Hydrogels are presently under investigation as a delivery system for bioactive molecules, because of their similar physical properties as that of
Crosslinking Of Polysaccharides: Methods And Applications
Polysaccharides are polymers of simple sugar building blocks. Crosslinked polysaccharides are having many applications in pharmaceuticals.
Different methods are available for crosslinking of polysaccharides. Different chemical and physical methods are summarized and discussed. Chemical crosslinking of polysaccharide is highly versatile method with good mechanical stability. However, the crosslinking agents used are not only affects the integrity of substances but are often toxic compounds, which have been extracted from gel before they can be applied. Such adverse effects are avoided with the use of physically crosslinked gels.
Polysaccharides are polymers of simple sugar building blocks. Polysaccharides functions as thickeners, stabilizers, suspending agents, gelling agents, film formers, aerating agents, flocculants, binders, emulsifiers, lubricants, texturing agents and structuring agents1,2. Polysaccharides are primarily used to thicken or gel water and are frequently classified into two groups thickeners and gelling agents3. Gelling agents are more difficult to use than thickeners and their use is complicated by the fact each requires its own set of procedure to produce satisfactory gel4. Thus polysaccharides are hydrated in an aqueous environment thereby creating the gel structure called hydrogel. Aqueous solutions of hydrophilic polymers at low or moderate concentrations, where no substantial entanglement of chains occurs, normally show Newtonian behavior. On the other hand, once crosslinking between different polymer chains are introduced, the so obtained network shows visco-elastic and sometimes pure elastic behavior. As the term implies, crosslinks have to be present to avoid dissolution of hydrophilic polymer chains into aqueous phase5-13. A great variety of methods for crosslinking has indeed been used. Since it is advantageous for many applications that the hydrogels are biodegradable, labile bonds are frequently introduced in the gel. These bonds can be present either in polymer backbone or in the crosslinks used to prepare gel. The labile bonds can be broken under physiological conditions either enzymatically or chemically; in most of cases by hydrolysis13. Crosslinked polysaccharides were used for coating and/or embedding medicinal active substances or drug compositions. The invention furthermore relates to a drug which contains an active substance which acts in the large intestine or an active substance which is broken down on passing through the stomach or small intestine could be coated with or embedded in one of the crosslinked polysaccharides14. In this review methods of crosslinking of polysaccharides are described and discussed. Chemical and physical methods are used for crosslinking of polysaccharides. In physical crosslinking dissolution is prevented by physical interaction which exists between different polymer chains. In chemical crosslinking covalent bonds are present between different polymer chains.
In recent years there has been increase in interest in physical crosslinking. The main reason is that use of crosslinking agents is avoided. These agents cannot only affect the integrity of substances to be entrapped e.g. proteins, cells, but these agents are often toxic compounds which have to be removed or extracted from the gel before they can be applied. In physical crosslinking, polysaccharides forms crosslinked network with counterion at the surface. High counterion concentration would require longer exposure times to achieve complete crosslinking of the polysaccharides. For physical crosslinking different methods have been investigated.
Crosslinking by ionic interaction: Alginate is a well-known example of polysaccharide that can be crosslinked by ionic interactions. Alginate is a polysaccharide with mannuronic and glucuronic acid residues can be crosslinked by calcium ions15. Crosslinking can be carried out at room temperature and physiological pH. Therefore alginates gels can be frequently used as matrix for the encapsulation of living cells16 and for the release of proteins17. The release of proteins from the alginate microparticles obtained by spraying a solution of sodium alginate into an aqueous solution of calcium chloride can be modulated by coating the particles with cationic polysaccharide for example chitosan18,19. Polycations can be crosslinked by anions. Chitosan is an amino-polysaccharide obtained by alkali induced deacetylation of chitin. Chitosan based hydrogels were obtained by croslinking with glycerol-phosphate disodium salt20. Interestingly, in presence of this salt, chitosan solution remains liquid below room temperature, but quickly gel when heated. Biological materials, proteins and chondrocytes, were incorporated prior to the injection within the thermogelling solution.20 Carrageenan a polysaccharide composed of 1,4-linked-α-D-galactose and 1, 3 linked-β-D-galactose with a variable portion of sulfate groups, forms a gel with potassium ions, but also shows gelation under salt-free conditions. However, gels prepared in the presence of metallic ions were substantially stronger than those obtained under salt-free conditions21. Ionically crosslinked chitosan hydrogels are formed by complex formation between chