cartilagelike substitutes, islet, kidney and fibroblast encapsulation, nerve regeneration.
Wound healing, drug delivery, soft tissue engineering, cell delivery, in vitro stem cell maintenance.
Wound healing, orthopedics, cardiac repair, neural tissue engineering, cornea repair, drug and gene delivery.
Keratynocytes encapsulation, bone and cartilage reparation, drug delivery, vocal fold and nerve regeneration, spinal cord injuries.
Application
Table 2: Applications of natural- and synthetic-based biopolymers to regenerative medicine.
DIABECELL® NTCELL® Xelma
Hemcon®
Hyalograft 3D TM
Example of Approved Clinical Product
(Popa et al. ; Popa et al. ; Mihaila et al. )
(Stokols et al. ; Stoppel et al. ; Elisseeff et al. ; Chen et al. )
(Bressan et al. ; Stoppel et al. ; Tan ; Vowden et al. ; Lee et al. ; Ghidoni et al. ; Sun and Tan )
(Stoppel et al. ; Azad et al. ; Obara et al. ; Mi et al. ; Noel et al. ; Noel et al. ; Lu et al. ; Chien et al. ; Roy et al. ; Gustafson et al. )
(Bressan et al. ; Stoppel et al. ; Prestwich ; Burdick and Prestwich ; Lee et al. ; Jia et al. ; Park et al. ; Horn et al. )
16 Biopolymers for Medical Applications
Adequate substrate for bone cells growth. Scaffolds of brittle nature.
Low immune response, good substrate for cell adhesion, chemotactic. Easily remodeled and degraded by cells. Chemical crosslinking decreases degradation and improves long-term mechanical properties. Many types available. Improper expression or mutation leads to disease. Small tropoelastin polymers can be used to form composite materials. Easily remodeled by cells. Stimulates cell migration, osteoconduction and vascularization. Fibrinolytic inhibitors, like aprotinin or aminocaproic acid, reduce in vitro degradation rates. Improper regulation of expression leads to diseases such as cancer, fibrosis.
PHAs
Collagen Gelatin
Elastin
Fibrin
Fibronectin
Grafted onto 2D and 3D surfaces to improve biocompatibility.
3D scaffolds
Films, gels 3D scaffolds, electrospun fibers.
3D scaffolds, membrane.
Hydrogel,
3D Scaffolds, HAp nanocomposite, nano-particles.
Wound healing, stem cell differentiation, cardiac repair, bone regeneration.
Wound healing, lung and cardiac repair, in vivo cell delivery, bone defects reparation.
Cardiac stent coatings, soft tissue reconstruction, orthopedics and cell encapsulation.
Fibroblast and keratinocytes encapsulation, wound healing, skin substitute, muscle repair, nerve regeneration, anti-aging, soft tissue reconstruction, bone repair.
Corneal epithelium repair, heart valves, bone tissue regeneration, drug delivery systems.
TachoSil® CASCADE® Autologous Platelet System
Integra TM ApliGraft® ORCEL TM NeuroFlex® NeuroMatrix® NeuroMend® Dynamatrix® INFUSE®
HCE
Table 2 cont
(Grinnell ; Mosahebi et al. ; Prestwich ; Barker ; Stoppel et al. )
(Siemer et al. ; Anegg et al. ; Torio-Padron et al. ; Cherubino and Marra ; Christman et al. ; Wu et al. )
(Boland et al. ; Jordan et al. ; Schwartz and Wolff ; Salzberg ; Sell et al. )
(Bressan et al. ; Stoppel et al. ; Heimbach et al. ; Halim et al. ; Meek and Coert ; Nevins et al. ; McKay et al. ; Zhang et al. a)
(Sodian et al. ; Sodian et al. ; Errico et al. ; Pielichowska and Blazewicz )
Biopolymers in Regenerative Medicine 17
Natural-Based
Low enzymatic degradation rate controlled by crystallinity (β-sheet content), and some concerns arise on potential cytotoxic effects. Intrinsic mechanical properties. Mechanics tailored by modifying concentration, crystallization, molecular weight, and scaffold size. Thermoplastic behavior, promotes cell adhesion, non-cytotoxic and biocompatible.
Silk
Starch
Versatility of the PEG macromer chemistry and excellent biocompatibility.
Structure attributed to disulfide bridges; more bridges yields lower elasticity. Classified as neutralbasic or acidic, dictating in vivo occurrence.
Keratin
PEG/PEO
Properties
Biopolymer
Table 2 cont.
3D Scaffold, hydrogels, micelles.
3D scaffold
3D Scaffolds, foams, films, sponges, hydrogels, electrospun fibers.
3D scaffold, hydrogel, films.
Biomaterial Form
Fibroblast and keratinocytes encapsulation, ulcers wound healing, drug and gene delivery.
Bone and cartilage regeneration, spinal cord injury treatment.
Tendon and skeletal tissues regeneration, cornea repair, drug delivery.
Cornea tissue engineering, wound healing, skin regeneration, cardiac repair, drug delivery, nerve repair, cell encapsulation.
Application
Xelma
PolyActiveTM
Example of Approved Clinical Product
(Bressan et al. ; Lin and Anseth a; Park et al. ; Salinas et al. ; Elisseeff et al. ; Mahoney and Anseth ; Osada et al. ; Lin and Anseth a)
(Salgado et al. ; Martins et al. ; Gomes et al. ; SáLima et al. ; Salgado et al. )
(Zhang et al. b; Kundu ; Stoppel et al. ; Meinel et al. )
(Apel et al. ; ElloumiHannachi et al. ; Satija et al. ; Reichl ; Nishida et al. ; Sierpinski et al. )
18 Biopolymers for Medical Applications
Synthtic-Based
Low chemical versatility and slow degradation by hydrolysis or bulk erosion. Difficulties for withstanding mechanical loads.
Satisfactory biological results, mechanical properties inferior to those of PGA, PLGA.
PPF
and
PCL
Biodegradable thermoplastic polymer.
Degradation by hydrolysis. They can present some problems regarding cytotoxicity.
PLA
PGA/PLGA
It has low-temperature toughness, stress-crack resistance, hot-melt adhesive waterproof properties, and resistance to UV radiation.
PEVA
Hydrogel, 3D scaffold, nanocomposite.
3D scaffolds, nanocomposites, micelles, electrospun fibers, vesicles.
3D scaffolds, fibers, membranes.
3D scaffold, electrospun fibers, microspheres.
Micro/nanofibre layers, nano-composite scaffolds.
system,
Cartilage and bone regeneration, cell encapsulation, nerve regeneration.
Bone regeneration, drug delivery, cell encapsulation, skin regeneration.
Drug release, stents, stem cell encapsulation and differentiation, cartilage and bone regeneration, facial nerve defects regeneration.
Fibroblast and keratynocytes encapsulation, macromolecules immobilization, bone, cartilage and nerve regeneration.
Drug delivery cardiovascular stents.
DermaGraftTM
(Liao et al. ; Lee et al. ; Kim et al. ; Wang et al. ; Tan and Marra ; Lee et al. )
(Williams et al. ; Fujihara et al. ; Allen et al. ; Reneker et al. ; JagurGrodzinski ; Cao et al. ; Dai et al. )
(Crow et al. ; Tammela and Talja ; Kotsar et al. ; Zare-Mehrjardi et al. ; Mouthuy et al. ; Nassif and El Sabban ; Zhu and Lou )
(Bressan et al. ; Hart et al. ; Zhu et al. ; Kim et al. ; Evans et al. ; Kang et al. ; Uematsu et al. )
(Sultana et al. ; Alhusein et al. ; Strohbach and Busch )
Biopolymers in Regenerative Medicine 19
20 Biopolymers for Medical Applications units, coatings for pharmaceutical tablets and capsules, sutures, adhesives, and blood substitutes, kidney, liver, pancreas, bladder, bone cement, catheters, external and internal ear repairs, cardiac assist devices, implantable pumps, joint replacements, pacemaker, encapsulations, soft-tissue replacement, artificial blood vessels, artificial skin, dentistry, drug delivery, and targeting sites of inflammation or tumors and bags for the transport of blood plasma (Langer and Tirrell ; Mani et al. ; Melek ; Meyers et al. ; Niaounakis ; Patel ; Rathenow et al. ; Ratner et al. ; Stevens ; Teck Lim et al. ; Terzic and Nelson ; Tseng et al. ; Weiss and Calvert ; White et al. ; Yu and Ding ; Zhou et al. ; Zilla et al. ); some selected examples are summarized in Table 2.
Building Biomimetic Materials on the Basis of Biopolymers: along Physic, Chemistry, Biology, and Materials Science The investigation of biopolymers has been reserved to biochemists and molecular biologists for over half a century. Nevertheless, during the last decade, the soft matter physics, chemical, and material science’s community has been seized to this research field (Chassenieux et al. ). The earliest multidisciplinary “bioengineering” collaborations were born sometime in the s–s. Those teams of physicians, chemists and engineers not only noted the necessity of regulating the composition, purity, and physical properties of the materials they were using, but also recognized the need for new materials with innovative and superior properties (Ratner et al. ). This inspired the expansion of many original materials, starting from the s. Novel materials were designed and fabricated specifically for medical use, such as biodegradable polymers, “medical grade” silicones, pyrolytic carbon, and bioactive glasses and ceramics. Others were derived from existing materials that were then manufactured using new technologies, such as polyester fibers that were knitted or woven in the form of tubes for use as vascular grafts or cellulose acetate plastic that was processed as bundles of hollow fibers for use in artificial kidney dialysers (Ratner et al. ). Further materials were specifically modified to provide special biological properties, resembling one of the earliest “bioengineered” biomaterials involving the immobilization of heparin to create anticoagulant surfaces (Ratner et al. ). Biopolymers become the new building blocks from the point of view of macromolecular chemistry; the models and the tools provided by the soft matter physical-chemical community resulted in a better understanding of the mechanisms involved during their assembly to perform analogous task of the biological molecular machines (Kay et al. ). For example, cells, muscles, and connective tissue owe their remarkable mechanical properties to the complex biological macromolecular assemblies that are predominantly made from mixtures of stiff biopolymers (Kroy ; Meyers et al. ). As the hardness of these biopolymers, and the resulting anisotropic networks leading to its smart mechanical and dynamic properties, are far from being understood, a better comprehension of their incessant assembly, disassembly, restructuring, active and passive mechanical deformation can be achieved by physical-chemical theoretical modeling (Dobrynin and Carrillo ; Pritchard et al. ). Moreover, molecular biologists can create accurate mutations
Biopolymers in Regenerative Medicine 21
of specific groups at precise points along the chain for understanding, for example, the influence of a particular residue on the folding–unfolding process; its stimulus on biopolymer mechanical properties can be directly obtained by atomic force microscopy (AFM) measurements (Alessandrini and Facci ). It should be noted that some implants and devices, such as artificial heart valves, are comprised of more than one class of biomaterial. Bio-nanocomposites is a fascinating and interdisciplinary topic that constitutes a great area of interest for biomedical technologies such as tissue engineering (Zhang et al. ), medical implants (Negroiu et al. ; Rathenow et al. ; Kidane et al. ), dental applications (Chen ), and controlled drug delivery (Morgan et al. ; Ke et al. ). Biopolymer nano-composites are the result of the precise combination of biopolymers and inorganic/organic units that interact at the nanometer scale. The extraordinary versatility of these new materials that comes from the large range of biopolymers and fillers available, such as clays, cellulose whiskers, and metal nanoparticles, can be tailored only by the correct confluence of multidisciplinary methodologies (Chassenieux et al. ). An extremely valuable tool for various applications in the science of biomaterials (Sionkowska ) is the use of hybrid polymer systems composed of natural and synthetic macromolecules. The goal of bio-artificial blending is to produce man-made assortments that confer unique structural and mechanical properties on the base of the individual properties of natural polymers and synthetic polymers. Biopolymer’s blends are well known to exhibit a very rich and applicable phase behaviors (Chapman et al. ; Sionkowska ) and the miscibility of their components is an important aspect in determining the properties of the blend. The understanding of the underlying physics of these phase behaviors and of the rheology–morphology relationships of the resulting phases constitutes an interesting and important challenge for their optimal applications (Chassenieux et al. ). Actually, biomaterials scientists and engineers have developed a growing interest in natural tissues and biopolymers in combination with living cells. This is particularly evident in the field of tissue engineering, which focuses on the repair or regeneration of natural tissues and organs (Ratner et al. ). This interest has stimulated the development of novel technologies for the isolation, purification, and application of many different natural materials, including de-cellularized natural tissues and spider silk.
Biopolymers for Hard and Soft Tissue Regenerations Although the reconstruction of small or moderate sized tissue imperfections are technically feasible, thanks to the natural ability of the body to repair itself, larger volume defects remain problematic. The state-of-the-art of medical and surgical therapies continues to be suboptimal, in part because of a lack of replacement biological parts (Bressan et al. ). In this sense, many natural biomaterials based on biopolymers have been widely considered for hard and soft tissue reconstruction. They can be used alone or combined with other synthetic or inorganic constituents. The main properties of these tissue engineered materials are the special dressing, nursing care, and the reduced time in grafting. Regardless of their mechanical fragility and high cost, many recent in vivo investigations contributed to the FDA approval of new
22 Biopolymers for Medical Applications biomaterials for clinical use based on natural biopolymers as matrices for cell delivery and as scaffolds for cell-free support of native tissues. Some selected examples are summarized in Table 2.
Biopolymers gels for cell encapsulation Mammalian cells encapsulation on biopolymer gels becomes an increasing area of interest in regenerative medicine (Hunt and Grover ). The application these strategies to TE can be split into two main categories (Nedovic and Willaert ): (i) the replacement of the biochemical function or (ii) the replacement of the structurally functional tissue. Cell encapsulation in biopolymer hydrogels was originally explored for immuno isolation of cells producing therapeutic proteins for treatment of diseases. In such strategy it is required the chemical communication in the scaffold (i.e., diffusion of molecules),so it is possible to deliver cells encapsulated in an immuno isolatory nanoporous polymer membrane. The membranes are constructed in a way that their pores have to be large enough to allow nutrients, waste, and bioactive factors to diffuse but not so large as to allow immune cells to attack the cells inside (Nedovic and Willaert ). This strategy has mainly been employed to temporarily or permanently replace biochemical functions of the liver pancreas, and provide local protein delivery in neurological disorders. More recently, encapsulation of mammalian cells has been used in the regeneration of an array of different tissues. This second major strategy involves entrapping cells on a micro- or macro-porous polymer scaffold and promoting the formation of a new tissue that is structurally and functionally integrated with the surrounding tissue. The scaffold is constructed with a biocompatible material that it will degrade over time to leave only the integrated tissue in its place. A variety of naturally derived and synthetic biopolymers that can be processed into many different physical forms and geometries are used for cell encapsulation. The biomaterial component of these therapies must provide the appropriate mass transport properties, membrane or scaffold stability, and desirable cellular interactions depending on the location and desired function of the implant. Some of these studies are summarized in Table 2.
Stimuli responsive hydrogels based on biopolymers Intelligent hydrogels based on biopolymers which can change their swelling behavior and other properties in response to chemical and physical stimuli such as pH, metabolites or/and ionic factors, temperature and electric fields, have attracted great interest. These ‘‘smart’’ hydrogels, in addition to their biocompatibility, biodegradability, and biological functions, exhibit single or multiple stimuliresponsive characters which could be used in biomedical applications, ranging from controlled drug delivery systems and cell adhesion mediators to controllers of enzyme function and gene expression in bioengineering or tissue engineering. Among them, temperature- and pH-responsive hydrogels have been the most widely studied, because these two factors have physiological significance (Oh et al. ; Chilkoti et al. ; Prabaharan and Mano ; Alarcon et al. ). Biopolymers having a lower critical solution temperature (LCST) below human body temperature have a potential for
Biopolymers in Regenerative Medicine 23
injectable depot systems in therapeutic delivery systems and in tissue engineering. A number of polysaccharides have been considered to be combined with the thermoresponsive materials including chitosan, alginate, cellulose, and dextran. Due to the pH-sensitive character of chitosan or alginate, combination of these polymers with a thermoresponsive material will produce dual-stimuli-responsive polymeric gels to be used as delivery vehicles that respond to localized conditions of pH and temperature in the human body (Prabaharan and Mano ). Control over the function of a therapeutic biopolymer can be obtained by polymer–biopolymer conjugate chemistry. Responsive polymer–biopolymer conjugates have been extensively studied by Hoffman, Stayton, and co-workers (Hoffman ; Pack et al. ). They reported a temperature and photochemically switchable endoglucanase that displayed varying and opposite activities depending whether temperature or UV–Vis illumination was used as the switch (Shimoboji et al. ). Regarding synthetic polymers, Poly(Nisopropylacrylamide) (PNIPAm) is the most studied. It undergoes a sharp coil–globule transition in water at 32°C, changing from a hydrophilic to a hydrophobic state below this temperature. Surface modification of materials can be used to control and modulate cellular-material interactions, for example, to promote bone and skin cell interaction with the implant, and to prevent the adhesion of unwanted cells. Okano and co-workers have extensively used thermoresponsive PNIPAm-based polymers as surface mediators of biopolymer and cell attachment (Okano and Winnik ; Peppas et al. ). Human skin fibroblasts have been shown to attach to and proliferate at the surface of thermoresponsive hydrogels of ethylene glycol vinyl ether and butyl vinyl ether co-polymers. Cultured cells were readily detached from the polymer surface by lowering the incubation temperature from 37°C to 10°C for 30 min. Incorporation of Arg-Gly-Asp (RGD) peptides at the surfaces resulted in higher values of cell proliferation in the initial stage (Gümüşderelioğlu and Karakeçili ). Stile and Healy, extended this concept by the preparation of PNIPAm–RGD conjugates and manipulated osteoblast adhesion (Stile et al. ).
3D bio-printed scaffolds In order to permit cell morphogenesis associated with living tissue function, there is a need to supply the cells with appropriate stimuli within their physical 3D support structure. As it was mentioned in previous sections, biomimetic hydrogel scaffolds can be easily designed using natural ECM components, including collagen or fibrin. However, the range of physical properties, such as stiffness and mesh size—which can be controlled by the gelation process of the purified proteins—is relatively narrow. In addition, these materials are not typically available in large quantities and suffer from batch-to batch variations. Several attempts were made to improve the properties of protein hydrogel scaffolds by the introduction of covalent cross-linking, improving the self-assembly of the protein molecules or adding a coexistent polymer network (Zhu and Marchant ; Rajaram et al. ; Suo et al. ; Ahmed ). Because most of the conventional techniques for scaffold preparation are limited when it comes to the spatial control of porosity and pore size, computer-aided design (CAD) and advanced manufacturing techniques to improve scaffold development have been
24 Biopolymers for Medical Applications adopted by the tissue engineering community (Li et al. ; Bose et al. ). 3D bio-printing refers to the application of 3D printing technologies towards the development of precisely defined scaffolds for tissue regeneration. Although in the middle of s the term was reserved only for inkjet-based approaches, nowadays it is collectively used for all additive manufacturing (AM) processes (Li et al. ; Gross et al. ). 3D printing strategies can be applied, in one way or another, to bio-printing; these include: stereolithography (SLA) (Dhariwala et al. ), selective laser sintering (SLS) (Chang et al. ), fused deposition modeling (FDM) (Mironov et al. ), syringe deposition (Zhang et al. ), two photon laser lithography (Müller et al. ), powder printing (Gbureck et al. ), 3D inkjet printing (Xu et al. ), and organ printing (Mironov et al. ). All of these AM technologies have in common the capability to build a scaffold or tissue construct with complicated 3D geometries, without the necessity of tooling, directly from CAD files and using chloroform for binding polylactic acid (PLA) and polyglycolic acid (PGA) powders in a powder binding approach. Chloroform was used for selective solvation of the polymeric particles, resulting in particle adhesion upon chloroform evaporation (Li et al. ). Engineers and clinicians arrived to a widespread consensus that 3D bioprinting will permit the manufacturing of much more complex and intricate scaffolds for tissue regeneration, mainly because of the opportunities it presents for customizing scaffold shape, structural complexity, and cellular organization. Selected examples are summarized in Table 2.
“Engineered’’ peptide-based biopolymers in biomedicine and biotechnology In the s, the fundamental polypeptides structural features were elucidated. Forty years later, Ghadiri (Ghadiri et al. ) and Zhang (Zhang et al. ) demonstrated that these rules can be exploited and adapted to produce supramolecular peptide based materials (Zelzer and Ulijn ). A fresh class of biomaterials becomes known due to the exceptional chemical, physical, and biological properties of the “engineered’’ peptide-based biopolymers. The expansion of peptide-based biomaterials was motivated by the convergence of protein engineering and macromolecular self-assembly (Chow et al. ). Prototypical examples of engineered peptide-based biomaterials include poly-amino acids, elastin-like polypeptides, silk-like proteins, coiled-coil domains, tropoelastin-based peptides, leucinezipper-based peptides, peptide amphiphiles, betasheet forming ionic oligopeptides, and beta-hairpin peptides (Chow et al. ). In addition, biopolymers can be easily functionalized to enhance their interactions with cells and provide an optimal platform for cellular activities and tissue functions. In this section, we will discuss two main classes of peptide-based biopolymers in tissue engineering: self-assembling polypeptides that form gels by environmental stimuli and polypeptides that form gels via chemical crosslinking. The first class of hydrogels is based on naturally occurring fibrin, which is spontaneously formed by the polymerization of fibrinogen in the presence of thrombin and further cross-linked by the transglutaminase activity of factor XIIIa (Ehrbar et al. ; Schmoekel et al. ; Park et al. ; Sakiyama et al. ; Lee et al. ;
Biopolymers in Regenerative Medicine 25
Nettles et al. ; McHale et al. ). Gel formulations prepared from fibrin glue plus matrix-bound vascular endothelial growth factors (VEGFs) are also promising candidate substrates for expansion or transplantation of endothelial progenitor cells (EPCs). Ehrbar et al. studied three variant forms (VEGF), formulated within fibrin matrices, each with differential susceptibility to local cellular proteolytic activity (Ehrbar et al. ). Fibrin matrices were also successfully improved with bone morphogenetic protein-2 (BMP-2) to promote bone growth and healing (Schmoekel et al. ; Park et al. ) and with heparin-binding proteins to promote neuritis extension (Sakiyama et al. ; Lee et al. ). Elastin-like polypeptides (ELP) are useful for thermally sensitive injectable hydrogels because they undergo an inverse temperature phase transition and can be designed at the molecular level. The study of ELPs was pioneered by Dan Urry (Urry ), who synthesized a large number of polypeptides over the course of three decades and studied their biophysical properties in solution and as cross-linked elastomeric materials. ELPs have been investigated as an alternative scaffold for cartilage repair (McHale et al. ; Nettles et al. ). To emulate the triple helical structure of collagen, peptide-amphiphiles (PAs) consisting of a collagen sequence Gly-Val-Lys-Gly-Asp-Lys-Gly-Asn-Pro-Gly-TrpPro-Gly-Ala-Pro connected to a long-chain mono- or di-alkyl ester lipid, have been synthesized by Fields, Tirrell and coworkers (Yu et al. ). Neither the peptide nor the tail alone produced significant adhesion of melanoma cells; however, the self-assembled triple helical structure of the PA significantly promoted cell adhesion (Fields et al. ). In the second class of hydrogels, chemically cross-linked 3D networks are formed by Michael-type addition reactions between thiol-bearing bioactive peptides and conjugated unsaturations on single- or multi-armed poly(ethylene glycol) (PEG) chains end functionalized with vinyl sulfone (Hubbell ). ELP are also good candidates for chemical crosslinking, because it is easy to incorporate chemically active amino acids at the guest residue position in the elastin-based repeat unit, Val-Pro-Gly-Xaa-Gly and in addition, because ELPs can be designed at the molecular level and genetically synthesized, unique properties can be introduced by incorporating other biologically active peptide sequences. Examples can be found of ELP hydrogels that are formed by irradiation (Annabi et al. a), photo-initiation (Almany and Seliktar ), aminereactive chemical crosslinking (Annabi et al. b), and enzymatic crosslinking by tissue transglutaminase (McHale et al. ; Davis et al. ; Collighan and Griffin ). The hydrogels have been successfully used for cartilage and intervertebral disc tissue repair, small-diameter vascular grafts, urinary bladders, stem cell matrices, neural guides, stem cell sheets, and post-surgical wound treatment (Simnick et al. ; Chow et al. ; Lim ). The application of chemically cross-linked ELP hydrogels for in situ gelation by chemical crosslinking has been limited by poor solubility in water, concerns about toxicity, lack of biocompatible crosslinking reagents and by products, or slow gelation kinetics. Even though peptide-based biomaterials have become increasingly significant materials in regenerative medicine, their use has restrictions, related to their short shelf life and thermal instability. Many of these limitations can be addressed by emerging technologies, thus further expanding the uses of peptide-based biomaterials into applications for which they are currently impractical.
26 Biopolymers for Medical Applications
Perspectives and Outlooks Biomaterial design and its application to regenerative medicine have made great strides in the past decades and holds tremendous impact for future clinical applications. Sustained growth of this field centers in part on the development of novel materials and improved scaffold processing techniques. The specificities of the biopolymer block in terms of bioactivity, biocompatibility, and biodegradability allow specific application over the bio-medical fields. Polymer–biopolymer interactions can increasingly be designed as well as selected, and so their intervention in cellular dysfunctions may be possible and lead to more powerful, specific, and potent therapies. Moreover, a deeper comprehension of the underlying mechanisms of tissue regeneration would contribute invaluably to tailoring scaffold properties in a more representative manner of the native environment. Currently, the focus has been on addressing biomimetic surface topography for influencing cell behavior, controlled delivery of bioactive signals to stimulate regeneration, bone construct vascularization, articular cartilage zonal architecture, and osteochondral interface integration. Polymer chains can be prepared with individual segments that respond to pH, temperature, ionic strength, UV irradiation and electric fields, affording truly multifunctional materials. ‘Chemically-responsive’ systems, such as the glucose-sensitive polymers, are also becoming accessible. Structure–function relationships previously only obtainable for biomacromolecules can now be deduced for wholly synthetic materials owing to the degree of control accessible through living polymerisation methodologies, while biopolymer synthesis and activity can be manipulated through molecular biology approaches. This convergence of synthetic and natural macromolecular chemistry inherently leads to biomedical applications, as the ability to control polymer structure leads to the ability to manipulate functionality. Bio-printers can automate the assembly process and permit pre-programmed and complex manipulation of biopolymers—from the macromolecular to the living cell level—to achieve architectural and biochemical complexity that was never before possible and produce tissue and organ substitutes that precisely mimic their natural counterparts. It is expected that these diverse methodologies for regenerative medicine will translate from ‘bench to bedside’ in the future.
Acknowledgements The authors acknowledge Universidad Nacional del Sur (PGI 24/Q), Concejo Nacional de Investigaciones Científicas y Técnicas de la República Argentina (CONICET, PIP—CO) and Fundación Ramón Areces. PVM is an independent researcher of CONICET.
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2 Application of Natural, Semi-synthetic, and Synthetic Biopolymers used in Drug Delivery Systems Design Javier Sartuqui,§ Noelia L. D’Elía,§ A. Noel Gravina§ and Luciano A. Benedini* Introduction Science and technology play a key role in the extended life expectancy. In this sense, a wide range of innovative techniques and new devices have been developed, resulting in a reduction of morbidity and mortality. The use of drug delivery systems to improve the efficacy of bioactive molecules remains essential strategy for achieving the treatment against diseases and the progress in this field has been essential. In this context, synthetic, semi-synthetic, or natural polymers are frequently used for developing drug delivery systems. Accordingly, their application goes from the generation of suspension with cyclodextrins to solubilize hydrophobic drugs to the formation of matrices which control, by means of their degradation, the release of drugs.
Departamento de Química, Universidad Nacional del Sur, INQUISUR-CONICET () Bahía Blanca, Argentina. * Corresponding author: [emailprotected] § These authors contributed in the same way to this work.
Biopolymers used in Drug Delivery Systems 39
There are relevant factors that should be evaluated when choosing a polymer for use as a drug carrier. One of the most important is the biocompatibility, which is related with the acceptance of the material by tissues. The problems encompassing this condition can include hypersensitivity reactions; since that the pharmaceutical formulation should be in contact with different tissues, some of them more sensitive than others, the long time by an increased time of carrier-tissue interaction may cause an alteration in drug biodisponibility due to changing biopharmaceutical parameters. Biodegradability is the timely degradation of the polymer in contact with the tissue; this is the other important feature that must be considered. Furthermore, the drug delivery system must be degraded and their components removed from the body to prevent their accumulation, and thus avoiding any potential toxicity. In accordance with green chemistry, a solvent free processing to obtain the different drugs carriers is also important because the reduction of contaminant by-products is one of the biggest challenges for developing pharmaceutical products. Frequently, natural polymers are synthetically modified to reinforce their positive features and to decrease the negative ones. These new compounds are named semisynthetic derivatives. Sometimes positive characteristics can be improved, but negatives cannot be abolished. Hence, their advantages and disadvantages must be critically discussed, and the biocompatibility of these natural materials and their derivatives must be compared. Occasionally, availability from renewable resources is also considerate; and therefore, natural and semi-synthetic polymers are often advantageous compared to synthetic alternatives. Finally, when active biomolecules are included into formulations based in polymers, their physicochemical features, and sensibility must be considered. Thus, some characteristics of the drugs such as charge and solubility, among others, could direct their inclusion into a polymeric matrix. On the other hand, sensitive drugs such as peptides, proteins, and nucleic acids are increasing their relevance and this effect is due to the fact that potential treatment options have a medical unmet demand which is not covered by classical drug therapies. For these active pharmaceutical ingredients (API), additional conditions must be taken into consideration.
Polysaccharides Polysaccharides are polymeric biomaterials widely studied for drug delivery applications. These compounds can be produced by from microorganisms, animals, and plants; hence, they represent a renewable resource and are regarded as economical and environmentally favorable. Polysaccharides used for these applications combine several advantageous properties both clinical and physicochemical. Among the former can be mentioned low toxicity, good biocompatibility, and biodegradability, and among the latter, high stability and hydrophilicity. In addition, natural polysaccharides can be modified to improve, enhance, or avoid any molecular feature necessary to reach the ultimate objective. Thus, in this section we will focus on their main structural features and their importance in polysaccharides-based drug delivery systems.
40 Biopolymers for Medical Applications
Cyclodextrins Cyclodextrins (CDs) are crystalline, non-hygroscopic, and cyclic oligosaccharides derived from starch. The first reference to a substance which later proved to be a CD, was published by Villiers, in (Villiers ) and was named “cellulosine” by Schardinger (Schardinger ). He also observed that two distinct crystalline “cellulosines” were formed, being probably α- and β-CDs. However, it wasn’t until the s when preparations of CDs, their structure, physical and chemical properties, as well as their inclusion complex forming properties were discovered (Szejtli ). Chemically, CDs are cyclic oligosaccharides containing at least six D-(+)glucopyranose units attached by α (1→4) glucoside bonds. The three natural cyclodextrins, α, β, and γ; differ in their ring size, solubility, and their content of glucose units, having 6, 7, or 8, respectively (Rowe et al. ). However, Endo et al. () established an isolation and purification method for several kinds of large ring CDs and they also obtained a relatively large amount of δ-CD (Cyclomaltonose) with nine glucose units. Furthermore, both their molecular weight and their size cavity are increased from α to δ-CD. On the other hand, it must be considered that CDs can be modified to improve some of their physicochemical or toxicological features, and also to enhance physical and microbiological stability. From β-CD, numerous derivatives were obtained by chemical modification such as hydroxyethyl-β-CD, hydroxypropylβ-CD, sulfobutylether-β-CD, methyl-β-CD among others. Cyclodextrins have lipophilic inner cavities and hydrophilic outer surfaces, and are capable of interacting with a large variety of guest molecules to form non-covalent inclusion complexes. The lipophilicity of the cavity is due to the arrangement of hydroxyl groups within the molecule. They are chemically stable in neutral and basic conditions and undergo non-enzymatic hydrolysis in acidic conditions. According to the classification given by different pharmacopoeias, CDs are used as solubilizing and/ or stabilizing agents. CDs have been playing a very important role in formulation of poorly water-soluble drugs by improving apparent drug solubility and/or dissolution through inclusion complexation or solid dispersion (Tasić et al. ). In this context, the importance of CDs applications is found in the design of various novel delivery systems such as liposomes, microspheres, microcapsules, and nanoparticles (Challa et al. ). There are some factors influencing the formation and stability of inclusion complexes such as the presence of charge when the complexes drug-CDs are formed, temperature changes, addition of other co-polymers, and the preparation method of the formulation (Nagase et al. ; Mura et al. ). β-cyclodextrins is the least expensive and therefore the most commonly used CD, even though it is the least soluble. Hence, it is primarily used in tablets and capsules formulations. In the case of parenteral formulations, α-CD is mainly used; however, resulting from having the smallest cavity among CDs, it can only form inclusion complexes with small-sized molecules. In contrast, γ-CD has the largest cavity and it can be used to form inclusion complexes with big molecules (Rowe et al. ). β-cyclodextrin may be used to develop an oral tablet formulation by means of wetgranulation and, on the other hand, by direct-compression processes. In parenteral formulations, CDs have been used to produce stable and soluble preparations of drugs that would otherwise have been formulated using a non-aqueous solvent.
Biopolymers used in Drug Delivery Systems 41
In eye drops formulations, CDs form water-soluble complexes with lipophilic drugs such as corticosteroids and vitamin D2 (Palmieri et al. ). They can increase the water solubility of the drug, enhance drug absorption into the eye, improve aqueous stability, and reduce local irritation (Loftsson and Stefánsson ). CDs have also been used in the formulation of solutions (Prankerd et al. ), suppositories (Szente et al. ; Szente et al. ), and cosmetics (Amann and Dressnandt ; Buschmann and Schollmeyer ). In addition, other kind of drug delivery systems has been designed with CDs to carry sensitive drugs. In this context, it has been reported that their use as non-viral vectors for gene delivery induced an increment in the transfection efficiency, with high levels of reporter gene expression and also with low toxicity (Redenti et al. ; O’Neill et al. ; Lai ). Promising carriers for anti-cancer drug delivery in tumor therapy have been reported by Tan et al. (Tan et al. ). This research has shown greater control of drug release by incorporation of CDs into polymeric drug delivery systems. Here, 5-fluorouracil, doxorubicin, and vinblastine are carried into a complex built by a covalently linked reaction between chitosan and carboxylic acid group of CDs. These cyclic polysaccharides are able to have close cellular interactions, which make them a suitable option for carrying peptides, oligonucleotides, and proteins. All toxicity studies have demonstrated that, when orally administered, CDs are practically non-toxic due to the lack of absorption in the gastrointestinal tract (Irie and Uekama ). However, lipophilic methylated CDs are surface active and they are, to some extent (~ 10%), absorbed in the gastrointestinal tract. Consequently only limited amounts of these lipophilic CD derivatives can be included in oral formulations and they are unsuitable for parenteral formulations. Furthermore, α, β, and methylated CDs are nephrotoxic and should not be used in parenteral formulations. In contrast, γ-CD, 2-hydroxypropyl-β-CD, sulfobutylether β-CD, sulfated β-CD, and maltosyl β-CD appear to be safe even when administered parenterally.
Cellulose and derivatives Cellulose is the most abundant substance in the biosphere; it is the main molecule of cell walls of higher plants and it is also produced by some algae, fungi, protozoans, tunicates, and bacteria. The molecule is a linear polymer of D-anhydroglucopyranose units linked together by (1→4)-β-glycosidic bonds. The extensive intra- and intermolecular hydrogen bonding between the individual chains (Hinterstoisser and Salmén ) make it insoluble in water and most common solvents (Rowe et al. ). In order to improve water solubility, various cellulose derivatives have been synthesized by etherification of the hydroxyl groups on anhydroglucose units of cellulose. Hence, the most widely used are methyl cellulose, carboxymethyl cellulose, hydroxypropyl cellulose, hydroxypropyl methyl cellulose (HPMC), hydroxyethyl cellulose, and ethylhydroxyethyl cellulose. Bacterial cellulose (BC), originally reported by Brown (Brown ), has attracted considerable attention in both drug delivery and biomedical fields due to its unique fibrillar nanostructure, high water holding capacity, high degree of polymerization, high mechanical strength, and degree of crystallinity, as well as its availability for being effectively produced in high purity by
42 Biopolymers for Medical Applications Acetobacterxylinum (Esa et al. ). Cellulose and its derivatives have been widely used in the pharmaceutical industry due to their ability to swell in contact with water and their high compatibility which makes them suitable as a binder/diluent and also as an disintegrant agent in oral tablets and capsules, depending on the substitution degree (SD). Cellulose derivatives are able to form hydrogels and therefore, are appropriate as suspending or viscosity-increasing agents for oral suspensions. Other kind of applications such as wound dressing, transdermal patches, and ophthalmic preparations have also been reported for some of these derivatives; these traditional applications have been extensively discussed in literature (Shokri and Adibkia ; Kamel et al. ; Rowe et al. ). In native cellulose, the adjacent chains of the polymer fit closely together in an ordered crystalline region, resulting in a product with high strength. Different degrees of crystallinity can be found according to the source and degree of processing of the raw material which, in turn, varies the mechanical properties of the final product. Young’s Modulus, for example, can vary from to GPa in cellulose obtained from wood fibers (Wang ). As mentioned before, cellulose derivatives are able to form gels and a wide range of mechanical properties can be obtained depending on the SD, nature of the solvent, and concentration (Jain et al. ). Bacterial cellulose exists as a basic fibrillar structure times smaller than plant cellulose and highly crystalline (Esa et al. ). Its reported elastic modulus was approximately 10 GPa (Iguchi et al. ; Svensson et al. ), which is comparable to that of the articular cartilage, and this is extraordinary large for an organic material with a two dimensional structure. Therefore, bacterial cellulose is a suitable candidate to be applied in tissue engineering and also to develop membranes for controlled release for drugs. Cellulose and its ethers commonly used in the pharmaceutical industry induce negligible foreign body and inflammatory responses, being generally regarded as a non-toxic and non-irritant material. However, oral consumption of large amounts of them may have a laxative effect. In vivo biocompatibility of BC implanted subcutaneously in rats for up to 12 weeks has been studied, proving good integration into the host tissue, and no signs of inflammation or foreign body response (Helenius et al. ). Regarding their degradation, these materials are considered non- or slowly biodegradable in vivo, due to the lack of cellulase enzymes in animals (Dugan et al. ). Bacterial cellulose and its ethers can be used to create “smart” materials, which present differential behaviors under environmental stimulus. This fact constitutes a very versatile feature for drug delivery systems. Hydrogels, membranes, self-assembled systems, and nanocomposites are among the most widely investigated alternatives (Edgar ). In the particular case of BC, sources directly influence structure because its properties vary with bacterial strain and culture media; therefore, its knowledge can be used to tailor the material for different drug delivery purposes. A cellulose nanofibers–titania composite is currently under development for drug delivery of anesthetics, analgesics, and antibiotics (Galkina et al. ). This material is presented as an interesting alternative for wound-dressing with transdermal drug delivery properties. Sodium diclofenac, D-penicillamine, and phosphomycin were used as model drugs, showing uniform distribution within the nanofiber film and long-term drug release with different profiles: the quickest release was observed for
Biopolymers used in Drug Delivery Systems 43
the painkiller, a slower one for the anti-inflammatory agent, and the longest release took place for the strongly chemisorbed antibiotic agent. Polymer-nanoparticle (PNP) hydrogels were recently developed by mixing HPMC and carboxy-functionalized polystyrene nanoparticles (PSNPs) by Appel et al. ( ). Interestingly, these self-assembled hydrogels are able to flow under applied shear stress, followed by rapid self-healing when the stress is relaxed, allowing its safe subcutaneous injection. Moreover, owing to the hierarchical structure of the gel, molecular delivery was controlled allowing differential release of multiple compounds (tested with hydrophobic and hydrophilic therapeutic models, in both in vitro and in vivo systems). BC membranes produced from Gluconacetobactersacchari have been developed as systems for topical and transdermal drug delivery; using lidocaine hydrochloride and ibuprofen as models for hydrophilic and hydrophobic drugs, respectively. Trovatti et al. (Trovatti et al. ) proved that permeation rate is higher for the hydrophobic drug than for the hydrophilic one, demonstrating that these delivery systems can be tuned to modulate the bioavailability of drugs for percutaneous administration, having the advantage of using a membrane that is also able to absorb exudates and to adhere to irregular skin surfaces. Recently, Amin et al. () combined BC obtained from cream of coconut (also known as nata de coco) and different proportions of acrylic acid to fabricate thermally stable hydrogels with moldable pore sizes. Therefore, in vitro drug release studies with bovine serum albumin showed a thermo- and pH-responsive behavior of the hydrogels suggesting them as a suitable system for temperature-controlled delivery of protein-based drugs.
Guar gum Guar gum is a hydrocolloidal galactomannan that structurally comprises long and straight chains of (1→4)-α-D-mannopyranosyl units linked together by (1→4)-β-Dgalactopyranosyl units by (1→6) linkages. The ratio of D-mannose to D-galactose of guar gum has been known to be approximately and A single molecular weight is estimated to be in the range of kDa to kDa (Schierbaum ). Guar gum is obtained by grinding the endosperm portion of a leguminous plant called Cyamoposistetragonolobus (L.) Taub. that is grown mainly in India, Pakistan, and United States to produce seeds used for human and animal food (Rowe et al. ). Additionally, guar gum exhibits potential applications in various fields such as drugs, cosmetic, food, and textile industries. Different guar gum composites have been studied to improve the properties of conventional food technologies such as thermoplastic polymers and fillers (Funami et al. ). Generally, this hydrocolloidal agent is used as an additive in the food industry to facilitate gelling, thickening, firming, and emulsification of food products but a high viscosity (2, to 3, mPa.s) is reached when its concentration is above 1% w/v and this is a limiting factor for its use in food products (McCleary ), resulting in liquid products which are highly viscous. In order to reduce its viscosity, it may be processed into partially hydrolysed guar gum (PHGG), which is obtained by controlled partial enzymatic hydrolysis of guar gum seeds (Flammang et al. ). PHGG has the same chemical structure as the original guar gum, but with a significantly reduced molecular weight of around 20 kDa and one-tenth of the original chain length (Yoon et al. ). Guar gum produces
44 Biopolymers for Medical Applications a pseudoplastic viscous solution when hydrated in cold water and it also has a lowshear viscosity greater than other hydrocolloids (Brosio et al. ). Mechanical properties studies of low concentrated and almost monodisperse guar gums suspensions have shown that there is a plateau in the storage modulus at a frequency of ω = It was demonstrated that guar gum enhance rheological and large deformation properties of soybean β-conglycinin gel. Moreover, due to increasing concentrations of guar gum the elastic modulus of the composite is also increased (Zhu et al. ). Guar gum has many desirable properties for drug delivery applications and is generally used as a sustained release excipient owing to its high viscosity, low cost, and commercial availability. This compound forms a hydrophilic matrix that could be used as oral carrier for controlled delivery of drugs with varying solubility; therefore, its gelling property retards the release of drugs from the dosage form and it is susceptible to degradation in the colonic environment (Jain et al. ; Bhalla and Shah ; Krishnaiah et al. ). In order to improve its applications as drug delivery carrier, several chemical modifications have been made on guar gum such as cross-linking with borax, glutaraldehyde, and trisodiumtrimeta phosphate. These cross-linked formations reduce its enormous swelling. Furthermore, for the preparation of different guar gum-based systems, combinations with other natural or synthetic polymers such as polyacrylamide, polyvinylpyrrolidone, ethyl cellulose, hydroxypropyl methyl cellulose, polyvinyl alcohol, polyacrylic acid, sodium carboxymethyl cellulose, sodium alginate, xanthan gum, chitosan, carrageenan, hydroxypropyl cellulose, and carboxymethyl cellulose could be considered. In recent years, stimuli-responsive micro and nanogels have been designed, which respond to external stimuli such as pH, ionic strength, temperature, and electric current in order to deliver a specific drug dosage in a specific site (Prabaharan ). George et al. (George and Abraham ) have designed a pH sensitive system made of alginate-guar gum hydrogel cross-linked with glutaraldehyde for controlled delivery of proteins. These authors found that the presence of this modified guar gum increases the entrapment efficiency and prevents the rapid dissolution of alginate in a basic pH as the pH found in the intestine, ensuring a controlled release of the entrapped drug. Furthermore, guar gum has been used to develop sustainedrelease devices of water soluble antihypertensive drugs such as nifedipine, diltiazem hydrochloride, and other such as ketoprofen. Recent studies carried out by Das et al. (Das and Subuddhi ) have shown very encouraging results using pH-responsive hydrogel systems based on guar gum, poly(acrylic acid), and cross-linked cyclodextrin with tetraethyl orthosilicate for intestinal delivery of dexamethasone. They found that as the guar gum content increases, the rate of drug release decreases considerably and the drug release is prolonged. On the other hand, considering that guar gum and its derivatives have good film forming and controlled drug release abilities, they have the potential to be used as transdermal drug delivery devices (Altaf et al. ). The physiological effects of guar gum have been extensively studied, first on animals and then on humans. Studies revealed that guar gum is non-toxic; additionally, it does not have carcinogenic or teratogenic effects (Melnick et al. ). In addition, due to its high biocompatibility and biodegradability it is extensively used as a biomaterial. Guar gum cannot be degraded in the small intestine; however, in the large intestine, the glycosidic linkage present in guar gum is degraded due to the microbial
Biopolymers used in Drug Delivery Systems 45
enzyme present there (Tomlin et al. ). One of the bacteria responsible for guar gum degradation is Clostridium butyricum (Mudgil et al. ).
Carrageenan Carrageenans are a family of high molecular weight sulfated polysaccharides obtained by extraction from some members of the algae class Rhodophyceae (red seaweed). They are composed of galactose and anhydrogalactose units, linked by glycosidic unions. Depending on the method and the algae from which carrageenan is extracted, three main types of carrageenans can be obtained: kappa (κ), iota (ι), and lambda (λ) (Sankalia et al. ). The primary differences which influence the properties of carrageenan type are the number and position of sulfate ester groups as well as the content of 3,6-anhydrogalactose. Typically, commercial λ-carrageenan contains approximately 35% sulfate ester by weight and little or no 3,6-anhydrogalactose, ι-carrageenan contains about 32% sulfate ester by weight and approximately 30% 3,6-anhydrogalactose, and κ-carrageenan contains 25% sulfate ester by weight and approximately 34% 3,6-anhydrogalactose (Jana et al. ). Even though these three types of carrageenans have similar characteristics in their chemical structure, it was reported that higher levels of sulfate ester resulted in lower solubility temperature and lower gel strength (Necas and Bartosikova ). Moreover, given the ionic nature of the polymer, its gelation is strongly influenced by the presence of electrolytes and, among these three types, only κ- and ι-carrageenans evidence gel-forming ability; the κ-carrageenan gels are firmer than those obtained with ι-carrageenan, which are more elastic and soft (Bixler ). Carrageenan is widely used in the food industry due to its excellent gelling, thickening, emulsifying, and stabilizing abilities. Furthermore, it is also applied in other commercial products such as cosmetics, air freshener gels, and fire fighting foam (Necas and Bartosikova ), and recently, it is increasingly being used in pharmaceutical formulations as well (Li et al. ). Mechanical and rheological properties of carrageenan gels have been widely studied in the presence of ions. Carrageenans exist as a random coil at high temperature; and temperature reduction induces the formation of double helices. This leads to the formation of small independent domains involving a limited number of chains via intermolecular association. However, when cations are incorporated into carrageenan suspensions, helices of different domains aggregate to enable long range cross-linking which forms a cohesive network and this quaternary structure contributes to the final properties of the resultant gels (Morris et al. ). However, Thrimawithana et al. have demonstrated that increasing ion concentrations beyond a threshold also had a negative impact on some mechanical properties of carrageenan gels (Thrimawithana et al. ). Different carrageenan drug delivery systems have been developed, and they are mainly used as a polymer matrix in oral extended-release tablets (Hariharan et al. ), as a novel extrusion aid for the production of pellets (Thommes and Kleinebudde), and as a carrier in micro and nanoparticles systems (Cheng et al. ). In addition, based on their strong negative charge, carrageenans have been used as gelling and viscosity enhancing agents for the design of drug controlled-release systems which could be used, for example, as prolonged retention systems. It can be found combined
46 Biopolymers for Medical Applications with locust bean gum and gellan gum, in chitosan/carrageenan nanoparticles, agarose/ carrageenan hydrogels, and carrageenan/gelatin mucoadhesive systems, among others (Jana et al. ). In particular, κ-carrageenan is widely used due to their hydrogen bond-forming capability in several sites which impart bioadhesive properties to the final formulation. Moreover, its mucoadhesive property could be further enhanced by the negative charge of the sulfate group in the carrageenan structure; as a consequence, ionic bonds are formed with the positively charged mucin present on the buccal mucosa (Kianfar et al. ). Carrageenans have shown several potential pharmaceutical properties including anticoagulant, anticancer, antihyperlipidemic, and immunomodulatory activities (Wijesekara et al. ; Campo et al. ). Comparison of a variety of compounds reveals that carrageenan is an extremely potent infection inhibitor for a broad range of sexually transmitted human papillomavirus (Buck et al. ); in fact, it was reported that carrageenans-based gels used in sexual lubricant may offer protection against human papillomavirus transmission (Campo et al. ; Roberts et al. ). Additionally, Rocha de Souza et al. (Rocha de Souza et al. ) found a positive correlation between sulfate content and antioxidant activity of carrageenan. In contrast, it is known that carrageenans induce inflammatory responses in laboratory animals (Tobacman ; van der Kam et al. ; Sadeghi et al. ); and some studies showed that long-term administration of carrageenans in animal models caused ulcerative colitis or intestine mucous membrane damage. It was also reported that these compounds promote tumor growth (Tobacman ). Finally, specialists concluded that it is necessary to perform more epidemiological and essential studies to evaluate the safety of carrageenan (Li et al. ).
Hyaluronan Hyaluronan (HA), also known as hyaluronic acid or hyaluronate, is a negatively charged, linear and unbranched polysaccharide with a simple chemical structure consisting of alternating units of D-glucuronic acid and N-acetyl-D-glucosamine. It is considered the largest glycosaminoglycan, with a molecular weight ranged from to kDa (Rowe et al. ). HA was first isolated from bovine vitreous humor in by Meyer and Palmer (Meyer and Palmer ). It is currently extracted from animal waste (e.g., rooster comb) and it has been obtained by different biotechnological methods such as microbial (Widner et al. ) and enzymatic production (Kooy et al. ). HA has been widely studied because of its unique properties, such as aqueous solubility, and its viscoelastic properties that allow it to form highly viscous solutions and three dimensional structures. It has been reported that HA plays an important role in the structure and viscoelastic properties of different tissues such as skin and articular cartilage (Nair and Laurencin ). Regarding its mechanical properties, a single HA molecule is very flexible and its viscoelasticity is affected by the pH and ionic strength of its environment (Kobayashi et al. ). Furthermore, HA has a pKa value of about and therefore, a change in pH will affect the extent of ionization of the HA chains (Mi et al. ). To improve its mechanical properties HA can be chemically modified or cross-linked. Generally carboxylic acid and alcohol groups have been modified by esterification and by cross-
Biopolymers used in Drug Delivery Systems 47
linkers such as dihydrazide, dialdehyde, divinylsulfone, diglycidyl ethers, or disulfide (Jeon et al. ). Several investigations have shown that parameters such as elastic modulus, shear modulus, viscosity, and viscoelasticity depend on HA concentration and cross-linked degree of hydrogels (Balazs and Denlinger ; Altman and Moskowitz ; Nijenhuis et al. ). Mainly, it is possible to increase the hydrogel’s storage modulus by increasing the gel precursor solution’s HA concentration, with stiffness ranging from Pa to Pa (Lam et al. ). Although, a research have shown that the elastic modulus rises while HA concentration keeps below 20%, however above this value the elastic modulus decreases due to a significant growth of swelling of the hydrogel (Jeon et al. ). HA has a great potential to be used as a specific-target carrier and long-acting delivery systems of various molecules including proteins, peptides, and nucleotides. In encapsulation of proteins, HA provides a well-hydrated environment, helping them to retain their biological activity and to limit denaturation (Hoffman ). Recently, HA has been investigated as a drug delivery agent for various routes of administration, including dermal, ophthalmic, nasal, pulmonary, parenteral, and topical. Regarding dermal applications, Solaraze®, a HA gel with a commercial drug (diclofenac), was developed for the topical treatment of actinic keratosis. In this formulation, HA enhances significantly the partitioning of diclofenac into human skin and its retention and localization in the epidermis (Del Rosso ). Due to its mucoadhesive capacity, microspheres delivery systems made of HA have been used as a vehicle for topical ophthalmic drugs (Lim et al. ). Microspheres have also been used experimentally as delivery devices for nerve growth factors (Mohammad et al. ), and as a nasal delivery system for insulin (Illum et al. ). Moreover, paclitaxel and doxorubicin, both anticancer drugs, have been chemically linked to HA systems and it was found to selectively target human cancer cells because HA is the main ligand for CD44 and RHAMM receptors, which are over-expressed in a variety of tumor cell surfaces (Culty et al. ) including colon cancer (Tanabe et al. ), human breast epithelial cells (Bourguignon et al. ), lung cancer (Matsubara et al. ), and acute leukemia cells (Yokota et al. ). HA biocompatibility, non-toxic properties and lack of immunogenicity, make it an ideal scaffold for tissue engineering. In terms of biodegradation in human tissues, HA has a half-life from less than 1 to several days. Once it reaches the blood stream, about 85–95% is eliminated by the liver; while kidneys extract 10% but excrete about 1–2% in urine (Fraser et al. ). On the other hand, it was shown that HA is related to different kinds of diseases. Elevated proportions of HA, HA synthase, and hyaluronidase are involved in cell migration and metastasis at various stages of cancer progression (Lokeshwar et al. ). Moreover, HA oligomers formed by hyaluronidase degradation are pro-angiogenic (Liu et al. ) and have inflammatory and immuno-stimulatory properties (Xu et al. ).
Alginates Alginates are mainly obtained from cell walls of different species of brown algae belonging to Phaeophyceae class. Since that these algae are harvested from nature, there is a variety of types of alginates depending on the selected species, the time of
48 Biopolymers for Medical Applications collection and the region where each species is found. In this context, alginate allows significant variation of material properties solely based on polysaccharide composition (Grasdalen et al. ) and these properties allow tailoring of a variety of biomaterials suitable for tissue engineering. Alginates are water soluble and anionic linear hetero-polysaccharide composed of two different monomers (1→4)-β-linked: the β-D-mannuronic acid (M) (pKa = ) and the α-L-guluronic acid (G) (pKa = ). Therefore, if the pH of the alginatecontaining solution is lowered below the pKa of the constituting acids, phase separation or hydrogel formation occurs. Generally, they are composed of three different forms of polymer segments: consecutive G residues, consecutive M residues, and alternating MG residues. The resulting variability of alginate composition significantly affects its physical properties, for example: G rich domains with more than 6–10 residues bind divalent ions (Ca2+, Ba2+, etc.) forming cross-links between different chains in a so-called ‘egg-box arrangement’ (Grant et al. ). These polysaccharides are insoluble in aqueous-alcoholic solutions and also in organic solvents. Their use has been widely diffused in different industries such as pharmaceutical ones. Here, they are part of tablets and ophthalmic preparations, among others; however, nowadays the most important field of interest is the production of hydrogels. Alginates can be found forming salts with different cations: ammonium, potassium, sodium, and propylene glycol. Typically, alginate salts are prepared at 1% w/v in aqueous solution, and at 20°C they have a viscosity of 20– mPa x s. The viscosity of these gels may vary depending upon concentration, pH, temperature, or the presence of metal ions, for instance, above pH 10, their viscosity decreases (Rowe et al. ). The design of drug delivery systems based on alginates can be performed due to the sol-gel transition behavior of the alginate in the presence of divalent cations such as Ca2+, Sr2+, and Ba2+. After this reaction, the water solubility of the monovalent alginate decreases converting it into a water insoluble salt. Furthermore, GG blocks have shown to be more rigid than MM blocks because of axial–axial or diequatorial linkage (Rinaudo ). Therefore, gels formed from alginate with a high M content are typically softer and less porous than high G alginate gels, showing a higher degree of swelling and shrinking. Consequently, a high G alginate is advantageous in terms of maintenance of form and integrity over extended time (Simpson et al. ; De Vos et al. ). In drug delivery systems’ design, alginates are used as a stabilizing agent, suspending agent, tablet and capsule disintegrant, tablet binder, and viscosity increasing agent (Rowe et al. ). Moreover, different systems with applications in regenerative medicine, such as microspheres, microcapsules, sponges, foams, and fibers, have been developed. Alginates may be used to develop delivery systems for cationic polyelectrolytes and proteoglycans through simple electrostatic interactions due to its pH dependent anionic nature (Yu et al. ). Recently several different formulations were developed where this polymer was included; however, only two of them will be highlighted in this section: the development of nanoparticles and the production of hydrogels. The most important feature of these hydrogels is their adhesion to different tissues. The adhesive devices can be formulated for drug release into different mucosal tissues such as oral and vaginal ones, and can be developed as in situ-formed gels to be applied in buccal and ophthalmic mucosa to controllably
Biopolymers used in Drug Delivery Systems 49
release the API. The esophageal bio-adhesion of alginate suspensions may provide a barrier against gastric reflux or site-specific delivery of therapeutic agents (Richardson et al. ). Furthermore, nasal delivery systems based on mucoadhesive microspheres (Gavini et al. ), and a freeze-dried device intended for the delivery of bone-growth factors have been reported. One of the most important applications of the alginates is the development of hydrogel systems for delivery of sensitive drugs such as proteins and peptides (Gombotz and Pettit ). In these groups of drugs are included several proteins such as immunoglobulin, fibrinogen, insulin, melatonin, heparin, and hemoglobin. Related to peptides delivery, this polymer was blended with another natural polysaccharide, guar gum (George and Abraham ), to overcome the rapid dissolution of the alginate at high pH, a major limitation during delivery of peptide drugs (Yu et al. ; Li et al. ). In addition, sodium alginate microspheres have been used in the preparation of a DNA vaccine for the foot-mouth disease (Liu et al. ), and therefore, the incorporation of functional small interfering siRNAs proves the significance of this polyanionic polysaccharide. Moreover, the use of alginatebased delivery systems for distribution of cell induction ligands and also for bioactive molecules for signaling was reported (Kulkarni et al. ). Alginates are generally regarded as non-toxic and non-irritant materials. However, biocompatibilities of alginates were significantly affected by their composition and their molecular weight. In this context, it was suggested that unbound alginate oligosaccharides may be responsible for the induction of inflammatory reactions, and the purification of the alginate reduces the low molecular weight fraction which may lead to improved biocompatibility. In this context, their biodegradability strongly depends on the characteristics of each polymer and hence, the biodegradability of high molecular weight alginates is hampered when they are parenterally administered as they may exceed the threshold of renal clearance. Due to that fact, to improve the biodegradability of alginates, low molecular weight polymers are cross-linked with biodegradable molecules to obtain high molecular weight alginates with enhanced renal clearance. Nevertheless, this strategy has a disadvantage related with the high purification process required to use these assembled polymers (Germershaus et al. ).
Proteins Essentially, proteins are a polymeric arrangement of amino acids in a three-dimensional folded structure forming the major structural components of many human tissues; they also are one of the most important classes of identified biomolecules. There are at least two fundamental factors in the characterization of proteins. The first one is related to their morphology, which affects their solubility and the other is related to their biological function, that is, if a protein is a structural protein or a transport protein. Morphologically, proteins are divided into fibrous and globular proteins. The main difference between these two kinds of proteins is that fibrous proteins generally have only primary and secondary structures; whereas globular proteins have also tertiary and sometimes quaternary structures. In contrast to globular proteins, fibrous proteins provide mechanical and structural support in the body whereas globular proteins are related to transport function (Nelson et al. ). Fibrous proteins form
50 Biopolymers for Medical Applications the extra cellular matrix and/or basal lamina of the cells in different tissues such as ligament, bone, and skin. As mentioned above, proteins are the major component of natural tissues; therefore, this is one of the reasons why proteins and other amino acid-derived polymers have been a preferred biomaterial for medical uses such as haemostatic agents, scaffolds for tissue engineering, and drug delivery vehicles (Meinel et al. ). The use of biodegradable hydrogels based on proteins as drug delivery systems has a particular interest due to their biocompatibility and their relative inertness. For this reason, in this section we will show examples related to proteins forming hydrogels. Finally, it is important to remark that protein-based biomaterials are known to undergo naturally-controlled degradation processes.
Collagen I Collagen is the main structural protein in vertebrates, and it represents approximately 30% of all body proteins. Collagen’s family is characterized by a unique triple-helix configuration of three polypeptide subunits known as a α-chain. Due to differences in the helix’s lengths and in the nature of the non-helical portions have been separated, at least, 13 types of collagens. The basic collagen molecule is formed by more than amino acids which develop a unique triple-helix sequence, which in turn is composed by α-chains. A right-handed helix is formed by 3 α-chains (Friess ) and it is stabilized by hydrogen bonds, intra-molecular van de Waals interactions (Brinckmann et al. ), and some covalent bonds (Harkness ). The helix has an average molecular weight of kDa, a length of nm, and a diameter of nm (Friess ). Moreover the helices are associated into right handed microfibrils (40 nm in diameter) which are assembled into fibrils (– nm in diameter). Finally, a group of fibrils form collagen fibers (He, Mu et al. ). In addition, a distinctive collagen marker is the presence of 4-hydroxyproline in the triple-helix (Cen et al. ). The unique physiological characteristics of collagen and its capability to develop biomaterials derive from the structural complexity of the collagen molecule (Friess ). Reconstituted collagen fibrils have mechanical properties sensitive to their hydration state (van der Rijt et al. ) and are able to be manipulated by controlling their aqueous environment (Grant et al. ). Although it has been reported that a tendon’s collagen fibrils form a rope-like structure, mechanical properties at a sub-fibrillar level are not fully understood (Bozec et al. ). The self-assembly mechanism generates a homogeneous single fibril of collagen (Yang et al. ). However, the alignment of collagen molecules along the longitudinal fibril direction could cause a mechanical anisotropy. Tensile test has been performed on single collagen type I fibrils. For example, a Young’s modulus value of 5 ± 2 GPa was found for dry fibrils of type I collagen and when these fibrils were immersed in phosphate-buffered saline, its elasticity decreased to to GPa. These results support the hypothesis that the anisotropy of collagen arises from the alignment of sub fibrils along the fibril axis (Yang et al. ). Atomic Force Microscopy has been used to infer the elasticity of these structures and thus, the modulus of several collagen fibrils in air and aqueous fluid were compared. Therefore, this study (Atomic force microscopy) was carried out to describe the effect of hydration on the mechanical response (Grant et al. ).
Biopolymers used in Drug Delivery Systems 51
This behavior is due to that the cross-linking process increases the stiffness of the material and also sterilization with glutaraldehyde. On the other hand, thermal sterilization can decrease its stiffness (Lesiak-Cyganowska et al. ; Angele et al. ; Friess ). Different kinds of collagen such as powders, liquids, solid compressed masses, membranes, or sponges have been reported. The obtained behavior, which is result of a study of different drug delivery systems, must be in concordance or should explain the properties of these systems (Ruszczak and Friess ). Nowadays, different efforts to attach drugs or polymers structures to collagen have been described in literature. Controlling drug conjugates would allow the immobilization of therapeutic enzymes or drug delivery; in this regard, kanamycin and pilocarpine have been investigated as conjugate options (Friess ). Sheets, tubes, sponges, powders, fleeces, injectable solutions and dispersions are some of the forms in which collagen can be processed (Chvapil et al. ; Byrom ; Fu Lu and Thies ). Inserts and shields are among the most studied drug carrier applications of collagen. They are used for drug delivery above the corneal surface or for forming the cornea itself (Friess ). Inserts are cut from films or fabricated as molded rods prepared out of mixtures of drug and collagen by air-drying (Rubin et al. ). There are different kinds of injectable systems carried out as gels. One of them is initially liquid, which when is injected inside the eye, coagulate in it, turning into a gel. These gels are able to remain longer than liquid formulations and could achieve a sustained delivery of non-steroidal anti-inflammatory drugs or antibiotics (Friess ). A formulation of collagen with epinephrine for local vasoconstriction was tested aiming to enhance local drug retention, minimization of systemic side effects, and reduction of the required dose (Friess ). In order to deal with a key complication in surgery, which is the local treatment of soft tissue infections, combinations with antibiotics are being developed (Taylor ). Collagen products are appropriate for medical uses because of their low antigenicity, excellent biocompatibility, low immunoreactions, clear association with other biological species and polyelectrolyte behaviour. In addition, final products such as threads, sponges, films, and drug delivery systems are important considering the reconstitution of collagen into native fibres starting from collagen solutions (Chirita ). Since there are similarities between amino acids of collagen of different animal species and the low content of aromatic residues, generally, collagen fibres behave as a non-antigenic protein. However, there are massive concerns about massive immune responses or autoimmune diseases triggered by antibodies which may produce cross-reactions by collagen derived from animal tissues (Friess ). Despite their ability to interact with antibodies, collagens are weakly immunogenic in comparison to other proteins (Byrom ). Antigenic determinants of collagen can be classified into three following categories: 1) tridimensional conformation recognition by antibodies; 2) recognition of amino acid sequence located within the triple helical portion (Lynn et al. ); 3) recognition of terminal and non-helical regions (Lee et al. ; Chevallay and Herbage ; Hsu et al. ; Kikuchi et al. ). During the in vivo process, collagen is infiltrated by inflammatory cells such as fibroblasts, macrophages, or neutrophils, which secrete enzymes, activators, inhibitors, and regulatory molecules (Byrom ). Water, enzymes, and the digestion of linkages
52 Biopolymers for Medical Applications are required for collagen degradation. After a process of swelling by exposure to water, collagen is only completely digested by specific collagenases and cleaving enzymes (Harrington ). Collagen is degraded by endopeptidases and some non-enzymatic degradation mechanisms like hydrolysis (Okada et al. ). The connective tissue is digested by proteases, whereas metalloproteinases (MMPs) carry out the extracellular matrix degradation. Cysteine and aspartic proteases (cathepsins) degraded connective tissue intracellularly, while serine and MMP matrix degrade it extracellularly (Shingleton et al. ).
Gelatin Gelatines are proteins derived from collagen, soluble in warm water, and with molecular weights ranging from ~ 20 to kDa; and like in collagen, glycine (~ 24%), proline (~ 17%), alanine (~ 14%), and hydroxyproline (~ 10%) are the four most abundant amino acids. The essential amino acid, tryptophan, is not found in gelatin. The helical conformation can reach 70% and may be found in the gel form of gelatin. These regions have many inter and intramolecular associations and the α-chain of gelatin, which has a highly ordered sequence of amino acids, behaves like a randomcoil polymer in the solution. The gel structure is a combination of fine and coarse interchain networks, and the ratio is defined as a proportional relation between fine chains and coarse depends on the gel formation temperature. In addition, the rigidity of the gel is approximately proportional to the square of the gelatin concentration (Gurr and Mülhaupt ). The gelatines are known as type A and type B depending on the production process; thus, if it is treated with acid, it is called type A, and if it is alkali treated, it is type B. These treatments cause de-amidation of asparagine and glutamine resulting in an increase in the number of acids, aspartic and glutamic (Eysturskarð et al. ). Physical-chemical and rheological properties depend on their amino acid content. Rheological properties are important considerations in process design, evaluation, as well as in modelling. Hence, these are properties that indicate the quality of the product. Dynamic viscoelastic properties and flow properties provide information about their molecular arrangements. Hence, it is important to assess the rheological properties of gelatin along with its physical-chemical properties (Chandra and Shamasundar ). Mechanical properties such as the dynamic storage modulus and bloom value for gelatines are dependent on the average molecular weight and its distribution, whereas the content of the amino acids affects their physical properties. Low molecular weight fractions of gelatin block the helix assembly, perturbing the formation of the network. Both proline and hydroxyproline have stabilizing effects on the helices due to their ring conformation, and they also influence the flexibility of the chains. Consequently, the lower content of these amino acids increases the flexibility and, as a result, facilitates the reorganization of the network (Eysturskarð et al. ). Gelatin may be loaded with charged biomolecules due to its intrinsic features, and it can be used as a drug delivery carrier. The drug loading efficiency depends on the treatment that collagen received to produce the gelatin, that is, alkaline or acidic, and also the nature of the guest drug. The cross-linking and the gelatin molecular weight can be tuned to control the release kinetics of gelatin. This polymer gives
Biopolymers used in Drug Delivery Systems 53
the possibility to control both aspects, that is, drug loading and release kinetics (Santoro et al. ). Oral administration is the main use for gelatin capsules. Solid, semisolid, and liquid fillings can be carried in hard capsules, whereas soft capsules are mainly for semisolids or liquids. Active ingredients can be incorporated differently depending on the capsule: as a filling in the hard ones; whereas the soft ones are able to carry the drug within their soft shell as well as in the filling. In addition, they can release the content rapidly thanks to a fast swelling and dissolving. Gelatines can contain coloring and antimicrobial agents, and they can also be used for the microencapsulation of drugs where the API is sealed inside a microsized capsule or beadlet. Other examples of gelatin uses are ibuprofen-gelatin micropellets, pastes, pastilles, pessaries, and suppositories. It is also used as tablet binder, coating agent, and viscosity increasing agent (Rowe et al. ). In more specific examples, studies of releasing lysozyme from hydrogels are being conducted in order to deliver antibacterial proteins into prosthesis of heart valves to prevent valve endocarditis. There has been a recent development in long-circulating gelatine controlled release systems which improve the applications in chemotherapy because they can gradually be accumulated at the tumor site thanks to the leaky vasculature and lack of lymph vessels around tumors (Young et al. ). Releasing tetracycline and bisphosphonate from Gelfoam® pellets to reduce periodontal bone loss and controlled-release vehicles for chemo-therapeutic agents are other examples of current researches (Yaffe et al. ). As a collagen derivative, gelatin is a non-toxic, biodegradable, inexpensive, non-immunogenic material; therefore, it has a high potential to be used in a variety of medicinal agents. In addition, its water solubility and lesser cost are advantageous over its precursor (Varghese et al. ). As it was mentioned before, gelatin is highly biocompatible and biodegradable in a physiological environment. The digestive process confers to gelatin a very low antigenicity, with the formation of harmless metabolic products upon degradation. The presence of amino acidic sequences such as Arg-Gly-Asp (RGD) in the structure, improves the final biological performance of gelatin over synthetic polymers that lack these cell-recognition motifs (Santoro et al. ).
Human Serum Albumin Human Serum Albumin (HSA) is the main protein of the blood plasma, accounting for over 50% of its total protein content, and its concentration range is from to 5 g/dl. HSA is a small globular protein with a molecular weight of kDa comprised of a single polypeptide chain of amino acids; it is also the only major plasma protein that does not contain carbohydrate constituents (Rowe et al. ). Regarding its biological properties, albumin is responsible for 75–80% of the colloid osmotic pressure of plasma (Scatchard et al. ); it is also involved in transport and metabolism of several endogenous and exogenous compounds, such as hormones, bile acids, amino acids, fatty acids, toxic metabolites, metals, and drugs (Kratz ). The protein contains a single thiol group from a cysteine residue at position 34 (Cys34) that acts both as a binding site for many biologically active molecules and also providing antioxidant activity, and constituting the largest fraction of free thiol groups in the blood (Stewart
54 Biopolymers for Medical Applications et al. ). Due to the presence of undissociated acid content within the polypeptide, HSA participates in the regulation of acid-base balance (Bruegger et al. ). Albumin and other small macromolecules accumulate in the tumor area due to extensive angiogenesis, increased permeability, and lack of lymphatic drainage in a phenomenon that is universal in solid tumors and it is called enhanced permeability and retention (EPR) effect (Maeda et al. ), providing an attractive strategy for passive targeting of drugs into the tumoral tissue. Furthermore, albumin-binding proteins such as membrane associated gp60 and osteonectin (SPARC), which promote the accumulation of albumin within the tumor interstitium, can also be used in the targeting of tumors by the simple formation of the drug-albumin conjugation (Kratz ). Since Albumin is a naturally-occurring protein found in the body, it is not surprising that the protein is cataloged as a non-toxic material (Rowe et al. ). HSA has an average half-life of 19 days, which provides an attractive approach for improving the pharmacokinetic profiles of peptides and cytokines. Therefore, biodegradability has to be considered for each particular albumin-based drug delivery system because it has proven its strong dependence on the degree of cross-linking (Langer et al. ), pH, and temperature of preparation (Rohanizadeh and Kokabi ). Nowadays, albumin is used as a versatile protein carrier for drug targeting and for improving the pharmacokinetic profile of peptide or protein-based drugs. There are mainly three drug delivery technologies: coupling of low-molecular weight drugs to exogenous or endogenous albumin, conjugation with bioactive proteins, and encapsulation of drugs into albumin particulate systems such as nanoparticles or micelar structures. Several examples of these systems are presented below. The first drug-albumin conjugates were obtained by direct binding peptides or prodrugs to the Cys34 position of exogenous and endogenous albumin. Commercially available albumin can be successfully conjugated with doxorubicin maleimide derivatives (an antibiotic with antineoplastic activity), as reported by Drevs et al. (), to obtain the A-DOXO-HYD conjugate, which has proved to have a superior effect against murine renal carcinoma compared to free doxorubicin at the equitoxic dose. Endogenous albumin can also be used as a drug carrier as in the case of AldoxorubicinTM (CytRx Corporation, Los Angeles, CA, USA), a prodrug of doxorubicin that, following intravenous administration, is able to bind rapidly and selectively to the Cys34 position of albumin, leading to passive accumulation within the tumor; currently this prodrug is being tested in phase 3 clinical trials in patients with soft tissue sarcomas whose tumors have progressed after treatment with chemotherapy. Bioactive peptides, such as Insulin were successfully conjugated with albumin in the so called PC-DAC™:Insulin by ConjuChem, Inc. (Los Angeles, CA, USA), demonstrating more efficiency than insulin Glargine in diabetic rats and a prolonged duration of activity in preclinical pharmacodynamics studies. Albinterferon-α2bTM, a fusion protein of recombinant HSA and interferon α-2b, was developed as a long-acting interferon for the treatment of chronic hepatitis C by Human Genome Sciences in collaboration with Novartis. In this system, albumin was used to increase circulation half-life of interferon-α leading to a significant reduction of the dosing interval, granting a successful phase 3 clinical trial approval; however, Food and Drug Administration’s concerns regarding reduced performance led to the cancellation of
Biopolymers used in Drug Delivery Systems 55
the program in Albumin can also be used for encapsulating lipophilic drugs into nanoparticles using a quite elegant technology (nab or NP albumin bound) in which the drug is mixed with aqueous HSA and passed under high pressure through a jet to yield nanoparticles with sizes of – nm. An example of this is the commercially available nab-paclitaxel, also known as AbraxaneTM, a variation of paclitaxel in which the taxane is bond to albumin forming nanoparticles of an approximate diameter of nm, that was approved in for the treatment of metastatic breast cancer. The enhanced uptake of these albumin-based drug delivery systems in solid tumors can be ascribed to the EPR effect as well as to transcytosis initiated by binding of albumin with gp and SPARC (Desai et al. ).
Miscellaneous Polyethylene glycols Polyethylene glycol polymers (PEGs) are polyalcohols that have been described as an addition of polymers of ethylene oxide and water. These polymers are commonly named macrogols followed by a number indicating their molecular weight, which varies depending on the polymerization degree. Hence, polyethylene glycol grades from to (or macrogols to ) are liquids and grades up to are solids at 25°C. The empirical formula can be written as: HOCH2(CH2OCH2)mCH2OH where m represents the average number of oxyethylene groups that ranges from to , and their molecular weights ranges are from to However, there are grades of PEGs near to The number can be used to indicate the approximate molecular weight of a macrogol. All grades of polyethylene glycol are soluble in water and miscible in all proportions with other polyethylene glycols. Aqueous solutions of high molecular weight glycols (or high grades), may form gels with different viscosity (Rowe et al. ). PEGs are widely used in the manufacture of surfactants, pharmaceuticals, cosmetics, polyurethanes, as well as in a variety of different fields. Regarding pharmaceutical formulations they are used as excipient, being included in parenteral, topical, ophthalmic, oral, rectal preparations; and also have been used experimentally in biodegradable polymeric matrices and in controlled-release systems. Functionally, the pharmaceutical industry uses these compounds as an ointment base, plasticizer, solvent, suppository base, tablet, and capsule lubricant. PEGs are stable and aqueous polyethylene glycol solutions can be used either as suspending agents or to adjust the viscosity and consistency of other suspending vehicles. These compounds can also be used as a co-solvent in order to enhance the aqueous solubility or dissolution characteristics of poorly soluble compounds by making solid dispersions with an appropriate polyethylene glycol. In this context, PEGs enhance the stability of aspartame solutions (Yalwsky et al. ); they can be used in diazepam solutions for parenteral administration (Shah et al. ) and can also improve bentonite dispersions. First Ambrosi et al. () and later Benedini et al. () have used PEG to modify the transition temperature of coagels of ascorbylpalmitate and shift the existence limits of liquid crystals of ascorbylpalmitate.
56 Biopolymers for Medical Applications PEGs are essentially non-irritant to the skin and biocompatible, however they are not easily degradable polymers. PEGs with molecular weight lower than can be degraded by many bacteria species whereas those with higher molecular weights are significantly more resistant (Marchal et al. ). The oxidation of the terminal hydroxyl group and sequential shortening by a single oxyethylene unit is considered, by many authors, as a predominant pathway (Zgoła-Grześkowiak et al. ).
MESH: Biopolymers Classification: LCC QPB69 Includes bibliographical references and index. Identifiers: LCCN
E-Book Overview
This book presents an experimental and computational account of the applications of biopolymers in the field of medicine. Biopolymers are macromolecules produced by living systems, such as proteins, polypeptides, nucleic acids, and polysaccharides. Their advantages over polymers produced using synthetic chemistry include: diversity, abundance, relatively low cost, and sustainability. This book explains techniques for the production of different biodevices, such as scaffolds, hydrogels, functional nanoparticles, microcapsules, and nanocapsules. Furthermore, developments in nanodrug delivery, gene therapy, and tissue engineering are described.
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Biopolymers for Medical Applications
Biopolymers for Medical Design, Fabrication, Properties Applications and Applications of Smart and Advanced Materials Editors
Juan M. Ruso Soft Matter and Molecular Biophysics Group Department of Applied Physics University of Santiago de Compostela Santiago de Compostela Spain Editor
PaulaXu V. Hou Messina
Harvardof University Department Chemistry School of Engineering Applied Sciences Universidad Nacional del Surand INQUISUR-CONICET Cambridge, MA, Bahía Blanca USA Argentina
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A SCIENCE PUBLISHERS BOOK
CRC Press Taylor & Francis Group Broken Sound Parkway NW, Suite Boca Raton, FL © by Taylor & Francis Group, LLC CRC Press is an imprint of Taylor & Francis Group, an Informa business No claim to original U.S. Government works Printed on acid-free paper Version Date: International Standard Book Number (Hardback) This book contains information obtained from authentic and highly regarded sources. Reasonable efforts have been scrivener 1.9.13 crack Activators Patch to publish reliable data and information, but the author and publisher cannot assume responsibility for the validity of all materials or the consequences of their use. The authors and publishers have attempted to trace the copyright holders of all material reproduced in this publication and apologize to copyright holders if permission to publish in this form has not been obtained. If any copyright material has not been acknowledged please write and let us know so we may rectify in any future reprint. Except as permitted under U.S. Copyright Law, no part of this book may be reprinted, reproduced, scrivener 1.9.13 crack Activators Patch, transmitted, or utilized in any form by any electronic, mechanical, or other means, now known or hereafter invented, including photocopying, microfilming, and recording, or in any information storage or retrieval system, without written permission from the publishers. For permission to photocopy or use material electronically from this work, please access alshamasislamicinstitute.com.pkght. com (alshamasislamicinstitute.com.pk) or contact the Copyright Clearance Center, Inc. (CCC), Rosewood Drive, Danvers, scrivener 1.9.13 crack Activators Patch, MACCC is a not-for-profit organization that provides licenses and registration for a variety of users. For organizations that have been granted a photocopy license by the CCC, a separate system of payment has been arranged. Trademark Notice: Product or corporate names may be trademarks or registered trademarks, and are used only for identification and explanation without intent to infringe. Library of Congress Cataloging‑in‑Publication Data Names: Ruso, Juan M. (Juan Manuel), editor. MESH: Biopolymers Classification: LCC QPB69 KiB/s, done.
Resolving deltas: % (1/1), done.
Tapped formulae ( files, M)
Command (Confirm):
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Result:
==> Auto-updated Homebrew!
Updated Homebrew from 03ee to 6e
Updated 1 tap (homebrew/core).
==> Updated Formulae
abcm2ps cake git-imerge libyaml plowshare tor
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==> Deleted Formulae
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homebrew/core
homebrew/python
homebrew/science
Command (installing hdf5 and opencv):
$ brew install hdf5 opencv
Result:
==> Installing hdf5 from homebrew/science
==> Installing dependencies for homebrew/science/hdf5: autoconf, automake, libtool
==> Installing homebrew/science/hdf5 dependency: autoconf
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==> Pouring alshamasislamicinstitute.com.pk
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Emacs Lisp files have been installed to:
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==> Installing homebrew/science/hdf5 dependency: libtool
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==> Pouring libtool_alshamasislamicinstitute.com.pk
==> Caveats
In order to prevent conflicts with Apple's own libtool we have prepended a "g"
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==> Summary
🍺 /usr/local/Cellar/libtool/_1: 70 files, M
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==> autoreconf -fiv
==> ./configure --prefix=/usr/local/Cellar/hdf5/ --enable-production --enable-debug=no --with-zlib=/usr --with-szlib=/usr/local/opt/szip --enable-stat
==> make
==> make install
🍺 /usr/local/Cellar/hdf5/ files, M, built in 3 minutes 37 seconds
==> Installing opencv from homebrew/science
==> Installing dependencies for homebrew/science/opencv: cmake, eigen, ilmbase, openexr, pkg-config
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==> Pouring alshamasislamicinstitute.com.pk
==> Caveats
Emacs Lisp files have been installed to:
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==> Summary
🍺 /usr/local/Cellar/cmake/ 2, files, M
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==> Installing homebrew/science/opencv dependency: openexr
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==> Installing homebrew/science/opencv dependency: pkg-config
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==> Pouring pkg-config_alshamasislamicinstitute.com.pk
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==> Installing homebrew/science/opencv
==> Downloading alshamasislamicinstitute.com.pk
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==> cmake . -DCMAKE_C_FLAGS_RELEASE=-DNDEBUG -DCMAKE_CXX_FLAGS_RELEASE=-DNDEBUG -DCMAKE_INSTALL_PREFIX=/usr/local/Cellar/opencv/_3 -DCMAKE_BUILD_TYPE
==> make
Last 15 lines from /Users/USERNAME/Library/Logs/Homebrew/opencv/make:
[ 15%] Building CXX object modules/video/CMakeFiles/opencv_alshamasislamicinstitute.com.pk
cd /tmp/opencvtnphw6/opencv/macbuild/modules/video && /usr/local/Homebrew/Library/Homebrew/shims/super/clang++ -DCVAPI_EXPORTS -I/tmp/opencvtnphw6/opencv/modules/video/perf -I/tmp/opencvtnphw6/opencv/modules/video/include -I/tmp/opencvtnphw6/opencv/modules/calib3d/include -I/tmp/opencvtnphw6/opencv/modules/features2d/include -I/tmp/opencvtnphw6/opencv/modules/highgui/include -I/tmp/opencvtnphw6/opencv/modules/imgproc/include -I/tmp/opencvtnphw6/opencv/modules/flann/include -I/tmp/opencvtnphw6/opencv/modules/core/include -I/tmp/opencvtnphw6/opencv/modules/ts/include -I/tmp/opencvtnphw6/opencv/macbuild/modules/video -I/tmp/opencvtnphw6/opencv/modules/video/src -I/tmp/opencvtnphw6/opencv/modules/video/test -I/tmp/opencvtnphw6/opencv/macbuild -isystem /usr/local/include/eigen3 -fsigned-char -W -Wall -Werror=return-type -Werror=address -Werror=sequence-point -Wformat -Werror=format-security -Wmissing-declarations -Wmissing-prototypes -Wstrict-prototypes -Wundef -Winit-self -Wpointer-arith -Wshadow -Wsign-promo -Wno-narrowing -Wno-delete-non-virtual-dtor -Wno-unnamed-type-template-args -Wno-array-bounds -Wno-aggressive-loop-optimizations -fdiagnostics-show-option -Wno-long-long -Wno-semicolon-before-method-body -fno-omit-frame-pointer -msse -msse2 -mavx -DNDEBUG -DNDEBUG -isysroot /Applications/alshamasislamicinstitute.com.pk -fPIC -o CMakeFiles/opencv_alshamasislamicinstitute.com.pk -c /tmp/opencvtnphw6/opencv/modules/video/src/alshamasislamicinstitute.com.pk
[ 16%] Building CXX object modules/video/CMakeFiles/opencv_alshamasislamicinstitute.com.pk
cd /tmp/opencvtnphw6/opencv/macbuild/modules/video && /usr/local/Homebrew/Library/Homebrew/shims/super/clang++ -DCVAPI_EXPORTS -I/tmp/opencvtnphw6/opencv/modules/video/perf -I/tmp/opencvtnphw6/opencv/modules/video/include -I/tmp/opencvtnphw6/opencv/modules/calib3d/include -I/tmp/opencvtnphw6/opencv/modules/features2d/include -I/tmp/opencvtnphw6/opencv/modules/highgui/include -I/tmp/opencvtnphw6/opencv/modules/imgproc/include -I/tmp/opencvtnphw6/opencv/modules/flann/include -I/tmp/opencvtnphw6/opencv/modules/core/include -I/tmp/opencvtnphw6/opencv/modules/ts/include -I/tmp/opencvtnphw6/opencv/macbuild/modules/video -I/tmp/opencvtnphw6/opencv/modules/video/src -I/tmp/opencvtnphw6/opencv/modules/video/test -I/tmp/opencvtnphw6/opencv/macbuild -isystem /usr/local/include/eigen3 -fsigned-char -W -Wall -Werror=return-type -Werror=address -Werror=sequence-point -Wformat -Werror=format-security -Wmissing-declarations -Wmissing-prototypes -Wstrict-prototypes -Wundef -Winit-self scrivener 1.9.13 crack Activators Patch -Wshadow -Wsign-promo -Wno-narrowing -Wno-delete-non-virtual-dtor -Wno-unnamed-type-template-args -Wno-array-bounds -Wno-aggressive-loop-optimizations -fdiagnostics-show-option -Wno-long-long -Wno-semicolon-before-method-body -fno-omit-frame-pointer -msse -msse2 -mavx -DNDEBUG -DNDEBUG -isysroot /Applications/alshamasislamicinstitute.com.pk -fPIC -o CMakeFiles/opencv_alshamasislamicinstitute.com.pk -c /tmp/opencvtnphw6/opencv/modules/video/src/alshamasislamicinstitute.com.pk
[ 16%] Building CXX object modules/video/CMakeFiles/opencv_alshamasislamicinstitute.com.pk
cd /tmp/opencvtnphw6/opencv/macbuild/modules/video && /usr/local/Homebrew/Library/Homebrew/shims/super/clang++ -DCVAPI_EXPORTS -I/tmp/opencvtnphw6/opencv/modules/video/perf -I/tmp/opencvtnphw6/opencv/modules/video/include -I/tmp/opencvtnphw6/opencv/modules/calib3d/include -I/tmp/opencvtnphw6/opencv/modules/features2d/include -I/tmp/opencvtnphw6/opencv/modules/highgui/include -I/tmp/opencvtnphw6/opencv/modules/imgproc/include -I/tmp/opencvtnphw6/opencv/modules/flann/include -I/tmp/opencvtnphw6/opencv/modules/core/include -I/tmp/opencvtnphw6/opencv/modules/ts/include -I/tmp/opencvtnphw6/opencv/macbuild/modules/video -I/tmp/opencvtnphw6/opencv/modules/video/src -I/tmp/opencvtnphw6/opencv/modules/video/test -I/tmp/opencvtnphw6/opencv/macbuild -isystem /usr/local/include/eigen3 -fsigned-char -W -Wall -Werror=return-type -Werror=address -Werror=sequence-point -Wformat -Werror=format-security -Wmissing-declarations -Wmissing-prototypes -Wstrict-prototypes -Wundef -Winit-self -Wpointer-arith -Wshadow -Wsign-promo -Wno-narrowing -Wno-delete-non-virtual-dtor -Wno-unnamed-type-template-args -Wno-array-bounds -Wno-aggressive-loop-optimizations -fdiagnostics-show-option -Wno-long-long -Wno-semicolon-before-method-body -fno-omit-frame-pointer -msse -msse2 -mavx -DNDEBUG -DNDEBUG -isysroot /Applications/alshamasislamicinstitute.com.pk -fPIC -o CMakeFiles/opencv_alshamasislamicinstitute.com.pk -c /tmp/opencvtnphw6/opencv/modules/video/src/alshamasislamicinstitute.com.pk
[ 16%] Building CXX object modules/video/CMakeFiles/opencv_alshamasislamicinstitute.com.pk
cd /tmp/opencvtnphw6/opencv/macbuild/modules/video && /usr/local/Homebrew/Library/Homebrew/shims/super/clang++ -DCVAPI_EXPORTS -I/tmp/opencvtnphw6/opencv/modules/video/perf -I/tmp/opencvtnphw6/opencv/modules/video/include -I/tmp/opencvtnphw6/opencv/modules/calib3d/include -I/tmp/opencvtnphw6/opencv/modules/features2d/include -I/tmp/opencvtnphw6/opencv/modules/highgui/include -I/tmp/opencvtnphw6/opencv/modules/imgproc/include -I/tmp/opencvtnphw6/opencv/modules/flann/include -I/tmp/opencvtnphw6/opencv/modules/core/include -I/tmp/opencvtnphw6/opencv/modules/ts/include -I/tmp/opencvtnphw6/opencv/macbuild/modules/video -I/tmp/opencvtnphw6/opencv/modules/video/src -I/tmp/opencvtnphw6/opencv/modules/video/test -I/tmp/opencvtnphw6/opencv/macbuild -isystem /usr/local/include/eigen3 -fsigned-char -W -Wall -Werror=return-type -Werror=address -Werror=sequence-point -Wformat -Werror=format-security -Wmissing-declarations -Wmissing-prototypes -Wstrict-prototypes -Wundef -Winit-self -Wpointer-arith -Wshadow -Wsign-promo -Wno-narrowing -Wno-delete-non-virtual-dtor -Wno-unnamed-type-template-args -Wno-array-bounds -Wno-aggressive-loop-optimizations -fdiagnostics-show-option -Wno-long-long -Wno-semicolon-before-method-body -fno-omit-frame-pointer -msse -msse2 -mavx -DNDEBUG -DNDEBUG -isysroot /Applications/alshamasislamicinstitute.com.pk -fPIC -o CMakeFiles/opencv_alshamasislamicinstitute.com.pk -c /tmp/opencvtnphw6/opencv/modules/video/src/video_alshamasislamicinstitute.com.pk
[ 16%] Linking CXX shared library ././lib/libopencv_alshamasislamicinstitute.com.pk
cd /tmp/opencvtnphw6/opencv/macbuild/modules/video && /usr/local/Cellar/cmake//bin/cmake -E cmake_link_script CMakeFiles/opencv_alshamasislamicinstitute.com.pk --verbose=1
/usr/local/Homebrew/Library/Homebrew/shims/super/clang++ -fsigned-char -W -Wall -Werror=return-type -Werror=address -Werror=sequence-point -Wformat -Werror=format-security -Wmissing-declarations -Wmissing-prototypes -Wstrict-prototypes -Wundef -Winit-self -Wpointer-arith -Wshadow -Wsign-promo -Wno-narrowing -Wno-delete-non-virtual-dtor -Wno-unnamed-type-template-args -Wno-array-bounds -Wno-aggressive-loop-optimizations -fdiagnostics-show-option -Wno-long-long -Wno-semicolon-before-method-body -fno-omit-frame-pointer -msse -msse2 -mavx -DNDEBUG -DNDEBUG -isysroot /Applications/alshamasislamicinstitute.com.pk -dynamiclib -Wl,-headerpad_max_install_names -compatibility_version -current_version -o ././lib/libopencv_videodylib -install_name /tmp/opencvtnphw6/opencv/macbuild/lib/libopencv_videodylib CMakeFiles/opencv_alshamasislamicinstitute.com.pk CMakeFiles/opencv_alshamasislamicinstitute.com.pk CMakeFiles/opencv_alshamasislamicinstitute.com.pk CMakeFiles/opencv_alshamasislamicinstitute.com.pk CMakeFiles/opencv_alshamasislamicinstitute.com.pk CMakeFiles/opencv_alshamasislamicinstitute.com.pk CMakeFiles/opencv_alshamasislamicinstitute.com.pk CMakeFiles/opencv_alshamasislamicinstitute.com.pk CMakeFiles/opencv_alshamasislamicinstitute.com.pk CMakeFiles/opencv_alshamasislamicinstitute.com.pk CMakeFiles/opencv_alshamasislamicinstitute.com.pk ././lib/libopencv_imgprocdylib ././lib/libopencv_coredylib
cd /tmp/opencvtnphw6/opencv/macbuild/modules/video && /usr/local/Cellar/cmake//bin/cmake -E cmake_symlink_library ././lib/libopencv_videodylib ././lib/libopencv_videodylib ././lib/libopencv_alshamasislamicinstitute.com.pk
[ 16%] Built target opencv_video
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Preface Owing to their higher chemical and impact resistance in addition to their superior mechanical and thermal properties, biopolymers have become “the material of choice” in healing therapies. A wide range of different polymers are available for multiple medical applications; so much so that it is expected that the use of glass and metals in therapeutic devices will decline over the next few years while the use of polymers will increase. Although this subject has long been an important area of research for biochemists and physicists, engineers,
scrivener 1.9.13 crack Activators Patch, pharmacists and physicians are now taking a keen interest in it. Polymers’ versatility and, the scientist’s ability to engineer and customize their physical, chemical and biological properties to match the requirements of the varied and specific medical applications are the keys
scrivener 1.9.13 crack Activators Patch their increasing use. Applications, just to name a few, include medical tubing, controlled drug delivery and wound management (e.g., adhesives, sutures, lubricants and surgical meshes), orthopedic devices (screws, pins, and rods), dental materials (filler after a tooth extraction) and tissue engineering. This book has been devised so as to offer an
scrivener 1.9.13 crack Activators Patch of currently “hot” topics in this field. We, as editors of this book, have selected reputed scientists whose research and ideas have significantly contributed to progress in this area. Recognizing that there are different approaches to biopolymers is not enough. Experiments have been the centerpiece of the scientific method since Galileo. However, the power of modern computers has made computational approaches a key aspect in all kind of scientific research. This diversity needs to be preserved and promoted. Given that different approaches emphasize different aspects and offer different perspectives allows us to have a fuller, more balanced understanding of the complex entity called biopolymers. Especially in the long term, a discipline that contains a variety of different approaches can cope with a changing world better than others characterized by only a single way. For this reason, in this book, we have made special emphasis to both disciplines are reflected. The different classes of advanced materials based on biopolymer systems including biopolymer nano-fibers and nano-tubes, smart nano-assemblies for drug and gene delivery, ordered supramolecular systems as well as novel composite materials based on nanoparticles and biopolymers, are covered in the book. In the first nine chapters of this monograph a detailed account of the present status of biopolymers it is provided and highlighted the recent developments made by leading research groups.
vi
Biopolymers for Medical Applications
Since the requirements of medical applications are variable, there is no ideal biopolymer. Therefore, new materials are developed based on the desired properties for very specific purposes. This means that in addition to materials, processing techniques and computational tools are inherent in this process. Thus, the book is completed with five chapters featuring concepts of modeling and simulation of biological systems, drug-target interaction analysis via perturbation theory, guided self-assembly by structural DNA nanotechnology, dynamic examination of molecular drug-protein binding and selective imprinted xerogels. In chapters ranging from 10 to 14, the recent advances of mathematical and theoretical models, applied to find an accurate representation of the complexity of biological systems, have been highlighted. It shows how reasonably simple mathematics can be combined with different models to draw exciting conclusions. Interconnections are made between diverse biological examples and a variety of discrete and continuous equation models. On the other hand, the constant progresses in both computer power and algorithm design, makes highly promising the future of computer-aided drug design; thus, with every passing day molecular dynamics simulations, the science of simulating the motions of a system of particles, play an increasingly important role. The three final chapters of this book discusses the atomistic computer simulations of biopolymers (i.e., a protein), receptors and their associated small-molecule ligands that can act in drug discovery, including the identification of cryptic or allosteric binding sites, the enhancement of traditional virtual-screening methodologies, and the direct prediction of small-molecule binding energies. The limitations of current simulation methodologies, comprising the high computational costs and approximations of molecular
scrivener 1.9.13 crack Activators Patch required were also discussed. The variety of topics covered in this book aims to provide a comprehensive overview of the field of biopolymers for medical applications. Besides its usefulness for academics and industrial researchers, the book is of humanistic inspiration, revealing the special sensitivity of authors who have made a great effort to uproot the palisades that traditionally separate advanced professionals from those unfamiliar with these subjects. Indeed, we hope to convince the latter of the many new research opportunities in this field. Last, but not least, the fact that we are writing this preface is, without any doubt, due to the cooperation, support, and understanding of all the contributors who invested a considerable amount of time in helping this book to reach fruition. We have been privileged to coordinate the efforts of many talented scientists. Juan M. Ruso and Paula V. Messina
Contents Preface 1. Biopolymers in Regenerative Medicine: Overview, Current Advances and Future Trends Juan M. Ruso and Paula V. Messina
v 1
2. Application of Natural, Semi-Synthetic, and Synthetic Biopolymers used in Drug Delivery Systems Design Javier Sartuqui, Noelia L. D’Elía, A. Noel Gravina and Luciano A. Benedini
38
3. Polysaccharide Based Biomaterials Narendra Reddy and Divya Natraj
66
4. Biopolymers in the Prevention of Dental Erosion Javier Sotres
5. Drug Carriers by Liposomes Physically Coated with Peptides Qiufen Zhang, Cuicui Su, Nan Wang and Dehai Liang
6. Biopolymers
MDaemon Email Server Pro 21.0.0 Crack License key In Vitro Tissue Model Biofabrication Aleksander Skardal
7. Medical Application of Polyampholytes Kazuaki Matsumura, Robin Rajan, Sana Ahmed and Minkle Jain
8. Biomedical Applications of Recombinant Proteins and Derived Polypeptides Francisco Javier Arias, Sergio Acosta-Rodríguez, Tatjana Flora and Sofía Serrano-Dúcar
9. Cellulose Nanofibers for Biomedical Applications Marité Cardenas and Anna J. Svagan Modelling and Simulation of Biological Systems in Medical Applications S. Balaji
viii
Biopolymers for Medical Applications
High-Order Perturbation Theory Models of Drug-Target Interactomes for Proteins Expressed on Networks of Hippocampus Brain Region of Alzheimer Disease Patients Francisco J. Romero-Durán, Edgar Lopez-Castro, Xerardo García-Mera and Humberto González-Díaz
Structural Modeling for DNA and RNA Bindings to Breast Anticancer Drug Tamoxifen and Its Metabolites H. A. Tajmir-Riahi, P. Bourassa and T. J. Thomas
Dynamic Analysis of Backbone-Hydrogen-Bond Propensity for Protein Binding and Drug Design C. A. Menéndez, S. R. Accordino, J. A. Rodriguez Fris, D. C. Gerbino and G. A. Appignanesi
Molecular Dynamics Simulations and Comparison of Two New and High Selective Imprinted Xerogels Riccardo Concu, Manuel Azenha and M. Natalia D. S. Cordeiro
Index
1 Biopolymers in Regenerative Medicine: Overview, Current Advances and Future Trends Juan M. Ruso1 and Paula V. Messina2,* Introduction Overview An ambition of regenerative medicine is the in vivo restoration or, alternatively, the in vitro generation of a complex functional organ consisting of a scaffold made out of synthetic or natural materials that has been loaded with living cells (Melek; Terzic and Nelson ). Mammalian cells respond in vivo to the biological stimulus from the surrounding environment, which is structured by nanometer-scaled components. Consequently, materials intended for the reconstruction of the human body have to reproduce the correct signals that guide the cells towards a desirable behavior (Patel ), in this sense, polímeros are currently investigated. Exciting advances based on application of the self-assembled biocompatible polymeric scaffolds for regeneration of tissues and organs were systematically explored and described in detail in the literature (Niaounakis ; Kalia and Avérous ;
Soft Matter and Molecular Biophysics Group, Department of Applied Physics, University of Santiago de Compostela, Santiago de Compostela,Spain. 2 Department of Chemistry, Universidad Nacional del Sur,Bahía Blanca, Argentina. INQUISURCONICET. * Corresponding author: [emailprotected] 1
2 Biopolymers for Medical Applications Imam et al. ; Atala and Allickson ; Dutta and Dutta ). Their effectiveness in providing supports for cell growth and development in various tissues and enhancing or mimicking an extracellular matrix (ECM) has been carefully analyzed (Nedovic and Willaert ; Hunt and Grover ). Clinical results showing the benefits of such treatments, as well as their limitations are explored and novel polymer formulas, for coating implants, stents, and other medical devices, have been developed (Plackett ; Jagur‐Grodzinski ; Tseng et al. ; Weber et al. ; Mani et al. ; Jung et al. a; Jung et al. b; De Vicente et al. ; Ferreira et al. ; Schwarz et al. ). Furthermore, the application of these polymeric materials in tissue engineering of cartilage and bones are explored (Stevens ; Bessa et al. ; Yilgor et al. ; Beltrán et al. ). An innovative and transiently evolving biotechnological subfield, the synthetic biology, attempts to insert enhanced functionality and response to biomaterials by the use of recombinant polymer biotechnology to include genetic units that are not typically present on them (Hammer and Kamat ),
scrivener 1.9.13 crack Activators Patch. Consistently, synthetic membranes from bio-inspired block co-polypeptides developed into another emerging area of interest (Bellomo et al. ). This chapter offers a structural synopsis of biopolymers and discusses their physicochemical characteristics, organization—properties relationship, applications, and limitations. The classification of polymers is briefly mentioned and their chemical structures are provided. Biopolymers that are hydrolytically labile and erode (biodegradable polymers) as well as those that are bio-inert and remain unchanged after implantation (non-degradable polymers) are considered. Some synthetic derivatives of natural materials are briefly discussed where appropriate. It is the authors’ intention to provide a thorough general idea of the biopolymers’ applications to regenerative medicine. This chapter tends to be a guide for further reading on most biopolymer classifications and properties.
The basics: biopolymer definition and classification There is no a general consensus in literature and patents about the exact definition of the generic terms degradable, biodegradable, bio-based, compostable, biopolymer, and bioplastic; they appear to have multiple and overlapping meanings. We have presented here a brief description of each definition highlighting their differences. For more information consult Niaounakis (). Degradable is a general term used to describe all polymeric materials that disintegrate by a range of physical and chemical processes, while biodegradable is a term focused on the polymer’s functionality,
scrivener 1.9.13 crack Activators Patch, that is, “biodegradability”. This term is applied to those materials that will degrade, within a specific period of time and environment, under the action of microorganisms such as molds, fungi, and bacteria. According to the withdrawn standard ASTM D (ASTM Internationa, ), the
scrivener 1.9.13 crack Activators Patch biodegradable polymers specifically refer to polymers that are “capable of undergoing decomposition into carbon dioxide, methane, water, inorganic compounds, or biomass in which the predominant mechanism is the enzymatic action of microorganisms that can be measured by standard tests, over a specific period of time, reflecting available disposal conditions.” On the other hand, the Japan Bioplastics Association
Biopolymers in Regenerative Medicine 3
(JBPA) defines the term biodegradability as the characteristics of material that can be microbiologically degraded to the final products of carbon dioxide and water, which, in turn, are recycled in nature (Niaounakis ). Biodegradation should be differentiated from disintegration, which simply implies the breakdown of a material into small and separate fragments. Biodegradable polymers can be certified according to any of the following legally binding international standards: ISOENENASTM D (Niaounakis ). As a consequence of this classification, a polymer may be degradable but not biodegradable. Bio-based is a word focused on the origin of raw materials, and it’s applied to polymers obtained from renewable resources. In practical terms, a bio-based polymer is not per se an ecological polymer; this is subjected to a variety of concerns, including the material origin, the production method, and finally how such material is disposed at the end of its useful life. Accordingly to these classifications, not every
scrivener 1.9.13 crack Activators Patch polymer is biodegradable, e.g., bio-based polyethylene or polyamide 11; and not every biodegradable polymer is bio-based, e.g., poly(ε-caprolactone) or poly(glycolic acid); nevertheless some polymers fall into both categories, such as polyhydroxyalkanoates (PHA)s. Currently, there are no standards to certify a “bio-based product”. However, the bio-based content of a product can be quantify by measuring the bio-based content of materials via carbon isotope analysis, ASTM D (ASTM International b). Compostable polymers were circumscribed to the ASTM D (ASTM International ), that stated “a plastic which is capable of undergoing biological decomposition in a compost site as part of an available program”. Nevertheless, this definition obtained considerable disapproval, and in Januarythe ASTM removed the standard ASTM D (ASTM International ) and substituted it for the standard ASTM D() (ASTM International a); posteriorly it was withdrawn, with no replacement. To be called compostable, a polymer should meet one of the following international standards: ASTM Standard D (ASTM International a) or CEN standard EN (for compostable plastics), D or EN (for compostable packaging) (ASTM International b), and ISO The ISO-Standard not only refers to plastic packaging but to plastics in general. The biodegradation and/or disintegration rate, in addition to toxicity are the points that make the difference between biodegradable and compostable polymers. All compostable polymers are biodegradable by default, but not vice versa. Definitely, two different criteria point out the definition of a biopolymer: the source of the raw materials, and the biodegradability of the polymer. As a consequence, a biopolymer is a polymer derived from renewable resources, as well as a biological and fossil-based bio-degradable polymer (Niaounakis ). Based on its capacity to be chemically consumed by bacteria, fungi, or other biological means, biopolymers can be divided into two wide groups: biodegradable and non-biodegradable biopolymers. Alternatively, biopolymers can be classified on their origin as being either bio-based or fossil fuel-based. The central categories for distinguishing among the different types of biopolymers are mentioned below (Niaounakis ): i. Bio-based biodegradable biopolymers. ii. Non-Biodegradable bio-based biopolymers. iii,
scrivener 1.9.13 crack Activators Patch. Biodegradable biopolymers made from fossil fuels.
4 Biopolymers for Medical Applications The biopolymers belonging to (i) can be biologically generated by microorganisms, plants, and animals, or chemically synthesized from biological starting materials (e.g., corn, sugar, starch, etc.). Examples of biodegradable bio-based biopolymers are: (1) synthetic polymers from renewable resources such as poly(lactic acid) (PLA); (2) biopolymers produced by microorganisms, such as PHAs; (3) and those that are biosynthesized by various routes in the biosphere, such as starch or proteins. The biopolymers corresponding to (ii) can be produced either from biomass or from renewable resources and are non-biodegradable. Examples of non-biodegradable bio-based biopolymers are: (1) synthetic polymers from renewable resources such as specific polyamides from castor oil (polyamide 11), specific polyesters based on biopropanediol, biopolyethylene (bio-LDPE, bio-HDPE), biopolypropylene (bio-PP), or biopoly (vinyl chloride) (bio-PVC) based on bio-ethanol (e.g., from sugar cane), etc.; (2) naturally occurring biopolymers such as natural rubber or amber. The biopolymers of the last item (iii) are produced from fossil fuel, such as synthetic aliphatic polyesters made from crude oil or natural gas, and are formally biodegradable and compostable. Some examples of biodegradable biopolymers made from fossil fuels are: Poly(ε-caprolactone) (PCL), poly(butylene succinate) (PBS), and selected aliphatic-aromatic co-polyesters. All of them can be degraded by microorganisms (Niaounakis ). Biopolymers and bio-plastics are often considered synonymous, while they are different materials. Biopolymers are polymers that fit the definition given above and the bio-plastics are the plastics that are created by using biopolymers. According to the European Bioplastics e.V., a plastic material is defined as a bio-plastic if it is either bio-based, biodegradable, or contains both properties (Niaounakis ),
scrivener 1.9.13 crack Activators Patch. On the basis of this classification, a material is considered a bio-polymer if it is comprise of any biodegradable polymer (e.g., polymers of type i or iii) or of any bio-based polymers (e.g., polymers of type i or ii). A particular case is the bio-polyethylene derived from sugarcane, designated as “green
Outbyte Driver Updater For Windows it is non-biodegradable, but emits less greenhouse gases when compared to fossil-based polyethylene, and accordingly, is classified as a biopolymer (Niaounakis ). In general, polymers can also be classified on basis of their response to heat as thermoplastics,
scrivener 1.9.13 crack Activators Patch, thermosets, or elastomers (Raquez et al. ); and by their composition as blends (Paul ), composites (White et al. ; Saheb and Jog ), or laminates (Powell ); these classifications can be extended to biopolymers. Currently, the level of bio-based thermoset biopolymers exceeds the volume of bio-based thermoplastic biopolymers (Mohanty et al. ). Biopolymer blends are mixtures of polymers from different origins such as the commercial product Ecovio® (BASF AG), which is a blend of PLA and poly(butylene adipate-co-terephthalate) (PBAT) (Ecoflex®, BASF AG),
scrivener 1.9.13 crack Activators Patch. An extra group is constituted by the bio-composites; these are biopolymers or synthetic polymers reinforced with natural fibers (Mohanty et al. ), such as sisal, flax, hemp, jute, banana, wood, and various grasses, and/or fillers and additives. Novel bio-composites are based on a biodegradable matrix polymer reinforced with natural fibers (Mohanty et al. ).
Biopolymers in Regenerative Medicine 5
Biomaterials chronology and biopolymers Originally, the selection of materials for their use as medical implants was dependent on those already available off the shelf (Hench and Polak ). Early implantable materials include metals such as gold that were used in dentistry over 2, years ago (Langer and Tirrell ). The term “biomaterials” was first introduced within the last 50 years (Atala et al. ). Practically at the same time, and aided by the hasty industrial expansions of polymer synthesis, the assessment of synthetic polymers for biomedical applications was initiated. Polymethylmethacrylate, PMMA, was used in dentistry in the s and cellulose acetate was used in dialysis tubing in the s. Dacron was used to make vascular grafts; polyether urethanes, the materials used in ladies’ girdles,
scrivener 1.9.13 crack Activators Patch, were used in artificial hearts; and PMMA and stainless steel were used in total hip replacements (Langer and Tirrell ). The elaboration of plastic contact lenses, utilizing primarily PMMA, started around (Efron ), and the first data on the use of nylon as a suture was reported in (Atala et al. ). At the end of World War II, a wide variety of polymeric materials were available to inspiring surgeons to break new grounds in replacing diseased or damaged body parts. Materials such as silicones, polyurethanes, Teflon, Nylon, methacrylates, blends with titanium, and stainless steel were available for surgeons to overcome medical problems. Inspired by the idea to restore lost organ or tissue functionality, health and dental experts, made use of minimal regulatory controls to elaborate
phpstorm portable Activators Patch improvise replacements, bridges, conduits, and even organ systems based on such materials. Those early implants made from the available industrial materials were frequently incompatible with the host tissue, generally due to their insufficient purity,
scrivener 1.9.13 crack Activators Patch. From the beginning, alterations of the host tissue in reaction to the materials presence became ostensible. Additives such as plasticizers, un-polymerized reactants, and degradation products were evaluated as possible causes,
scrivener 1.9.13 crack Activators Patch, leading to a conscious
Second-generation materilas; materials bio-active. Goal : biodegradable shape memory polymers with programable surface.
t-generation materials; bio-inerts. Goal : reaction-interaction. Prototypical material of first-generation : silicone rubber. PGA as biodegradable suture. y implantable materials "of the self". PMMA · sed in dentistry; plastic contact lenses; dialysis tubing from cellulose acetate; Nylon sutures; vascular grafts of Dacon; hip replacements from PMMA plus stainless steel.
Fig. 1: Participation of biopolymer in the biomaterials evolution.
Third-generation materials; regeneration reneration
ofiunctional tissues. Goal: induction of response, reabsorbable specifical cellular response. resorbable scaffolds made from bio-polymers bio-polimers that involves molecular tailoring of GFs, adhesive amino-acids sequences or gene expression activation.
6 Biopolymers for Medical Applications exploration of polymer features for biomedical applications and biocompatibility testing. With an emerging knowledge of the immunological system and the understanding of the possible foreign body reaction, a first generation of materials was developed during the s and s (Ratner et al. ),
scrivener 1.9.13 crack Activators Patch. The first-generation materials were designed as bio-inert. The main objective was to create a material that would match the mechanical properties of the replaced tissue, and would not allow protein adsorption and cell adhesion, in order to reduce the possible immune response and rejection. The elastomeric polymer, silicone rubber was widely used as a prototypical material of the first generation (Teck Lim et al. ). In the early s, research shifted from materials that exclusively exhibited a bio-inert tissue response to materials that actively interacted with their environment. The secondgeneration biomaterials are specifically designed to be “bioactive”. This means they should elicit specific and desired cellular responses, like cell adhesion, proliferation and differentiation into a specific cell type, e.g., bone cells that will form a new bone tissue and thus integrate the implant strongly into the surrounding natural tissue (Hench and Polak ). The reaction of the cells should be controllable by the physical and chemical properties of the material surface. An additional advance in this second generation was the development of biodegradable materials that exhibited controllable chemical breakdown into non-toxic degradation products, which were either metabolized or directly eliminated. Biodegradable synthetic polymers were designed to resolve the interface problem, since the foreign material is ultimately replaced by regenerating tissues and eventually the regeneration site is histologically indistinguishable from the host tissue. Since the s, a biodegradable suture composed of polyglycolic (PGA) acid has been in clinical use (Atala et al. ; Ratner et al. ). Many groups continue to search for biodegradable polymers with needed properties such as strength, flexibility, a chemical composition conducive to tissue development, and a degradation rate consistent with the specific application (Zhou et al. ; Shih and Lin ; Evans et al. ). Polymeric materials with novel properties such as shape-memory and programmable and interactive surfaces that control the cellular microenvironment are also under investigation (Han et al. ; Brosnan et al. ; McCloskey ). Other biopolymers’ applications rapidly emerged, thus providing versatile technologies for regenerative medicine, for example, as fracture fixation assistances, as drug delivery devices or as transports of signaling molecules or genetic code information. Biopolymers-based systems can permit delivery of drugs, active proteins, and other macromolecules (Jonker et al. ; Pal et al. ; Estrada and Champion ; Srichana and Domb ) localized the site where the drug is needed,
scrivener 1.9.13 crack Activators Patch. Despite considerable clinical success of bio-inert, bioactive, and resorbable implants, there is still a high long-term prostheses failure rate and need for revision surgery (Atala et al. ; Ratner et al. ). Artificial biomaterials cannot respond, unlike living tissue, to changing physiological loads or biochemical stimuli so improvements of first- and second-generation biomaterials have been incomplete,
scrivener 1.9.13 crack Activators Patch. To overcome these limitations, a third generation of biomaterials that involves molecular tailoring of resorbable polymers for specific cellular responses is being developed. By immobilizing specific biomolecules, such as signaling molecules or cell-specific adhesion peptides or proteins, onto a material it is possible to mimic the extracellular matrix (ECM) environment and stimulate the specific response of cells at
Biopolymers in Regenerative Medicine 7
a molecular level and activate specific gene expression that regulates regeneration and the self-healing process. One of the most advanced strategies in the present research on tissue engineering is the
scrivener 1.9.13 crack Activators Patch of tridimensional (3D) porous scaffolds made of resorbable biopolymers that should be seeded with the patient’s own cells or even stem cells (Weiss
scrivener 1.9.13 crack Activators Patch Calvert ; Rezwan et al. ; Stoddart et al. ). Upon implantation into the body, the polymeric scaffolds will provide the cells the necessary support during self-healing process and should be gradually degraded, as they will be continuously replaced by new bone; finally it will disappear completely. Biomimetic surfaces prepared on basis of biopolymers are promising tools to control cell adhesion, implant integration, cell differentiation, and tissue development (Dalsin et al. ; Cheng et al. ; Kim et al. ). Constantly expanding knowledge of the basic biology of stem cell differentiation and the corresponding signaling pathways as well as tissue development provides the basis for novel molecular design of scaffolds. It is rather important that the engineered scaffold will be designed to be steadily remodeled in vivo and to resemble the histological and mechanical properties of the surrounding tissue. Due to this paradigm shift, mechanically labile hydrogels,
scrivener 1.9.13 crack Activators Patch, especially injectable systems that can be used to directly encapsulate cells, have gained great importance as a basis for biomimetic cell carriers (Yu and Ding ; Nicodemus and Bryant ; Wu et al. ; Jiang et al. ). In spite of the great advances attained, in the case of polymer-based devices for bone tissue replacement, their potential use is still very limited due to their insufficient mechanical properties as load-bearing implants. These materials need further improvements, e.g., strong mechanically resistant reinforcement with fibrous or particulate component and loading with bioactive molecules which would accelerate the formation of regenerated, mineralized, and fully functional bone tissue. The subsequent sections will provide a synopsis on the biopolymers impact on the third-generation materials, focusing on their translational potential evidenced by preclinical studies outcomes.
The Role of Biopolymers in Translational Medicine Novel tissue engineering (TE) strategies are developed with the aim to overcome the socio-economic and health burden of different tissues injuries and improve the life of patients worldwide (Ratner et al. ). In the last decades, a pool of multiple techniques and methodologies for biomaterials fabrication has been described in an attempt to address and explore the major functional architectural and compositional cues of native tissues (Atala and Allickson ; Chaikof et al. ; Song et al. ; Hook et al. ; Hassan et al. b). The search for improved and tissueoriented implantable units has extended the knowledge on biomaterials’ potential and highlighted the interest for multimodal scaffolds with novel structures and physicalchemical features (Hassan et al. a; Hassan et al. b; Ruso et al. ; D’Elía et al. ; Gravina et al. ; Ruso et al. ). The multifunctional or multimodal properties of these scaffolds result from the combination of different topographies that are not typically available in a given material, increasing their potential role in regenerative medical strategies (Gravina et al. ; D’Elía et al. ; Gravina et al. ; Hassan et al. a; Hassan et al. b; M Ruso et al. ). Polymers
8 Biopolymers for Medical Applications play a pivotal role to the construction of 3D templates and to the attainment of synthetic ECM environments for tissue regeneration (Sartuqui et al. ; Stevens and George ; Hong and Stegemann ; Geckil et al. ; Tsang and Bhatia ). Figure 2 shows the increasing interest in the study of polymeric materials and their application in tissue engineering; there is a particular emphasis on the development of musculoskeletal tissue’s substitutes. Among the common materials applied to regenerative medicine, the interest on polymers in the last ten years corresponds to the 60% of the researchers’ reports, Fig. 3. Biopolymers can be obtained from both synthetic and
scrivener 1.9.13 crack Activators Patch resources (Atala and Allickson ; Imam et al. ; JagurGrodzinski ; Kalia and Avérous ; Niaounakis ; Niaounakis ). Since each group possesses distinct advantages and limitations, a wide variety of composite materials and interpenetrating networks have been utilized to achieve desired results. Synthetic polymers are versatile to tailoring a wide range of degradation rates, structural features and mechanical properties,
scrivener 1.9.13 crack Activators Patch, representing a reliable mine of new-fangled materials. The composition of the synthetic polymers can be designed to minimize the immune response and combine the best properties together. Synthetic polymers
mcafee total protection product key free Activators Patch been described by their degradation by hydrolysis of the ester bonds under physiological conditions and to avoid problems of immunogenicity, that are compelling arguments for achieving the purpose and pursuing the approaches of TE and regenerative medicine (Atala and Allickson ). Nevertheless, the majority of synthetic polymers are hydrophobic, which presents a major drawback for the migration of viable cells into the scaffold core. Examples of synthetic and popular
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Biopolymers in Regenerative Medicine 9 4%1%
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biodegradable synthetic polymers include poly(ethylene glycol) (PEG)/poly(ethylene oxide) (PEO), Poly(ethylene-covinylacetate) (EVA), poly(α-hydroxy acids), especially poly(lactic acid) (PLA), poly(glycolic acid) (PGA) and their co-polymers, poly(εcaprolactone) (PLGA), poly(propylene fumarate), poly(dioxanone), polyorthoesters, polycarbonates, polyanhydrides, and polyphosphazenes. Particularly interesting are PLA and PGA polyesters which have been extensively used in biodegradable implants, tissue engineering, and drug delivery systems, see Tables 1 and 2. Natural polymers have been presented as an interesting option to the currently used synthetic materials due to a higher biodegradability rate and non-cytotoxicity (Atala and Allickson ). They are taken from native sources, exhibit similar properties to soft tissues; and their synthesis often involves enzyme-catalyzed, chain growth polymerization reactions of activated monomers, which are typically formed within cells by metabolic processes. Within this group are included collagen, gelatin, dextran, agarose/alginate,
windows 10 crack download acid, cellulose, and fibrin gels (see Tables 1 and 2). Although they have to be purified to avoid foreign body response after implantation, natural polymers are widely used in regenerative medicine. They have a wide range of mechanical, chemical, and physical properties, are resistant to biochemical attack, and as a consequence of their versatility and flexibility they can be easily processed and shaped. Moreover, they are inert towards host tissues after implantation and are available at a reasonable cost. Independent of their origin, polymers lack properties to stimulate biological functions, such as osteo-conductivity and cell bioactivity. As a consequence, hybrid variants of these materials have emerged through synthetic designs (Bourgeat-Lami et al. ) and genetic engineering of peptide-based biopolymers (Atala and Allickson ). Biodegradable polymers have been selected for the drug delivery system as they do not need surgery to be removed after releasing of the drugs and can be excreted by the body itself. Examples of biomedical applications using biopolymers include heart valves, vascular grafts, artificial hearts,
hotspot shield vpn elite apk full crack implants, contact lenses, intraocular lenses, components of extracorporeal oxygenators, dialyzers and plasmapheresis
NH2
O
OH
OH
O HO
O HO O
OH
O
OH
NH2
O
NH
O
n
HitFilm 4 Pro Crack + Activator Full Version Download Free n HO
*
OH
NH2
O OH
HO
O OH
O
m
O HO
O O
OH OH
n
O
1 →4 linked β-D-mannuronic acid (M) and α-L-guluronic acid (G) residues
O
OH
Alginic Acid/ Sodium Alginate
Characteristics
Alginic Acid or its sodium salt, Sodium Alginate, is an anionic polysaccharide disseminated in the cell walls of brown algae. G residues associate with divalent cations to form ionic crosslinks.
Chitosan is a linear polysaccharide obtained from deacetylation of chitin (main component
scrivener 1.9.13 crack Activators Patch the exoskeletons of crustaceans’ shells) and is a material structurally similar to GAGs, being degradable by enzymes in humans.
Hyaluronic acid (HA) is a glycosaminoglycan (GAG) present in all vertebrates. HA is a major component of connective
scrivener 1.9.13 crack Activators Patch and plays an important role in lubrication, cell differentiation, and cell growth.
Natural-Based Biopolymers
Randomly distributed b-()-linked D-glucosamine and N-acetyl-D-glucosamine
HO HO
OH
O HO
Chitosan
*
O
Hyaluronic Acid
Name
Table 1: Regular natural- and synthetic-based biopolymers involved in regenerative medicine.
10 Biopolymers for Medical Applications
Agarose
O
O
OH
OH
OH O
HO
O
O
OH
O
O
n OH
n
OH
OH
OH
O
O
carrageenan
CH2OH
poly-(R)hydroxybutyrate (P3HB)
O OH
OH OH
O
PHAs are linear polyesters produced in nature by bacterial fermentation of sugar or lipids.
Agarose is a natural-based polysaccharide obtained from agar.
It is extracted from red seaweeds; carrageenan displays close similarities with mammalian GAGs.
Gelatin
Mirillis Splash Pro 2.8.1 Crack Full With Serial Key Free Download is an irreversibly hydrolyzed form of collagen. Table 1 cont
Collagen is the central structural protein in the extracellular space in animals’ Monomeric and crosslinked 3D triple helical structures. Many types, type I consists of two connective tissues; it is the most abundant protein in mammals, representing about 25%–35% of the whole-body protein content. identical α1 chains and one α2 chain
O
Collagen
H
O
Poly(hydroxyalkanoates) (PHAs) /
H
OH
O
CH2OH -O2SO
scrivener 1.9.13 crack Activators Patch OH
Carrageenan
Biopolymers in Regenerative Medicine 11
Insoluble polymer found in non-mineralized tissues. Bundles form intermediate filaments that make up hair (α-keratins) and nails (β-keratins). Monomers form stable left-handed superhelical structures to form filaments. Silk is a natural protein fiber mainly composed of fibroin and is extracted from the cocoons of the Bombyxmori silkworm. Foams, sponges, films, and hydrogels are formed from the silk solution.
Keratin
Silk
Glycoprotein secreted by fibroblasts
Fibronectin
This binds integrins, transmits mechanical cues from the environment to the cell and binds other ECM proteins such as collagen and fibrin.
It is formed by the action of the protease thrombin that cleaves fibrinogen which causes the latter to polymerize, generating soft gels. Gelation kinetics is controlled by the ratio of thrombin to fibrinogen, calcium concentration, and temperature.
It is a fibrous, non-globular protein involved in the clotting of blood
Fibrin
Characteristics Elastin is the elastic component in soft tissues that allows tissue to return to normal shape following stretch or pinch. Formed by crosslinking smaller tropoelastin polymers using lysyl oxidase to form mesh-like structures.
Name
Natural-Based Biopolymers
Elastin
Table 1 cont.
12 Biopolymers for Medical Applications
H
OH
H
O
OH
H
CH2OH
n = -
OH
H
Starch H O
H H OH
H
O
OH
H
CH2OH H O n
H
H
OH
H
CH2OH
OH
H
O
OH
H
Table 1 cont
Starch is a polysaccharide consisting of a large number of glucose units joined by glycosidic bonds and produced by green plants as an energy store. It is quite abundant in nature and is an almost unlimited source and low-cost associated raw material.
Biopolymers in Regenerative Medicine 13
n
*
O
O
Poly(lactic
scrivener 1.9.13 crack Activators Patch (PLA)
*
O
m
*
H
n *
OCOCH3
n O
Polylactic acid (PLA) is thermoplastic, aliphatic polyester, produced from non-toxic renewable feedstock, naturally occurring organic acid, or made by fermentation of sugars obtained from renewable resources such as sugarcane.
Poly(ethylene-covinylacetate) (PEVA) is the copolymer of ethylene and vinylacetate. It is a polymer that approaches elastomeric (“rubber-like”) materials in softness and flexibility.
H
Poly(ethylene-covinylacetate) (PEVA)
Characteristics PEG, PEO, or POE refers to an oligomer or polymer of ethylene oxide. The three names are chemically synonymous, but historically PEG is preferred in the biomedical field, whereas PEO is more prevalent in the field of polymer chemistry.
Name
Synthetic-Based Biopolymers
Poly(ethylene glycol) (PEG)/Poly(ethylene oxide) (PEO)
Table 1 cont.
14 Biopolymers for Medical Applications
O n OH
HO
O O
Poly(propylene fumarate) (PPF)
*
Poly(ε-caprolactone) (PCL)
H
O
O
O
O
; HO
O
n
*
O
n
Polyglycolic Acid (PGA)/Poly l-glycolic Acid (PLGA)
O
OH
x O
O y
H
PPF can be cross-linked via radical polymerization by itself or with crosslinkers such as methylmethacrylate, N-vinyl pyrrolidinone (NVP), and biodegradable macromers of PPF-diacrylate or poly(ethylene glycol)diacrylate.
Polycaprolactone (PCL) is a biodegradable polyester with a low melting point of around 60°C and a glass transition temperature of about −60°C.
PGA and PLGA are synthesized by means of ring-opening copolymerization of two different monomers, the cyclic dimers (1,4-dioxane2,5-diones) of glycolic acid and lactic acid.
Biopolymers in Regenerative Medicine 15
Natural-Based
Biomaterial Form
Soluble, cationic in acidic conditions, and insoluble in neutral and basic conditions. Hemostatic stimulates osteo-conduction and wound healing. Shape-ability to fit the defect site, degradability. Degradation through ionic exchange with surrounding media. Variations in local mechanical properties controlled by concentration of calcium ions. Slow degradation profile and the low mechanical properties, 3D scaffolds exhibiting soft and flexible structure suitable for chondrocyte maintenance and MSC differentiation. Thermally, pH and cation concentration responsive material, in expensive and easy
alphacam 2018 download crack Activators Patch manipulate. Effectiveness in maintaining the proliferative and chondrogenic potential of encapsulated cells.
Alginic Acid/ Sodium Alginate
Agarose
Carrageenan
Hydrogel
3D Scaffolds, hydrogels.
Soft gels, composite materials, electrospun fibers.
3D Scaffolds, hydrogel, membrane, nano-particles.
Minimal immune response and 3D Scaffolds,
scrivener 1.9.13 crack Activators Patch, chemotactic combined with the hydrogels, adequate agents. Osteo-inductive electrospun and angiogenesis in combination fibers, nano-and with GFs. micro-gels.
Properties
Chitosan
Hyaluronic Acid
Biopolymer
Skeletal tissues regeneration, cell delivery system.
Skeletal tissues regeneration, efficient system for cartilagelike substitutes, islet, kidney and fibroblast encapsulation, nerve regeneration.
Wound healing, drug delivery, soft tissue engineering, cell delivery, in vitro stem cell maintenance.
Wound healing, orthopedics, cardiac repair, neural tissue engineering, cornea repair, drug and gene delivery.
Keratynocytes encapsulation, bone and cartilage reparation, drug delivery, vocal fold and nerve regeneration, spinal cord injuries.
Application
Table 2: Applications of natural- and synthetic-based biopolymers to regenerative medicine.
DIABECELL® NTCELL® Xelma
Hemcon®
Hyalograft 3D TM
Example of Approved Clinical Product
(Popa et al. ; Popa et al. ; Mihaila et al. )
(Stokols et al. ; Stoppel et al. ; Elisseeff et al. ; Chen et al. )
(Bressan et al. ; Stoppel et al. ; Tan ; Vowden et al. ; Lee et al. ; Ghidoni et al. ; Sun and Tan )
(Stoppel et al. ; Azad et al. ; Obara et al. ; Mi et al. ; Noel et al. ; Noel et al. ; Lu et al. ; Chien et al. ; Roy et al. ; Gustafson et al. )
(Bressan et al. ; Stoppel et al. ; Prestwich ; Burdick and Prestwich ; Lee et al. ; Jia et al. ; Park et al. ; Horn et al. )
16 Biopolymers for Medical Applications
Adequate substrate for bone cells growth. Scaffolds of brittle nature.
Low immune response, good substrate for cell adhesion, chemotactic,
scrivener 1.9.13 crack Activators Patch. Easily remodeled and degraded by cells. Chemical crosslinking decreases degradation and improves long-term mechanical properties. Many types available. Improper expression or mutation leads to disease. Small tropoelastin polymers can be used to form composite
Ashampoo Music Studio 8.0.6.0 Crack With License Key Free Download. Easily remodeled by cells. Stimulates cell migration, osteoconduction and vascularization. Fibrinolytic inhibitors, like aprotinin or aminocaproic acid, reduce in vitro degradation rates. Improper regulation of expression leads to diseases such as cancer, fibrosis.
PHAs
Collagen Gelatin
Elastin
Fibrin
Fibronectin
Grafted
Doxillion Document Converter Plus 5.54 Crack Registration Code 2D and 3D surfaces to improve biocompatibility.
3D scaffolds
Films, gels 3D scaffolds, electrospun fibers.
3D scaffolds, membrane.
Hydrogel,
3D Scaffolds, HAp nanocomposite, nano-particles.
Wound healing, stem cell differentiation, cardiac repair, bone regeneration.
Wound healing, lung and cardiac repair, in vivo cell delivery, bone defects reparation.
Cardiac stent coatings, soft tissue reconstruction, orthopedics and cell encapsulation.
Fibroblast and keratinocytes encapsulation, wound healing, skin substitute, muscle repair, nerve regeneration,
scrivener 1.9.13 crack Activators Patch, anti-aging, soft tissue reconstruction, bone repair.
Corneal epithelium repair, heart valves, bone tissue regeneration, drug delivery systems.
TachoSil® CASCADE® Autologous Platelet System
Integra TM ApliGraft® ORCEL TM NeuroFlex® NeuroMatrix® NeuroMend® Dynamatrix® INFUSE®
HCE
Table 2 cont
(Grinnell ; Mosahebi et al. ; Prestwich ; Barker ; Stoppel et al. )
(Siemer et al. ; Anegg et al. ; Torio-Padron et al. ; Cherubino and Marra ; Christman et al. ; Wu et al. )
(Boland et al. ; Jordan et al. ; Schwartz and Wolff ; Salzberg ; Sell et al. )
(Bressan et al. ; Stoppel et al. ; Heimbach et al. ; Halim et al. ; Meek and Coert ; Nevins et al. ; McKay et al. ; Zhang et al. a)
(Sodian et al,
scrivener 1.9.13 crack Activators Patch. ; Sodian et al. ; Errico et al. ; Pielichowska and Blazewicz )
Biopolymers in Regenerative Medicine 17
Natural-Based
Low enzymatic degradation rate controlled by crystallinity (β-sheet content), and some concerns arise on potential cytotoxic effects. Intrinsic mechanical properties. Mechanics tailored by modifying concentration, crystallization, molecular weight, and scaffold size. Thermoplastic behavior, promotes cell adhesion, non-cytotoxic and biocompatible.
Silk
Starch
Versatility of the PEG macromer chemistry and excellent biocompatibility.
Structure attributed to disulfide bridges; more bridges yields lower elasticity. Classified as neutralbasic or acidic, dictating in vivo occurrence.
Keratin
PEG/PEO
Properties
Biopolymer
Table 2 cont.
3D Scaffold, hydrogels, micelles.
3D scaffold
3D Scaffolds, foams, films, sponges, hydrogels, electrospun fibers.
3D scaffold, hydrogel, films.
Biomaterial Form
Fibroblast and keratinocytes encapsulation, ulcers wound healing, drug and gene delivery.
Bone and cartilage regeneration, spinal cord injury treatment.
Tendon and skeletal tissues regeneration, cornea repair, drug delivery.
Cornea tissue engineering, wound healing, skin regeneration, cardiac repair, drug delivery, nerve repair, cell encapsulation.
Application
Xelma
PolyActiveTM
Example of Approved Clinical Product
(Bressan et al. ; Lin and Anseth a; Park et al. ; Salinas et al. ; Elisseeff et al. ; Mahoney and Anseth ; Osada et al. ; Lin and Anseth a)
(Salgado et al. ; Martins et al. ; Gomes et al. ; SáLima et al. ; Salgado et al. )
(Zhang et al. b; Kundu ; Stoppel et al. ; Meinel et al. )
(Apel et al. ; ElloumiHannachi et al. ; Satija et al. ; Reichl ; Nishida et al. ; Sierpinski et al. )
18 Biopolymers for Medical Applications
Synthtic-Based
Low chemical versatility and slow degradation by hydrolysis or bulk erosion. Difficulties for withstanding mechanical loads.
Satisfactory biological results, mechanical properties inferior to those of PGA, PLGA.
PPF
and
PCL
Biodegradable thermoplastic polymer.
Degradation by hydrolysis. They can present some problems regarding cytotoxicity.
PLA
PGA/PLGA
It has low-temperature toughness, stress-crack resistance, hot-melt adhesive waterproof properties, and resistance to UV radiation.
PEVA
Hydrogel, 3D scaffold, nanocomposite.
3D scaffolds, nanocomposites, micelles, electrospun fibers, vesicles.
3D scaffolds, fibers, membranes.
3D scaffold, electrospun fibers, microspheres.
Micro/nanofibre layers, nano-composite scaffolds.
system,
Cartilage and bone regeneration, cell encapsulation, nerve regeneration.
Bone regeneration, drug delivery, cell encapsulation, skin regeneration.
Drug release, stents, stem cell encapsulation and differentiation, cartilage
scrivener 1.9.13 crack Activators Patch bone regeneration, facial nerve defects regeneration.
Fibroblast and keratynocytes encapsulation, macromolecules immobilization, bone, cartilage and nerve regeneration.
Drug delivery cardiovascular stents.
DermaGraftTM
(Liao et al. ; Lee et al. ; Kim et al. ; Wang et al. ; Tan and Marra ; Lee et al. )
(Williams et al. ; Fujihara et al. ; Allen et al. ; Reneker et al. ; JagurGrodzinski ; Cao et al,
scrivener 1.9.13 crack Activators Patch. ; Dai et al. )
(Crow et al. ; Tammela and Talja ; Kotsar et al. ; Zare-Mehrjardi et al. ; Mouthuy et al. ; Nassif and El Sabban ; Zhu and Lou )
(Bressan et al. ; Hart et al. ; Zhu et al. ; Kim et al. ; Evans et al. ; Kang et al. ; Uematsu et al. )
(Sultana et al. ; Alhusein et al. ; Strohbach and Busch )
Biopolymers in Regenerative Medicine 19
20 Biopolymers for Medical Applications units, coatings for pharmaceutical tablets and capsules, sutures, adhesives, and blood substitutes, kidney, liver, pancreas, bladder, bone cement, catheters, external and internal ear repairs, cardiac assist devices, implantable pumps, joint replacements, pacemaker, encapsulations, soft-tissue replacement, artificial blood vessels, artificial skin,
scrivener 1.9.13 crack Activators Patch, dentistry, drug delivery, and targeting sites of inflammation or tumors and bags for the transport of blood plasma (Langer and Tirrell ; Mani et al. ; Melek ; Meyers et al. ; Niaounakis ; Patel ; Rathenow et al. ; Ratner et al. ; Stevens ; Teck Lim et al. ; Terzic and Nelson ; Tseng et al. ; Weiss and Calvert ; White et al. ; Yu and Ding ; Zhou et al. ; Zilla et al. ); some selected examples are summarized in Table 2.
Building Biomimetic Materials on the Basis of Biopolymers: along Physic, Chemistry, Biology, and Materials Science The investigation of biopolymers has been reserved to biochemists and molecular biologists for over half a century. Nevertheless, during the last decade, the soft matter physics, chemical, and material science’s community has been seized to this research field (Chassenieux et al. ). The earliest multidisciplinary “bioengineering” collaborations were born sometime in the s–s. Those teams of physicians, chemists and engineers not only noted the necessity of regulating the composition, purity, and physical properties of the materials they were using, but also recognized the need for new materials with innovative and superior properties (Ratner et al. ). This inspired the expansion of many original materials, starting from the s. Novel materials were designed and fabricated specifically for medical use, such as biodegradable polymers, “medical grade” silicones, pyrolytic carbon, and bioactive glasses and ceramics. Others were derived from existing materials that were then manufactured using new technologies, such as polyester fibers that were knitted or woven in the form of tubes for use as vascular grafts or cellulose acetate plastic that was processed as bundles of hollow fibers for use in artificial kidney dialysers (Ratner et al. ). Further materials were specifically modified to provide special biological properties, resembling one of the earliest “bioengineered” biomaterials involving the immobilization of heparin to create anticoagulant surfaces (Ratner et al. ). Biopolymers become the new building blocks from the point of view of macromolecular chemistry; the models and the tools provided by the soft matter physical-chemical community resulted in a better understanding of the mechanisms involved during their assembly to perform analogous task of the biological molecular machines (Kay et al. ). For example, cells,
scrivener 1.9.13 crack Activators Patch, and connective tissue owe their remarkable mechanical properties to the complex biological macromolecular assemblies that are predominantly made from mixtures of stiff biopolymers (Kroy ; Meyers et al. ),
scrivener 1.9.13 crack Activators Patch. As the hardness of these biopolymers, and the resulting anisotropic networks leading to its smart mechanical and dynamic properties, are far from being understood, a better comprehension of their incessant assembly, disassembly, restructuring, active and passive mechanical deformation can be achieved by physical-chemical theoretical modeling (Dobrynin and Carrillo ; Pritchard et al. ). Moreover, molecular biologists can create accurate mutations
Biopolymers in Regenerative Medicine 21
of specific groups at precise points along the chain for understanding, for example, the influence of a particular residue on the folding–unfolding process; its stimulus on biopolymer mechanical properties can be directly obtained by atomic force microscopy (AFM) measurements (Alessandrini and Facci ). It should be noted that some implants and devices, such as artificial heart valves, are comprised of more than one class of biomaterial. Bio-nanocomposites is a fascinating and interdisciplinary topic that constitutes a great area of interest for biomedical technologies such as tissue engineering (Zhang et al. ), medical implants (Negroiu et al. ; Rathenow et al. ; Kidane et al. ), dental applications (Chen ), and controlled drug delivery (Morgan et al. ; Ke et al. ). Biopolymer nano-composites are the result of the precise combination of biopolymers and inorganic/organic units that interact at the nanometer scale. The extraordinary versatility of these new materials that comes from the large range of biopolymers and fillers available, such as clays, cellulose whiskers, and metal nanoparticles, can be tailored only by the correct confluence of multidisciplinary methodologies (Chassenieux et al. ). An extremely valuable tool for various applications in the science of biomaterials (Sionkowska ) is the use of hybrid polymer systems composed of natural and synthetic macromolecules. The goal of bio-artificial blending is to produce man-made assortments that confer unique structural and mechanical properties on the
scrivener 1.9.13 crack Activators Patch of the individual properties of natural polymers and synthetic polymers. Biopolymer’s blends are well known to exhibit a very rich and applicable phase behaviors (Chapman et al,
scrivener 1.9.13 crack Activators Patch. ; Sionkowska ) and the miscibility of their components is an important aspect in determining the properties of the blend. The understanding of the underlying physics of these phase behaviors and of the rheology–morphology relationships of the resulting phases constitutes an interesting and important challenge for their optimal applications (Chassenieux et al. ). Actually, biomaterials scientists and engineers have developed a growing interest in natural tissues and biopolymers in combination with living cells. This is particularly evident in the field of tissue engineering,
scrivener 1.9.13 crack Activators Patch, which focuses on the repair or regeneration of natural tissues and organs (Ratner et al. ). This interest has stimulated the development of novel technologies for the isolation, purification, and application of many different natural materials, including de-cellularized natural tissues and spider silk.
Biopolymers for Hard and Soft Tissue Regenerations Although the reconstruction of small or moderate sized tissue imperfections are technically feasible, thanks to the natural
scrivener 1.9.13 crack Activators Patch of the body to repair itself, larger volume defects remain problematic. The state-of-the-art of medical and surgical therapies continues to be suboptimal, in part because of a lack of replacement biological parts (Bressan et al.
scrivener 1.9.13 crack Activators Patch. In this sense, many
scrivener 1.9.13 crack Activators Patch biomaterials based on biopolymers have been widely considered for hard and soft tissue reconstruction. They can be used alone or combined with other synthetic or inorganic constituents. The main properties of these tissue engineered materials are the special dressing, nursing care, and the reduced time in grafting. Regardless of their mechanical fragility and high cost, many recent in vivo investigations contributed to the FDA approval of new
22 Biopolymers for Medical Applications biomaterials for clinical use based on natural biopolymers as matrices for cell delivery and as scaffolds for cell-free support of native tissues. Some selected examples are
scrivener 1.9.13 crack Activators Patch in Table 2.
Biopolymers gels for cell encapsulation Mammalian cells encapsulation on biopolymer gels becomes an increasing area of interest in regenerative medicine (Hunt and Grover ). The application these strategies to TE can be split into two main categories (Nedovic and Willaert ): (i) the replacement of the biochemical function or (ii) the replacement of the structurally functional tissue. Cell encapsulation in biopolymer hydrogels was originally explored for immuno isolation of cells producing therapeutic proteins for treatment of diseases. In such strategy it is required the chemical communication in the scaffold (i.e., diffusion of molecules),so it is possible to deliver cells encapsulated in an immuno isolatory nanoporous polymer membrane. The membranes are constructed in a way that their pores have to be large enough to allow nutrients, waste, and bioactive factors to diffuse
scrivener 1.9.13 crack Activators Patch not so large as to allow immune cells to attack the cells inside (Nedovic and Willaert ). This strategy has mainly
scrivener 1.9.13 crack Activators Patch employed to temporarily or permanently replace biochemical functions of the liver pancreas, and
scrivener 1.9.13 crack Activators Patch local protein delivery in neurological disorders. More recently, encapsulation of mammalian cells has been used in the regeneration of an array of different tissues. This second major strategy involves entrapping cells on a micro- or macro-porous polymer scaffold and promoting the formation of a new tissue that is structurally and functionally integrated with the surrounding tissue. The scaffold is constructed with a biocompatible material that it will degrade over time to leave only the integrated tissue in its place. A variety of naturally derived and synthetic biopolymers that can be processed into many different physical forms and geometries are used for cell encapsulation. The biomaterial component of these therapies must provide the appropriate mass transport properties, membrane or scaffold stability, and desirable cellular interactions depending on the location and desired function of the implant. Some of these studies are summarized in Table 2.
Stimuli responsive hydrogels based on biopolymers Intelligent hydrogels based on biopolymers which can change their swelling behavior and other properties in response to chemical and physical stimuli such as pH, metabolites or/and ionic factors, temperature and electric fields, have attracted great interest. These ‘‘smart’’ hydrogels, in addition to their biocompatibility, biodegradability, and biological functions, exhibit single or multiple stimuliresponsive characters which could be used in biomedical applications, ranging from controlled drug delivery systems and cell adhesion mediators to controllers of enzyme function and gene expression in bioengineering or tissue engineering. Among them, temperature- and pH-responsive hydrogels have been the most widely studied, because these two factors have physiological significance (Oh et al. ; Chilkoti et al. ; Prabaharan and Mano ; Alarcon et al. ). Biopolymers having a lower critical solution temperature (LCST) below human body temperature have a potential for
Biopolymers in Regenerative Medicine 23
injectable depot systems in therapeutic delivery systems and in tissue engineering. A number of polysaccharides have been considered to be combined with the thermoresponsive materials including chitosan, alginate, cellulose, and dextran. Due to the pH-sensitive character of chitosan or alginate, combination of these polymers with a thermoresponsive material will produce dual-stimuli-responsive polymeric gels to be used as delivery vehicles that respond to localized conditions of pH and temperature in the human body (Prabaharan and Mano ). Control over the function of a therapeutic biopolymer can be obtained by polymer–biopolymer conjugate chemistry. Responsive polymer–biopolymer conjugates have been extensively studied by Hoffman, Stayton, and co-workers (Hoffman ; Pack et al. ). They reported a temperature and photochemically switchable endoglucanase that displayed varying and opposite activities depending whether temperature or UV–Vis illumination was used as the switch (Shimoboji et al. ). Regarding synthetic polymers, Poly(Nisopropylacrylamide) (PNIPAm) is the most studied. It undergoes a sharp coil–globule transition in water at 32°C, changing from a hydrophilic to a hydrophobic state below this temperature. Surface modification of materials can be used to control and modulate cellular-material interactions, for example, to promote bone and skin cell interaction with the implant, and to prevent the adhesion of unwanted cells. Okano and co-workers have extensively used thermoresponsive PNIPAm-based polymers as surface mediators of biopolymer and cell attachment (Okano and Winnik ; Peppas et al. ). Human skin fibroblasts have been shown to attach to and proliferate at the surface of thermoresponsive hydrogels of ethylene glycol vinyl ether and butyl vinyl ether co-polymers. Cultured cells were readily detached from the polymer surface by lowering the incubation temperature from 37°C to 10°C for 30 min. Incorporation of Arg-Gly-Asp (RGD) peptides at the surfaces resulted in higher values of cell proliferation in the initial stage (Gümüşderelioğlu and Karakeçili ). Stile and Healy, extended this concept by the preparation of PNIPAm–RGD conjugates and manipulated osteoblast adhesion (Stile et al. ).
3D bio-printed scaffolds In order to permit cell morphogenesis associated with living tissue function, there is a need to supply the cells with appropriate stimuli within their physical 3D support structure. As it was mentioned in previous sections, biomimetic hydrogel scaffolds can be easily designed
scrivener 1.9.13 crack Activators Patch natural ECM components, including collagen or fibrin. However, the range of physical properties, such as stiffness and mesh size—which can be controlled by the gelation process of the purified proteins—is relatively narrow. In addition, these materials are not typically available in large quantities and suffer from batch-to batch variations. Several attempts were made to improve the properties of protein hydrogel scaffolds by the introduction of covalent cross-linking,
scrivener 1.9.13 crack Activators Patch, improving the self-assembly of the protein molecules or adding a coexistent polymer network (Zhu and Marchant ; Rajaram et al. ; Suo et al. ; Ahmed ). Because most of the conventional techniques for scaffold preparation are limited when it comes to the spatial control of porosity and pore size, computer-aided design (CAD) and advanced manufacturing techniques to improve scaffold development have been
24 Biopolymers for Medical Applications adopted by the tissue engineering community (Li et al. ; Bose et al. ). 3D bio-printing refers to the application of 3D printing technologies towards the development of precisely defined scaffolds for tissue regeneration. Although in the middle of s the term was reserved only for inkjet-based approaches, nowadays it is collectively used for all additive manufacturing (AM) processes (Li et al. ; Gross et al. ). 3D printing strategies can be applied, in one way or another, to bio-printing; these include: stereolithography (SLA) (Dhariwala et al. ), selective laser sintering (SLS) (Chang et al. ), fused deposition modeling (FDM) (Mironov et al. ), syringe deposition (Zhang et al. ),
scrivener 1.9.13 crack Activators Patch, two photon laser lithography (Müller et al. ), powder printing (Gbureck et al. ), 3D inkjet printing (Xu et al. ), and organ printing (Mironov et al. ). All of these AM technologies have in common the capability to build a scaffold or tissue construct with complicated 3D geometries, without the necessity of tooling, directly from CAD files and using chloroform for binding polylactic acid (PLA) and polyglycolic acid (PGA) powders in a powder binding approach. Chloroform was used for selective solvation
home design pro the polymeric particles, resulting in particle adhesion upon chloroform evaporation (Li et al. ). Engineers and clinicians arrived to a widespread consensus that 3D bioprinting will permit the manufacturing of much more complex and intricate scaffolds for tissue regeneration, mainly because of the opportunities it presents for customizing scaffold shape, structural complexity, and cellular organization. Selected examples are summarized in Table 2.
“Engineered’’ peptide-based biopolymers in biomedicine and biotechnology In the s, the fundamental polypeptides structural features were elucidated. Forty years later, Ghadiri (Ghadiri et al. ) and Zhang (Zhang et al. ) demonstrated that these rules can be exploited and adapted to produce supramolecular peptide based materials (Zelzer and Ulijn ). A fresh class of biomaterials becomes known due to the exceptional chemical, physical, and biological properties of the “engineered’’ peptide-based biopolymers. The expansion of peptide-based biomaterials was motivated by the convergence of protein engineering and macromolecular self-assembly (Chow et al. ). Prototypical examples of engineered peptide-based biomaterials include poly-amino acids, elastin-like polypeptides, silk-like proteins, coiled-coil domains, tropoelastin-based peptides, leucinezipper-based peptides, peptide amphiphiles, betasheet forming ionic oligopeptides, and beta-hairpin peptides (Chow et al. ). In addition, biopolymers can be easily functionalized to enhance their interactions with cells and provide an optimal platform for cellular activities and tissue functions. In this section, we will discuss two main classes of peptide-based biopolymers in tissue engineering: self-assembling polypeptides that form gels by environmental stimuli and polypeptides that form gels via chemical
scrivener 1.9.13 crack Activators Patch. The first class of hydrogels is based on naturally occurring fibrin, which is spontaneously formed by the polymerization of fibrinogen in the
scrivener 1.9.13 crack Activators Patch of thrombin and further cross-linked by the transglutaminase activity of factor XIIIa (Ehrbar et al. ; Schmoekel et al. ; Park et al. ; Sakiyama et al. ; Lee et al. ;
Biopolymers in Regenerative Medicine 25
Nettles et al. ; McHale et al. ). Gel formulations prepared from fibrin glue plus matrix-bound vascular endothelial growth factors (VEGFs) are also promising candidate substrates for expansion or transplantation of endothelial progenitor cells (EPCs). Ehrbar et al. studied three variant
scrivener 1.9.13 crack Activators Patch (VEGF), formulated within fibrin matrices, each with differential susceptibility to local cellular proteolytic activity (Ehrbar et al. ). Fibrin matrices were also successfully improved with bone morphogenetic protein-2 (BMP-2) to promote bone growth and healing (Schmoekel et al. ;
Scrivener 1.9.13 crack Activators Patch et al. ) and with heparin-binding proteins to promote neuritis extension (Sakiyama et al. ; Lee et al. ). Elastin-like polypeptides (ELP) are useful for thermally sensitive injectable hydrogels because they undergo an inverse temperature phase transition and can be designed at the molecular level. The study of ELPs was pioneered by Dan Urry (Urry ),
scrivener 1.9.13 crack Activators Patch, who synthesized a large number of polypeptides over the course of three decades and studied their biophysical properties in solution and as cross-linked elastomeric materials. ELPs have been investigated as an alternative scaffold for cartilage repair (McHale et al. ; Nettles et al. ). To emulate
Filmora 8.2 Licensed email and Registration code triple helical structure of collagen, peptide-amphiphiles (PAs) consisting of a collagen sequence Gly-Val-Lys-Gly-Asp-Lys-Gly-Asn-Pro-Gly-TrpPro-Gly-Ala-Pro connected to a long-chain mono- or di-alkyl ester lipid, have been synthesized by Fields, Tirrell and coworkers (Yu et al. ). Neither the peptide nor the tail alone produced significant adhesion of
scrivener 1.9.13 crack Activators Patch cells; however, the self-assembled triple helical structure of the PA significantly promoted cell adhesion (Fields et al. ). In the second class of hydrogels,
scrivener 1.9.13 crack Activators Patch, chemically cross-linked 3D networks are formed by Michael-type addition reactions between thiol-bearing bioactive peptides and conjugated unsaturations on single- or multi-armed poly(ethylene glycol) (PEG) chains end functionalized with vinyl sulfone (Hubbell ). ELP are also good candidates for chemical crosslinking, because it is easy to incorporate chemically active amino acids at the guest residue position in the elastin-based repeat unit, Val-Pro-Gly-Xaa-Gly and in addition, because ELPs can be designed at the molecular level and genetically synthesized, unique properties can be introduced by incorporating other biologically active peptide sequences,
scrivener 1.9.13 crack Activators Patch. Examples can be found of ELP hydrogels that are formed by irradiation (Annabi et al. a), photo-initiation (Almany and Seliktar ), aminereactive chemical crosslinking (Annabi et al. b), and enzymatic crosslinking by tissue transglutaminase (McHale et al. ; Davis et al. ; Collighan and Griffin ). The hydrogels have been successfully used for cartilage and intervertebral disc tissue repair, small-diameter vascular grafts, urinary bladders, stem cell matrices, neural guides, stem cell sheets, and post-surgical wound treatment (Simnick et al. ; Chow et al. ; Lim ). The application of chemically cross-linked ELP hydrogels for in situ gelation by chemical
scrivener 1.9.13 crack Activators Patch has been limited by poor solubility in water, concerns about toxicity, lack of biocompatible crosslinking reagents and by products, or slow gelation kinetics. Even though peptide-based biomaterials have become increasingly significant materials in regenerative medicine, their
scrivener 1.9.13 crack Activators Patch has restrictions, related to their short shelf life and thermal instability. Many of these limitations can be addressed by emerging technologies, thus further expanding the uses of peptide-based biomaterials into applications for which they are currently impractical.
26 Biopolymers for Medical Applications
Perspectives and Outlooks Biomaterial design and its application to regenerative medicine have made great strides in the past decades and holds tremendous impact for future clinical applications. Sustained growth of this field centers in part on the development of novel materials and improved scaffold processing techniques. The specificities of the biopolymer block in terms of bioactivity, biocompatibility, and biodegradability allow specific application over the bio-medical fields. Polymer–biopolymer interactions can increasingly be designed as well as selected, and so their intervention in cellular dysfunctions may be possible and lead to more powerful, specific, and potent therapies. Moreover, a deeper comprehension of the underlying mechanisms of tissue regeneration would contribute invaluably to tailoring scaffold properties in a more representative manner of the native environment. Currently, the focus has been on addressing biomimetic surface topography for influencing cell behavior, controlled delivery of bioactive signals to stimulate regeneration, bone construct vascularization, articular cartilage zonal architecture, and osteochondral interface integration. Polymer chains can be prepared with individual segments that respond to pH, temperature, ionic strength, UV irradiation and electric fields, affording truly multifunctional materials. ‘Chemically-responsive’ systems, such as the glucose-sensitive polymers, are also becoming accessible. Structure–function relationships previously only obtainable for biomacromolecules can now be deduced for wholly synthetic materials owing to the degree of control accessible through living polymerisation methodologies, while biopolymer synthesis and activity can be manipulated through molecular biology approaches. This convergence of synthetic and natural macromolecular chemistry inherently leads to biomedical applications, as the ability to control polymer structure leads to the ability to manipulate functionality. Bio-printers can automate the assembly process and permit pre-programmed and complex manipulation of biopolymers—from the macromolecular to the living cell level—to achieve architectural and biochemical complexity that was never before possible and produce tissue and organ substitutes that precisely mimic their natural counterparts. It is expected that these diverse methodologies for regenerative medicine will translate from ‘bench to bedside’ in the future.
Acknowledgements The authors acknowledge Universidad Nacional del Sur (PGI 24/Q), Concejo Nacional de Investigaciones Científicas y Técnicas de la República Argentina (CONICET, PIP—CO) and Fundación Ramón Areces. PVM is an independent researcher of CONICET.
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scrivener 1.9.13 crack Activators Patch, interfaces and supramolecular functionality. Chemical Society Reviews – Zhang, L. G., J. P. Fisher and K. Leong. 3D Bioprinting and Nanotechnology in Tissue Engineering and Regenerative Medicine. Academic Press, London NW1 7BY,UK. Zhang, S., T,
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2 Application of Natural, Semi-synthetic, and Synthetic Biopolymers used in Drug Delivery Systems Design Javier Sartuqui,§ Noelia L. D’Elía,§ A. Noel Gravina§ and Luciano A. Benedini* Introduction Science and technology play a key role in the extended life expectancy. In this sense, a wide range of innovative techniques and new devices have been developed, resulting in a reduction of morbidity and mortality. The use of drug delivery systems to improve the efficacy of bioactive molecules remains essential strategy for achieving the treatment against diseases and the progress in this field has been essential. In this context, synthetic, semi-synthetic, or natural polymers are frequently used for developing drug delivery systems. Accordingly, their application goes from the generation of suspension with cyclodextrins to solubilize hydrophobic drugs to the formation of matrices which control, by means of their degradation, the release of drugs.
Departamento de Química, Universidad Nacional del Sur, INQUISUR-CONICET () Bahía Blanca,
Scrivener 1.9.13 crack Activators Patch. * Corresponding author: [emailprotected] § These authors contributed in the same way to this work.
Biopolymers
scrivener 1.9.13 crack Activators Patch in Drug Delivery Systems 39
There are relevant factors that should be evaluated when choosing a polymer for use as a drug carrier. One of the most important is the biocompatibility, which is related with the acceptance of the material by tissues. The problems encompassing this condition can include hypersensitivity reactions; since that the pharmaceutical formulation should be in contact with different tissues, some of them more sensitive than others, the long time by an increased time of carrier-tissue interaction
scrivener 1.9.13 crack Activators Patch cause an alteration in drug biodisponibility due to changing biopharmaceutical parameters. Biodegradability is the timely degradation of the polymer in contact with the tissue; this is the other important feature that must be considered. Furthermore, the drug delivery system must be degraded and their components removed from the body to prevent their accumulation, and thus avoiding any potential toxicity. In accordance with green chemistry, a solvent free processing to obtain the different drugs
scrivener 1.9.13 crack Activators Patch is also important because the reduction of contaminant by-products is one of the biggest challenges for developing pharmaceutical products. Frequently, natural polymers are synthetically modified to reinforce their positive features and to decrease the negative ones. These new compounds are named semisynthetic derivatives. Sometimes positive characteristics can be improved, but negatives cannot be abolished. Hence, their advantages and disadvantages must be critically discussed, and the biocompatibility of these natural materials and their derivatives must be compared. Occasionally, availability from renewable resources is also considerate; and therefore, natural and semi-synthetic polymers are often advantageous compared to synthetic alternatives. Finally, when active biomolecules are
scrivener 1.9.13 crack Activators Patch into formulations based in polymers, their physicochemical features, and sensibility must be considered. Thus, some characteristics of the drugs such as charge and solubility, among others, could direct their inclusion into a polymeric matrix. On the other hand, sensitive drugs such as peptides, proteins, and nucleic acids are increasing their relevance and this effect is due to the fact that potential treatment options have a medical unmet demand which is not covered by classical drug therapies. For these active pharmaceutical ingredients (API), additional conditions must be taken into consideration.
Polysaccharides Polysaccharides are polymeric biomaterials widely studied for drug delivery applications. These compounds can be produced by from microorganisms, animals,
scrivener 1.9.13 crack Activators Patch, and plants; hence, they represent a renewable resource and are regarded as economical and environmentally favorable. Polysaccharides used for these applications combine several advantageous properties both clinical and physicochemical,
scrivener 1.9.13 crack Activators Patch. Among the former can be mentioned low toxicity, good biocompatibility, and biodegradability, and among the latter, high stability and hydrophilicity. In addition, natural polysaccharides can be modified to improve, enhance, or avoid any molecular feature necessary to reach the ultimate objective. Thus, in this section we will focus on their main structural features and their importance in polysaccharides-based drug delivery systems.
40 Biopolymers for Medical Applications
Cyclodextrins Cyclodextrins (CDs) are crystalline, non-hygroscopic, and cyclic oligosaccharides derived from starch. The first reference to a substance which later proved to be a CD, was published by Villiers, in (Villiers ) and was named “cellulosine” by Schardinger (Schardinger ). He also observed that two distinct crystalline “cellulosines” were formed, being probably α- and β-CDs. However, it wasn’t until the s when preparations of CDs, their structure, physical and chemical properties, as well as their inclusion complex forming properties were discovered (Szejtli ). Chemically, CDs are cyclic oligosaccharides containing at least six D-(+)glucopyranose units attached by α (1→4) glucoside bonds. The three natural cyclodextrins, α, β, and γ; differ in their ring size, solubility, and their content of glucose units, having 6, 7, or 8, respectively (Rowe et al. ). However, Endo et al. () established an isolation and purification method for several kinds of large ring CDs and they also obtained a relatively large amount of δ-CD (Cyclomaltonose) with nine glucose units. Furthermore, both their molecular
scrivener 1.9.13 crack Activators Patch and their size cavity are increased from α to δ-CD. On the other hand,
scrivener 1.9.13 crack Activators Patch, it must be considered that CDs can be modified to improve some of their physicochemical or toxicological features, and also to enhance physical and microbiological stability. From β-CD, numerous derivatives were obtained by chemical modification such as hydroxyethyl-β-CD, hydroxypropylβ-CD, sulfobutylether-β-CD, methyl-β-CD among others. Cyclodextrins have lipophilic inner cavities and hydrophilic outer surfaces, and are capable of interacting with a large variety of guest molecules to form non-covalent inclusion complexes. The lipophilicity of the cavity is due to the arrangement of hydroxyl groups within the molecule. They are chemically stable in neutral and basic conditions and undergo non-enzymatic hydrolysis in acidic conditions. According to the classification given by different pharmacopoeias, CDs are used as solubilizing and/ or stabilizing agents. CDs have been playing a very important role in formulation of poorly water-soluble drugs by improving apparent drug solubility and/or dissolution through inclusion complexation or solid dispersion (Tasić et al. ). In this context, the importance of CDs applications is found in the design of various novel delivery systems such as liposomes, microspheres, microcapsules, and nanoparticles (Challa et al. ). There are some factors influencing the formation and stability of inclusion complexes such as the presence of charge when the complexes drug-CDs are formed, temperature changes, addition of other co-polymers, and the preparation method of the formulation (Nagase et al. ; Mura et al. ). β-cyclodextrins is the least expensive and therefore the most commonly used CD, even though it is the least soluble. Hence, it is primarily used in tablets and capsules formulations. In the case of parenteral formulations, α-CD is mainly used; however, resulting from having the smallest cavity among CDs, it can only form inclusion complexes with small-sized molecules. In contrast, γ-CD has the largest cavity and it can be used to form inclusion complexes with big molecules (Rowe et al. ). β-cyclodextrin may be used to develop an oral tablet formulation by means of wetgranulation and, on
scrivener 1.9.13 crack Activators Patch other hand, by direct-compression processes. In parenteral formulations, CDs have been used to produce stable and soluble preparations of drugs that would otherwise have been formulated using a non-aqueous solvent.
Biopolymers used in Drug Delivery Systems 41
In eye drops formulations, CDs form water-soluble complexes with lipophilic drugs such as corticosteroids and vitamin D2 (Palmieri et al. ). They can increase the water solubility of the drug, enhance drug absorption into the eye, improve aqueous stability, and reduce local irritation (Loftsson and Stefánsson ). CDs have also been used in the formulation of solutions (Prankerd et al. ), suppositories (Szente et al. ; Szente et al,
scrivener 1.9.13 crack Activators Patch. ), and cosmetics (Amann and Dressnandt ; Buschmann and Schollmeyer ). In addition, other kind of drug delivery systems has been designed with CDs to carry sensitive drugs. In this context, it has been reported that their use as non-viral
scrivener 1.9.13 crack Activators Patch for gene delivery induced an increment in the transfection efficiency, with high levels of reporter gene expression and also with low toxicity (Redenti et al. ; O’Neill et al. ; Lai ). Promising carriers for anti-cancer drug delivery in tumor therapy have been reported by Tan et al. (Tan et al. ). This research has shown greater control of drug release by incorporation of CDs into polymeric drug delivery systems. Here, 5-fluorouracil, doxorubicin, and vinblastine are carried into a complex built by a covalently linked reaction between chitosan and carboxylic acid group of CDs. These cyclic polysaccharides are able to have close cellular interactions, which make them a suitable option for carrying peptides, oligonucleotides, and proteins. All toxicity studies have demonstrated that, when orally administered, CDs are practically non-toxic due to the lack of absorption in the gastrointestinal tract (Irie and Uekama ). However, lipophilic methylated CDs are surface active and they are, to some extent (~ 10%), absorbed in the gastrointestinal tract. Consequently only limited amounts of these lipophilic CD derivatives can be included in oral formulations and they are unsuitable for parenteral formulations. Furthermore, α, β, and methylated CDs are nephrotoxic and should not be used in parenteral formulations. In contrast, γ-CD, 2-hydroxypropyl-β-CD, sulfobutylether β-CD, sulfated β-CD, and maltosyl β-CD appear to be safe even when administered parenterally.
Cellulose and derivatives Cellulose is the most abundant substance in the biosphere; it is the main molecule of cell walls of higher plants and it is also produced by some algae, fungi, protozoans, tunicates, and bacteria. The molecule is a linear polymer of D-anhydroglucopyranose units linked together by (1→4)-β-glycosidic bonds. The extensive intra- and intermolecular hydrogen bonding between the individual chains (Hinterstoisser and Salmén ) make it insoluble in water and most common solvents (Rowe et al. ). In order to improve water solubility, various cellulose derivatives have been synthesized by etherification
scrivener 1.9.13 crack Activators Patch the hydroxyl groups on anhydroglucose units of cellulose. Hence, the most widely used are methyl cellulose, carboxymethyl cellulose, hydroxypropyl cellulose, hydroxypropyl methyl cellulose (HPMC), hydroxyethyl cellulose, and ethylhydroxyethyl cellulose. Bacterial cellulose (BC), originally reported by Brown (Brown ), has attracted considerable attention in both drug delivery and biomedical fields due to its unique fibrillar nanostructure, high water holding capacity, high degree of polymerization, high mechanical strength, and degree of crystallinity, as well as its availability for being effectively produced in high purity by
42 Biopolymers for Medical Applications Acetobacterxylinum (Esa et al. ). Cellulose and its derivatives have been widely used in the pharmaceutical industry due to their ability to swell in contact with water and their high compatibility which makes them suitable as a binder/diluent and also as an disintegrant agent in oral tablets and capsules, depending on the substitution degree (SD). Cellulose derivatives are able to form hydrogels and therefore, are appropriate as suspending or viscosity-increasing agents for oral suspensions. Other kind of applications such as wound dressing, transdermal patches, and ophthalmic preparations have also been reported for some of these derivatives; these traditional applications have been extensively discussed in literature (Shokri and Adibkia ; Kamel et al. ; Rowe et al. ). In native cellulose, the adjacent chains of the polymer fit closely together in an ordered crystalline region, resulting in a product with high strength. Different degrees of crystallinity can be found according to the source and degree of processing of the raw material which, in turn, varies the mechanical properties of the final product. Young’s Modulus, for example, can vary from to GPa in cellulose obtained from wood fibers (Wang ). As mentioned before, cellulose derivatives are able to form gels and a wide range of mechanical properties can be obtained depending on the SD, nature of the solvent, and concentration (Jain et al. ). Bacterial cellulose exists as a basic fibrillar structure times smaller than plant cellulose and highly crystalline (Esa et al. ). Its reported elastic modulus was approximately 10 GPa (Iguchi et al. ; Svensson et al. ), which is comparable to that of the articular cartilage, and this is extraordinary large for an organic material with a two dimensional structure. Therefore, bacterial cellulose is a suitable candidate to be applied in tissue engineering and also to develop membranes for controlled release for drugs. Cellulose and its ethers commonly used in the pharmaceutical industry induce negligible foreign body and inflammatory responses, being generally regarded as a non-toxic and non-irritant material. However, oral consumption of large amounts of them may have a laxative effect. In vivo biocompatibility of BC implanted subcutaneously in rats for up to 12 weeks has been studied, proving good integration into the host tissue, and no signs of inflammation or foreign body response (Helenius et al,
scrivener 1.9.13 crack Activators Patch. ). Regarding their degradation, these materials are considered non- or slowly biodegradable in vivo, due to the lack of cellulase enzymes in animals (Dugan et al. ). Bacterial cellulose and its ethers can be used to create “smart” materials, which present differential behaviors under environmental stimulus. This fact constitutes a very versatile feature for drug delivery systems. Hydrogels, membranes, self-assembled systems, and nanocomposites are among the most widely investigated alternatives (Edgar ). In the particular case of BC, sources directly influence structure because its properties vary with bacterial strain and culture media; therefore, its knowledge can be used to tailor the material for different drug delivery purposes. A cellulose nanofibers–titania composite is currently under development for drug delivery of anesthetics, analgesics, and antibiotics (Galkina et al. ).
Scrivener 1.9.13 crack Activators Patch material is presented as an interesting alternative for wound-dressing with transdermal drug delivery properties. Sodium diclofenac, D-penicillamine, and phosphomycin were used as model drugs, showing uniform distribution within the nanofiber film and long-term drug release with different profiles: the quickest release was observed for
Biopolymers used in Drug Delivery Systems 43
the painkiller, a slower one for the anti-inflammatory agent, and the longest release took place for the strongly chemisorbed antibiotic agent. Polymer-nanoparticle (PNP) hydrogels were recently developed by mixing HPMC and carboxy-functionalized polystyrene nanoparticles (PSNPs) by Appel et al. ( ). Interestingly, these self-assembled hydrogels are able to flow under applied shear stress, followed by rapid self-healing when the stress is relaxed, allowing its safe subcutaneous injection. Moreover,
scrivener 1.9.13 crack Activators Patch, owing to the hierarchical structure of the gel, molecular delivery was controlled allowing differential release of multiple compounds (tested with hydrophobic and hydrophilic therapeutic models, in both in vitro and in vivo systems). BC membranes produced from Gluconacetobactersacchari have been developed as systems for topical and transdermal drug delivery; using lidocaine hydrochloride and ibuprofen as models for hydrophilic and hydrophobic drugs, respectively. Trovatti et al. (Trovatti et al. ) proved that permeation rate is higher for the hydrophobic drug than for the hydrophilic one, demonstrating that these delivery systems can be tuned to modulate the bioavailability of drugs for percutaneous administration, having the advantage of using a membrane that is also able to absorb exudates and to adhere to irregular skin surfaces. Recently, Amin et al. () combined BC obtained from cream of coconut (also known as nata de coco) and different proportions of acrylic acid to fabricate thermally stable hydrogels with moldable pore sizes. Therefore, in vitro drug release studies with bovine serum albumin showed a thermo- and pH-responsive behavior of the hydrogels suggesting them as a suitable system for temperature-controlled delivery of protein-based drugs.
Guar gum Guar gum is a hydrocolloidal galactomannan that structurally comprises long and straight chains of (1→4)-α-D-mannopyranosyl units linked together by (1→4)-β-Dgalactopyranosyl units by (1→6) linkages. The ratio of D-mannose to D-galactose of guar gum has been known to be approximately and A single molecular weight is estimated to be in the range of kDa to kDa (Schierbaum ). Guar gum is obtained by grinding the endosperm portion of a leguminous plant called Cyamoposistetragonolobus (L.) Taub. that is grown mainly in India, Pakistan,
scrivener 1.9.13 crack Activators Patch, and United States to produce seeds used for human and animal food (Rowe et al. ). Additionally, guar gum exhibits potential applications in various fields such as drugs, cosmetic, food, and textile industries. Different guar gum composites have been studied to improve the properties of conventional food technologies such as thermoplastic polymers and fillers (Funami et al. ). Generally, this hydrocolloidal agent is used as an additive in the food industry to facilitate gelling, thickening, firming, and emulsification of food products but a high viscosity (2, to 3, mPa.s) is reached when its concentration is above 1% w/v and this is a limiting factor for its use in food products (McCleary ), resulting in liquid products which are highly viscous. In order to reduce its viscosity, it may be processed into partially hydrolysed guar gum (PHGG), which is obtained by controlled partial enzymatic hydrolysis of guar gum seeds (Flammang et al. ). PHGG has the same chemical structure as the original guar gum, but with a significantly reduced molecular weight of around 20 kDa and one-tenth of the original chain length (Yoon et al. ). Guar gum produces
44 Biopolymers for Medical Applications a pseudoplastic viscous solution when hydrated in cold water and it also has a lowshear viscosity greater than other hydrocolloids (Brosio et al. ). Mechanical properties studies of low concentrated and almost monodisperse guar gums suspensions have shown that there is a plateau in the storage modulus at a frequency of ω = It was demonstrated that guar gum enhance rheological
scrivener 1.9.13 crack Activators Patch large deformation properties of soybean β-conglycinin gel. Moreover, due to increasing concentrations of guar gum the elastic modulus of the composite is also increased (Zhu et al. ). Guar gum has many desirable properties for drug delivery applications and is generally used as a sustained release excipient owing to its high viscosity, low cost, and commercial availability. This compound forms a hydrophilic matrix that could be used as oral carrier for controlled delivery of drugs with varying solubility; therefore, its gelling property retards the release of drugs from the dosage form and it is susceptible to degradation in the colonic environment (Jain et al. ; Bhalla and Shah ; Krishnaiah et al. ). In order to improve its applications as
scrivener 1.9.13 crack Activators Patch delivery carrier, several chemical modifications have been made on guar gum such as cross-linking with borax, glutaraldehyde, and trisodiumtrimeta phosphate. These cross-linked formations reduce its enormous swelling. Furthermore, for the preparation of different guar gum-based systems, combinations with other natural or synthetic polymers such as polyacrylamide, polyvinylpyrrolidone, ethyl cellulose, hydroxypropyl methyl cellulose, polyvinyl alcohol, polyacrylic acid, sodium carboxymethyl cellulose, sodium alginate, xanthan gum, chitosan, carrageenan, hydroxypropyl cellulose, and carboxymethyl cellulose could be considered. In recent years, stimuli-responsive micro and nanogels have been designed, which respond to external stimuli such as pH, ionic strength, temperature, and electric current in order to deliver a specific drug dosage in a specific site (Prabaharan ). George et al. (George and Abraham ) have designed a pH sensitive system made of alginate-guar gum hydrogel cross-linked with glutaraldehyde for controlled delivery of proteins. These authors found that the presence of this modified guar gum increases the entrapment efficiency and prevents the rapid dissolution of alginate in a basic pH as the pH found in the intestine, ensuring a controlled release of the entrapped drug. Furthermore, guar gum has been used to develop sustainedrelease devices of water soluble antihypertensive drugs such as nifedipine, diltiazem hydrochloride, and other such as ketoprofen. Recent studies carried out by Das et al. (Das and Subuddhi ) have shown very encouraging results using pH-responsive hydrogel systems based on guar gum, poly(acrylic acid), and cross-linked cyclodextrin with tetraethyl orthosilicate for intestinal delivery of dexamethasone. They found that as the guar gum content increases, the rate of drug release decreases considerably and the drug release is prolonged. On the other hand, considering that guar gum and its derivatives have good film forming
scrivener 1.9.13 crack Activators Patch controlled drug release abilities, they have the potential to be used as transdermal drug delivery devices (Altaf et al. ). The physiological effects of guar gum have been extensively studied, first on animals and then on humans. Studies revealed that guar gum is non-toxic; additionally, it does not have carcinogenic or teratogenic effects (Melnick et al. ). In addition, due to its high biocompatibility and biodegradability it is extensively used as a biomaterial. Guar gum cannot be degraded in the small intestine; however, in the large intestine, the glycosidic linkage present in guar gum is degraded due to the microbial
Biopolymers used in Drug Delivery Systems 45
enzyme present there (Tomlin et al. ). One of the bacteria responsible for guar gum degradation is Clostridium butyricum (Mudgil et al. ).
Carrageenan Carrageenans are a family of high molecular weight sulfated polysaccharides obtained by extraction from some members of the algae class Rhodophyceae (red seaweed). They are composed of galactose and anhydrogalactose units, linked by glycosidic unions. Depending on the method and the algae from which carrageenan is extracted, three main types of carrageenans can be obtained: kappa (κ), iota (ι), and lambda (λ) (Sankalia et al. ). The primary differences which influence the properties of carrageenan type are the number and position of sulfate ester groups as well as the content of 3,6-anhydrogalactose. Typically, commercial λ-carrageenan contains approximately 35% sulfate ester by weight and little or no 3,6-anhydrogalactose,
scrivener 1.9.13 crack Activators Patch, ι-carrageenan contains about 32% sulfate ester by weight and approximately 30% 3,6-anhydrogalactose, and κ-carrageenan contains 25% sulfate ester by weight and approximately 34% 3,6-anhydrogalactose (Jana et al. ). Even though these three types of carrageenans have similar characteristics in their chemical
scrivener 1.9.13 crack Activators Patch, it was reported that higher levels of sulfate ester resulted in lower solubility temperature and lower gel strength (Necas and Bartosikova ). Moreover, given the ionic nature of the polymer, its gelation is strongly influenced by the presence of electrolytes and, among these three types, only κ- and ι-carrageenans evidence gel-forming ability; the κ-carrageenan gels are firmer than those obtained with ι-carrageenan, which are more elastic and soft (Bixler ). Carrageenan is widely used in the food industry due to its excellent gelling, thickening, emulsifying, and stabilizing abilities. Furthermore, it is also applied in other commercial products such as cosmetics, air freshener gels, and
scrivener 1.9.13 crack Activators Patch fighting foam (Necas and Bartosikova ), and recently, it is increasingly being used in pharmaceutical formulations as well (Li et al. ). Mechanical and rheological properties of carrageenan gels have been widely studied in the presence of ions. Carrageenans exist as a random coil at high temperature; and temperature reduction induces the formation of double helices. This leads to the formation of small independent domains involving a limited number of chains via intermolecular association. However, when cations are incorporated into carrageenan suspensions, helices of different domains aggregate to enable long range cross-linking which forms a cohesive network and this quaternary structure contributes to the final properties of the resultant gels (Morris et al. ). However, Thrimawithana et al. have demonstrated that increasing ion concentrations beyond a threshold also had a negative impact on some mechanical properties of carrageenan gels (Thrimawithana et al. ). Different carrageenan drug delivery systems have been developed, and they are mainly used as a polymer matrix in oral extended-release tablets (Hariharan et al. ), as a novel extrusion aid for the production of pellets (Thommes and Kleinebudde), and as a carrier in micro and nanoparticles systems (Cheng et al. ). In addition, based on their strong negative charge, carrageenans have been
scrivener 1.9.13 crack Activators Patch as gelling and viscosity enhancing agents for the design of drug controlled-release systems which could be used, for example, as prolonged retention systems. It can be
scrivener 1.9.13 crack Activators Patch combined
46 Biopolymers for Medical Applications with locust bean gum and gellan gum, in chitosan/carrageenan nanoparticles, agarose/ carrageenan hydrogels, and carrageenan/gelatin mucoadhesive systems, among others (Jana et al. ). In particular, κ-carrageenan is widely used due to their hydrogen bond-forming capability in several sites which impart bioadhesive properties to the final formulation. Moreover, its mucoadhesive property could be further enhanced by the negative charge of the sulfate group in the carrageenan structure; as a consequence, ionic bonds are formed with the positively charged mucin present on the buccal mucosa (Kianfar et al. ). Carrageenans have shown several potential pharmaceutical properties including anticoagulant, anticancer,
scrivener 1.9.13 crack Activators Patch, antihyperlipidemic, and immunomodulatory activities (Wijesekara et al. ; Campo et al. ). Comparison of a variety of compounds reveals that carrageenan is an extremely potent infection inhibitor for a broad range of sexually transmitted human papillomavirus (Buck et al. ); in fact, it was reported that carrageenans-based gels used in sexual lubricant may offer protection against human papillomavirus transmission (Campo et al. ; Roberts et al. ),
scrivener 1.9.13 crack Activators Patch. Additionally, Rocha de Souza et al. (Rocha de Souza et al. ) found a positive correlation between sulfate content and antioxidant activity of carrageenan. In contrast, it is known that carrageenans induce inflammatory responses in laboratory animals (Tobacman ; van der Kam et al. ; Sadeghi et al. ); and
scrivener 1.9.13 crack Activators Patch studies showed that long-term administration of carrageenans in animal models caused ulcerative colitis or intestine mucous membrane damage. It was also reported that these compounds promote tumor growth (Tobacman ). Finally, specialists concluded that it is necessary to perform more epidemiological and essential studies to evaluate the safety of carrageenan (Li et al. ).
Hyaluronan Hyaluronan (HA), also known as hyaluronic acid or hyaluronate, is a negatively charged, linear and unbranched polysaccharide with a simple chemical structure consisting of alternating units of D-glucuronic acid and N-acetyl-D-glucosamine. It is considered the largest glycosaminoglycan, with a molecular weight ranged from to kDa (Rowe et al. ). HA was first isolated from bovine vitreous humor in by Meyer and Palmer (Meyer and Palmer ). It is currently extracted from animal waste (e.g., rooster comb) and it has been obtained by different biotechnological methods such as microbial (Widner et al. ) and enzymatic production (Kooy et al. ). HA has been widely studied because of its unique properties, such as aqueous solubility, and its viscoelastic properties that allow it to form highly viscous solutions and three dimensional structures. It has been reported that HA plays an important role in the structure and viscoelastic properties of different tissues such as skin and articular cartilage (Nair and Laurencin ). Regarding its mechanical properties, a single HA molecule is very flexible and its viscoelasticity is affected by the pH and ionic strength of its environment (Kobayashi et al. ). Furthermore, HA has a pKa value of about and therefore, a change in pH will affect the extent of ionization of the HA chains (Mi et al. ). To improve its mechanical properties HA can be chemically modified or cross-linked. Generally carboxylic acid and alcohol groups have been modified by esterification and by
easeus data recovery wizard keygen machine code Biopolymers used in Drug Delivery Systems 47
linkers such as dihydrazide, dialdehyde, divinylsulfone, diglycidyl ethers, or disulfide (Jeon et al. ). Several investigations have shown that parameters such as elastic modulus, shear modulus, viscosity, and viscoelasticity depend on HA concentration and cross-linked degree of hydrogels (Balazs and Denlinger ; Altman and Moskowitz ; Nijenhuis et al. ). Mainly, it is possible to increase the hydrogel’s storage modulus by increasing the gel precursor solution’s HA concentration, with stiffness ranging from Pa to Pa (Lam et al. ). Although, a research have shown that the elastic modulus rises while HA concentration keeps below 20%, however above this value the elastic modulus decreases due to a significant growth of swelling of the hydrogel (Jeon et al. ). HA has a great potential to be used as a specific-target carrier and long-acting delivery systems of various molecules including proteins, peptides, and nucleotides. In encapsulation of proteins, HA provides a well-hydrated environment, helping them to retain their biological activity and to limit denaturation (Hoffman ). Recently, HA has been investigated as a drug delivery agent for various routes of administration, including dermal, ophthalmic, nasal, pulmonary, parenteral, and topical. Regarding dermal applications, Solaraze®, a HA gel with a commercial drug (diclofenac), was developed for the topical treatment of actinic keratosis. In this formulation, HA enhances significantly the partitioning of diclofenac into human skin and its retention and localization in the epidermis (Del Rosso ). Due to its mucoadhesive capacity, microspheres delivery systems made of HA have been used as a vehicle for topical ophthalmic drugs (Lim et al. ). Microspheres have also been used experimentally as delivery devices for nerve growth factors (Mohammad et al. ), and as a nasal delivery system for insulin (Illum et al. ). Moreover, paclitaxel and doxorubicin, both anticancer drugs, have been chemically linked to HA systems and it was found to selectively target human cancer cells because HA is the main ligand for CD44 and RHAMM receptors, which are over-expressed in a variety of tumor cell surfaces (Culty et al. ) including colon cancer (Tanabe et al. ), human breast epithelial cells (Bourguignon et al. ), lung cancer (Matsubara et al. ), and acute leukemia cells (Yokota et al. ). HA biocompatibility, non-toxic properties and lack of immunogenicity, make it an ideal scaffold for tissue engineering. In terms of biodegradation in human tissues, HA has a half-life from less than 1 to several days. Once it reaches the blood stream, about 85–95% is eliminated by the liver; while kidneys extract 10% but excrete about 1–2% in urine (Fraser et al. ). On the other hand, it was shown that HA is related to different kinds of diseases. Elevated proportions of HA, HA synthase, and hyaluronidase are involved in cell migration and metastasis at various stages of cancer progression (Lokeshwar et al. ). Moreover, HA oligomers formed by hyaluronidase degradation are pro-angiogenic (Liu et al. ) and have inflammatory
scrivener 1.9.13 crack Activators Patch immuno-stimulatory properties (Xu et al. ).
Alginates Alginates are mainly obtained from cell walls of different species of brown algae belonging to Phaeophyceae class. Since that these algae are harvested from nature, there is a variety of types of alginates depending on the selected species, the time of
48 Biopolymers for Medical Applications collection and the region where each species is found. In this context, alginate allows significant variation of material properties solely based on polysaccharide composition (Grasdalen et al. ) and these properties allow tailoring of a variety of biomaterials suitable for tissue engineering. Alginates are water soluble and anionic linear hetero-polysaccharide composed of two different monomers (1→4)-β-linked: the β-D-mannuronic acid (M) (pKa = ) and the α-L-guluronic acid (G) (pKa = ). Therefore, if the pH of the alginatecontaining solution is lowered below the pKa of the constituting acids, phase separation or hydrogel formation occurs. Generally, they are composed of three different forms of polymer segments: consecutive G residues, consecutive M residues, and alternating MG residues. The resulting variability of alginate composition significantly affects its physical properties, for example: G rich domains with more than 6–10 residues bind divalent ions (Ca2+, Ba2+, etc.) forming cross-links between different chains in a so-called ‘egg-box arrangement’ (Grant et al. ). These polysaccharides are insoluble in aqueous-alcoholic solutions and also in organic solvents. Their use has been widely diffused in different industries such as pharmaceutical ones. Here, they are part of tablets and ophthalmic preparations, among others; however, nowadays the most important field of interest is the production of hydrogels. Alginates can be found forming salts with different cations: ammonium, potassium, sodium, and propylene glycol. Typically, alginate salts are prepared at 1% w/v in aqueous solution, and at 20°C they have a viscosity of 20– mPa x s. The viscosity of these gels may vary depending upon concentration, pH, temperature, or the presence of metal ions, for instance, above pH 10, their viscosity decreases (Rowe et
scrivener 1.9.13 crack Activators Patch. ). The design of drug delivery systems based on alginates can be performed due to the sol-gel transition behavior of the alginate in the presence of divalent cations such as Ca2+, Sr2+, and Ba2+. After this reaction, the water solubility of the monovalent alginate decreases converting it into a water insoluble salt. Furthermore, GG blocks have shown to be more rigid than MM blocks because of axial–axial or diequatorial linkage (Rinaudo ). Therefore, gels formed from alginate with a high M content are typically softer and less porous than high G alginate gels, showing a higher degree of swelling and shrinking. Consequently, a high G alginate is advantageous in terms of maintenance of form and integrity over extended time (Simpson et al. ; De Vos et al. ). In drug delivery systems’ design, alginates are used as a stabilizing agent, suspending agent, tablet and capsule disintegrant, tablet binder, and viscosity increasing agent (Rowe et al. ). Moreover, different systems with applications in regenerative medicine, such as microspheres, microcapsules, sponges, foams, and fibers, have been developed. Alginates may be used to develop delivery systems for cationic polyelectrolytes and proteoglycans through simple electrostatic interactions
DAZ Studio Pro Keygen to its pH dependent anionic nature (Yu et al. ). Recently several different formulations were developed where this polymer was included; however, only two of them will be highlighted in this section: the development
scrivener 1.9.13 crack Activators Patch nanoparticles and the production of hydrogels. The most important feature of these hydrogels is their adhesion to different tissues. The adhesive devices can be formulated for drug release into different mucosal tissues such as oral and vaginal ones, and can be developed as in situ-formed gels to be applied in buccal and ophthalmic mucosa to controllably
Biopolymers used in Drug Delivery Systems 49
release the API. The esophageal bio-adhesion of alginate suspensions may provide a barrier against gastric reflux or site-specific delivery of therapeutic agents (Richardson et al. ). Furthermore, nasal delivery systems based on mucoadhesive microspheres (Gavini et al. ), and a freeze-dried device intended for the delivery of bone-growth factors have been reported. One of the most important applications of the alginates is the development of hydrogel systems for delivery of sensitive drugs such as proteins and peptides (Gombotz and Pettit ). In these groups of drugs are included several proteins such as immunoglobulin, fibrinogen, insulin, melatonin, heparin, and hemoglobin. Related to peptides delivery, this polymer was blended with another natural polysaccharide, guar gum (George and Abraham ), to overcome the rapid dissolution of the alginate at high pH, a major limitation during delivery of peptide drugs (Yu et al. ; Li et al. ). In addition, sodium alginate microspheres have been used in the preparation of a DNA vaccine for the foot-mouth disease (Liu et al. ), and therefore, the incorporation of functional small interfering siRNAs proves the significance of this polyanionic polysaccharide. Moreover, the use of alginatebased delivery systems for distribution of cell induction ligands and also for bioactive molecules for signaling was reported (Kulkarni et al. ). Alginates are generally regarded as non-toxic and non-irritant materials. However, biocompatibilities of alginates were significantly affected by their composition and their molecular weight. In this context, it was suggested that unbound alginate oligosaccharides may be responsible for the induction of inflammatory reactions, and the purification of the alginate reduces the low molecular weight fraction which may lead to improved biocompatibility. In this context, their biodegradability strongly depends on the characteristics of each polymer and hence, the biodegradability of high molecular weight alginates is hampered when they are parenterally administered as they may exceed the threshold of renal clearance. Due to that fact, to improve the biodegradability of alginates, low molecular weight polymers are cross-linked with biodegradable molecules to obtain high molecular weight alginates with enhanced renal clearance. Nevertheless, this strategy has a disadvantage related with the high purification process required to use these assembled polymers (Germershaus et al. ).
Proteins Essentially, proteins are a polymeric arrangement of amino acids in a three-dimensional folded structure forming the major structural components of many human tissues; they also are one of the most important classes of identified biomolecules. There are at least two fundamental factors in the characterization of proteins. The first one is related to their morphology, which affects their solubility and the other is related to their biological function, that is, if a protein is a structural protein or a transport protein. Morphologically, proteins are divided into fibrous and globular proteins. The main difference between these two kinds of proteins is that fibrous proteins generally have only primary and secondary structures; whereas globular proteins have also tertiary and sometimes quaternary structures. In contrast to globular proteins,
scrivener 1.9.13 crack Activators Patch, fibrous proteins provide mechanical and structural support in the body whereas globular proteins are related to transport function (Nelson et al. ). Fibrous proteins form
50 Biopolymers for Medical Applications the extra cellular matrix and/or basal lamina of the cells in different tissues such as ligament, bone, and skin. As mentioned above, proteins are the major component of natural tissues; therefore, this is one of the reasons why proteins and other amino acid-derived polymers have been a preferred biomaterial for medical uses such as haemostatic agents, scaffolds for tissue engineering, and drug delivery vehicles (Meinel et al. ). The use of biodegradable hydrogels based on proteins as drug delivery systems has a particular interest due to their biocompatibility and their relative inertness. For this reason, in this section we will show examples related to proteins forming hydrogels. Finally, it is important to remark that protein-based biomaterials are known to undergo naturally-controlled degradation processes.
Collagen I Collagen is the main structural protein in vertebrates, and it represents approximately 30% of all body proteins. Collagen’s family is characterized by a unique triple-helix configuration of three polypeptide subunits known as a α-chain. Due to differences in the helix’s lengths and in the nature of the non-helical portions have been separated, at least, 13 types of collagens. The basic collagen molecule is formed by more than amino acids which develop a unique triple-helix sequence, which in turn is composed by α-chains. A right-handed helix is formed by 3 α-chains (Friess ) and it is stabilized by hydrogen bonds, intra-molecular van de Waals interactions (Brinckmann et al. ), and some covalent bonds (Harkness ). The helix has an average molecular weight of kDa, a length of nm, and a diameter of nm (Friess ). Moreover the helices are associated into right handed microfibrils (40 nm in diameter) which are assembled into fibrils (– nm in diameter). Finally, a group of fibrils form collagen fibers (He, Mu et al. ). In
scrivener 1.9.13 crack Activators Patch, a distinctive collagen marker is the presence of 4-hydroxyproline in the triple-helix (Cen et al. ). The unique physiological characteristics of collagen and its capability to develop biomaterials derive from the structural complexity of the collagen molecule (Friess ). Reconstituted collagen fibrils have mechanical properties sensitive to their hydration state (van der Rijt et al. ) and are able to be manipulated by controlling their aqueous environment (Grant et al. ). Although it has been reported that a tendon’s collagen fibrils form a rope-like structure, mechanical properties at a sub-fibrillar level are not fully understood (Bozec et al. ),
scrivener 1.9.13 crack Activators Patch. The self-assembly mechanism generates a homogeneous single fibril of collagen (Yang et al. ). However, the alignment of collagen molecules along the longitudinal fibril direction could cause a mechanical anisotropy. Tensile test has been performed on single collagen type I fibrils. For example, a Young’s modulus value of 5 ± 2 GPa was found for dry fibrils of type I collagen and when these fibrils were immersed in phosphate-buffered saline, its elasticity decreased to to GPa. These results support the hypothesis that the anisotropy of collagen arises from the alignment of sub fibrils along the fibril axis (Yang et al. ). Atomic Force Microscopy has been used to infer the elasticity of these structures and thus, the modulus of several collagen fibrils in air and aqueous fluid were compared. Therefore, this study (Atomic force microscopy) was carried out to describe the effect of hydration on the mechanical response (Grant et al. ).
Biopolymers used in Drug Delivery Systems 51
This behavior is due to that the cross-linking process increases the stiffness of the material and also sterilization with glutaraldehyde. On the other hand, thermal sterilization can decrease its stiffness (Lesiak-Cyganowska et al. ; Angele et al. ; Friess ). Different kinds of collagen such as powders, liquids, solid compressed masses, membranes, or sponges have been reported. The obtained behavior, which is result of a study of different drug delivery systems, must be in concordance or should explain the properties of these systems (Ruszczak and Friess ). Nowadays, different efforts to attach drugs or polymers structures to collagen have been described in literature. Controlling drug conjugates would allow the immobilization of therapeutic enzymes or drug delivery; in this regard, kanamycin and pilocarpine have been investigated as conjugate options (Friess ). Sheets, tubes, sponges, powders, fleeces, injectable solutions and dispersions are some
scrivener 1.9.13 crack Activators Patch the forms in which collagen can be processed (Chvapil et al. ; Byrom ; Fu Lu and Thies ). Inserts and shields are among the most studied drug carrier applications of collagen. They are used for drug delivery above the corneal surface or for forming the cornea itself (Friess ). Inserts are cut from films or fabricated as molded rods prepared out of mixtures of drug and collagen by air-drying (Rubin et al. ). There are different kinds of injectable systems carried out as gels. One of them is initially liquid, which when is injected inside the eye, coagulate in it, turning into a gel. These gels are able to remain longer than liquid formulations and could achieve a sustained delivery of non-steroidal anti-inflammatory drugs or antibiotics (Friess ). A formulation of collagen with epinephrine for local vasoconstriction was tested aiming to enhance local drug retention, minimization of systemic side effects, and reduction of the required dose (Friess ). In order to deal with a key complication in surgery, which is the local treatment of soft tissue infections, combinations with antibiotics are being developed (Taylor ). Collagen products are appropriate for medical uses because of their low antigenicity, excellent biocompatibility, low immunoreactions, clear association with other biological species and polyelectrolyte behaviour,
scrivener 1.9.13 crack Activators Patch. In addition,
scrivener 1.9.13 crack Activators Patch, final products such as threads, sponges, films, and drug delivery systems are important considering the reconstitution of collagen into native fibres starting from collagen solutions (Chirita ). Since there are similarities between amino acids of collagen of different animal species and the low content of aromatic residues, generally, collagen fibres behave as a non-antigenic protein. However, there are massive concerns about massive immune responses or autoimmune diseases triggered by antibodies which may produce cross-reactions by collagen derived from animal tissues (Friess ). Despite their ability to interact with antibodies, collagens are weakly immunogenic in comparison to other proteins (Byrom ). Antigenic determinants of collagen can be classified into three following categories: 1) tridimensional conformation recognition by antibodies; 2) recognition of amino acid sequence located within the triple helical portion (Lynn et al. ); 3) recognition of terminal and non-helical regions (Lee et al. ; Chevallay and Herbage ; Hsu et al. ; Kikuchi et al. ). During the in vivo process, collagen is infiltrated by inflammatory cells such as fibroblasts, macrophages, or neutrophils, which secrete enzymes, activators, inhibitors, and regulatory molecules (Byrom ). Water, enzymes, and the digestion of linkages
52 Biopolymers for Medical Applications are required for collagen degradation. After a process of swelling by exposure to water, collagen is only completely digested by specific collagenases and cleaving enzymes (Harrington ). Collagen is degraded by endopeptidases and some non-enzymatic degradation mechanisms like hydrolysis (Okada et al. ). The connective tissue is digested by proteases, whereas metalloproteinases (MMPs) carry out the extracellular matrix degradation. Cysteine and aspartic proteases (cathepsins) degraded connective tissue intracellularly, while serine and MMP matrix degrade it extracellularly (Shingleton et al. ).
Gelatin Gelatines are proteins derived from collagen, soluble in warm water, and with molecular weights ranging from ~ 20 to kDa; and like in collagen, glycine (~ 24%), proline (~ 17%), alanine (~ 14%), and hydroxyproline (~ 10%) are the four most abundant amino acids. The essential amino acid, tryptophan, is not found in gelatin. The helical conformation can reach 70% and may be found in the gel form of gelatin. These regions have many inter and intramolecular associations and the α-chain of gelatin, which has a highly ordered sequence of amino acids, behaves like a randomcoil polymer in the solution. The gel structure is a combination of fine and coarse interchain networks, and the ratio is defined as a proportional relation between fine chains and coarse depends on the gel formation temperature. In addition, the rigidity of the gel is approximately proportional to the square of the gelatin concentration (Gurr and Mülhaupt ). The gelatines are known as type A and type B depending on the production process; thus, if it is treated with acid, it is called type A, and if it is alkali treated, it is type B. These treatments cause de-amidation of asparagine and glutamine resulting in an increase in the number of acids, aspartic and glutamic (Eysturskarð et al. ). Physical-chemical and rheological properties depend on their amino acid content. Rheological properties are important considerations in process design, evaluation, as well as in modelling. Hence, these are properties that indicate the quality of the product. Dynamic viscoelastic properties and flow properties provide information about their molecular arrangements. Hence, it is important to assess the rheological properties of gelatin along with its physical-chemical properties (Chandra and Shamasundar ). Mechanical properties such as the dynamic storage modulus and bloom value for gelatines are dependent on the average molecular weight and its distribution, whereas the content of the amino acids affects their physical properties. Low molecular weight fractions of gelatin block the helix assembly, perturbing the formation of the network. Both proline and hydroxyproline have stabilizing effects on the helices due to their ring conformation, and they also influence the flexibility of the chains. Consequently, the lower content of these amino acids increases the flexibility and, as a result, facilitates the reorganization of the network (Eysturskarð et al. ). Gelatin may be loaded with charged biomolecules due to its intrinsic features, and it can be used as a drug delivery carrier. The drug loading efficiency depends on the treatment that collagen received to produce the gelatin, that is, alkaline or acidic, and also the nature of the guest drug. The cross-linking and the gelatin molecular weight can be tuned to control the release kinetics of gelatin. This polymer gives
Biopolymers used in Drug Delivery Systems 53
the possibility to control both aspects, that is, drug loading and release kinetics
ccleaner apk et al. ). Oral administration is the main use for gelatin capsules. Solid, semisolid, and liquid fillings can be carried in hard capsules, whereas soft capsules are mainly for semisolids or liquids. Active ingredients can be incorporated differently depending on the capsule: as a filling in the hard ones; whereas the soft ones are able to carry the drug within their soft shell as well as in the filling. In addition, they can release the content rapidly thanks to a fast swelling and dissolving. Gelatines can contain coloring and antimicrobial agents, and they can also be used for the microencapsulation of drugs where the API is sealed inside a microsized capsule or beadlet. Other examples of gelatin uses are ibuprofen-gelatin micropellets, pastes,
scrivener 1.9.13 crack Activators Patch, pastilles, pessaries, and suppositories. It is also used as tablet binder, coating agent, and viscosity increasing agent (Rowe et al. ). In more specific examples, studies of releasing lysozyme from hydrogels are being conducted in order to deliver antibacterial proteins into prosthesis of heart valves to prevent valve endocarditis. There has been a recent development in long-circulating gelatine controlled release systems which improve the applications in chemotherapy because they can gradually be accumulated at the tumor site thanks to the leaky vasculature and lack of lymph vessels around tumors (Young et al. ). Releasing tetracycline and bisphosphonate from Gelfoam® pellets to reduce periodontal bone loss and controlled-release vehicles for chemo-therapeutic agents are other examples of current researches (Yaffe et al. ). As a collagen derivative, gelatin is a non-toxic, biodegradable, inexpensive, non-immunogenic material; therefore, it has a high potential to be used in a variety of medicinal agents. In addition, its water solubility and lesser cost are advantageous over its precursor (Varghese et al. ). As it was mentioned before, gelatin is highly biocompatible and biodegradable in a physiological environment. The digestive process confers to gelatin a very low antigenicity, with the formation of harmless metabolic products upon degradation. The presence of amino acidic sequences such as Arg-Gly-Asp (RGD) in the structure, improves the final biological performance of gelatin over synthetic polymers that lack these cell-recognition motifs (Santoro et al. ).
Human Serum Albumin Human Serum Albumin (HSA) is the main protein of the blood plasma, accounting for over 50% of its total protein content, and its concentration range is from to 5 g/dl. HSA is a small globular protein with a molecular weight of kDa comprised of a single polypeptide chain of amino acids; it is also the only major plasma protein that does not contain carbohydrate constituents (Rowe et al. ). Regarding its biological properties, albumin is responsible for 75–80% of the colloid osmotic pressure of plasma (Scatchard et al. ); it is also involved in transport and metabolism of several endogenous and exogenous compounds, such as hormones, bile acids,
scrivener 1.9.13 crack Activators Patch, amino acids, fatty acids, toxic metabolites, metals, and drugs (Kratz ). The protein contains a single thiol group from a cysteine residue at position 34 (Cys34) that acts both as a binding site for many biologically active molecules and also providing antioxidant activity, and constituting the largest fraction of free thiol groups in the blood (Stewart
54 Biopolymers for Medical Applications et al. ). Due to the presence of undissociated acid content within the polypeptide, HSA participates in the regulation of acid-base balance (Bruegger et al. ). Albumin and other small macromolecules accumulate in the tumor area due to extensive angiogenesis, increased permeability, and lack of lymphatic drainage in a phenomenon that is universal in solid tumors and it is called
scrivener 1.9.13 crack Activators Patch permeability and retention (EPR) effect (Maeda et al,
scrivener 1.9.13 crack Activators Patch. ), providing an attractive strategy for passive targeting of drugs into the tumoral tissue. Furthermore, albumin-binding proteins such as membrane associated gp60 and osteonectin (SPARC), which promote the accumulation of albumin within the tumor interstitium, can also be used in the targeting of tumors by the simple formation of the drug-albumin conjugation (Kratz ). Since Albumin is a naturally-occurring protein found in the body, it is not surprising that the protein is cataloged as a non-toxic material (Rowe et al,
scrivener 1.9.13 crack Activators Patch. ). HSA has an average half-life of 19 days, which provides an attractive approach for improving the pharmacokinetic profiles of peptides and cytokines. Therefore, biodegradability has to be considered for each particular albumin-based drug delivery system because it has proven its strong dependence on the degree
scrivener 1.9.13 crack Activators Patch cross-linking (Langer et al. ), pH, and temperature of preparation (Rohanizadeh and Kokabi ). Nowadays, albumin is used as a versatile protein carrier for drug targeting and for improving the pharmacokinetic profile of peptide or protein-based drugs. There are mainly three drug delivery technologies: coupling of low-molecular weight drugs to exogenous or endogenous albumin, conjugation with bioactive proteins, and encapsulation of drugs into albumin particulate systems such as nanoparticles or micelar structures. Several examples of these systems are presented below. The first drug-albumin conjugates were obtained by direct binding peptides or prodrugs to the Cys34 position of exogenous and endogenous albumin. Commercially available albumin can be successfully conjugated with doxorubicin maleimide derivatives (an antibiotic with antineoplastic activity), as reported by Drevs et al. (), to obtain the A-DOXO-HYD conjugate, which has proved to have a superior effect against murine renal carcinoma compared to free doxorubicin at the equitoxic dose. Endogenous albumin can also be used as a drug carrier as in the case of AldoxorubicinTM (CytRx Corporation, Los Angeles, CA, USA), a prodrug of doxorubicin that, following intravenous administration, is able to bind rapidly and selectively to the Cys34 position of albumin,
scrivener 1.9.13 crack Activators Patch, leading to passive accumulation within the tumor; currently this prodrug is being tested in phase 3 clinical trials in patients with soft tissue sarcomas whose tumors have progressed after treatment with chemotherapy. Bioactive peptides, such as Insulin were successfully conjugated with albumin in the so called PC-DAC™:Insulin by ConjuChem, Inc. (Los Angeles, CA, USA), demonstrating more efficiency than insulin Glargine in diabetic rats and a prolonged duration of activity in preclinical pharmacodynamics studies. Albinterferon-α2bTM, a fusion protein of recombinant HSA and interferon α-2b, was developed
scrivener 1.9.13 crack Activators Patch a long-acting interferon for the treatment of chronic hepatitis C by Human Genome Sciences in collaboration with Novartis,
scrivener 1.9.13 crack Activators Patch. In this system, albumin was used to increase circulation half-life of interferon-α leading to a significant reduction of the dosing interval, granting a successful phase 3 clinical trial approval; however, Food and Drug Administration’s concerns regarding reduced performance led to the cancellation of
Biopolymers used in Drug Delivery Systems 55
the program in Albumin can also be used for encapsulating lipophilic drugs into nanoparticles using a quite elegant technology (nab or NP albumin bound) in which the drug is mixed with aqueous HSA and passed under high pressure through a jet to yield nanoparticles with sizes of – nm. An example of this is the commercially available nab-paclitaxel, also known as AbraxaneTM, a variation of paclitaxel in which the taxane is bond to albumin forming nanoparticles of an approximate diameter of nm, that was approved in for the treatment of metastatic breast cancer. The enhanced uptake of these albumin-based drug delivery systems in solid tumors can be ascribed to the EPR effect as well as to transcytosis initiated by binding of albumin with gp and SPARC (Desai et al. ).
Miscellaneous Polyethylene glycols Polyethylene glycol polymers (PEGs) are polyalcohols that have been described as an addition of polymers of ethylene oxide and water. These polymers are commonly named macrogols followed by a number indicating their molecular weight, which varies depending on the polymerization degree. Hence, polyethylene glycol grades from to (or macrogols to ) are liquids and grades up to are solids at 25°C. The empirical formula can be written as: HOCH2(CH2OCH2)mCH2OH where m represents the average number of oxyethylene groups that ranges from toand their molecular weights ranges are from to However, there are grades of PEGs near to The number can be used to indicate the approximate molecular weight of a macrogol. All grades of polyethylene glycol
scrivener 1.9.13 crack Activators Patch soluble in water and miscible in all proportions with other polyethylene glycols. Aqueous solutions of high molecular weight glycols (or high grades), may form gels with different viscosity (Rowe et al,
scrivener 1.9.13 crack Activators Patch. ). PEGs are widely used in the manufacture of surfactants, pharmaceuticals, cosmetics, polyurethanes, as well as in a variety of different fields. Regarding pharmaceutical formulations they are used as excipient, being included in parenteral, topical, ophthalmic, oral, rectal preparations; and also have been used experimentally in biodegradable polymeric matrices and in controlled-release systems. Functionally, the pharmaceutical industry uses these compounds as an ointment base, plasticizer, solvent, suppository base, tablet, and capsule lubricant. PEGs are stable and aqueous polyethylene glycol solutions can be used either as suspending agents or to adjust the viscosity and consistency of other suspending vehicles. These compounds can also be used as a co-solvent in order to enhance the aqueous solubility or dissolution characteristics of poorly soluble compounds by making solid dispersions with an appropriate polyethylene glycol. In this context, PEGs enhance the stability of aspartame solutions (Yalwsky et al. ); they can be used in diazepam solutions for parenteral administration (Shah et al. ) and can also improve bentonite dispersions. First Ambrosi et al. () and later Benedini et al. () have used PEG to modify the transition temperature of coagels of ascorbylpalmitate and shift the existence limits of liquid crystals of ascorbylpalmitate.
56 Biopolymers for Medical Applications PEGs are essentially non-irritant to the skin and biocompatible, however they are not easily degradable polymers. PEGs with molecular weight lower than can be degraded by many bacteria species whereas those with higher molecular weights are significantly more resistant (Marchal et al. ). The oxidation of the terminal hydroxyl group and sequential shortening by a single oxyethylene unit is considered, by many authors, as a predominant pathway (Zgoła-Grześkowiak et al. ).
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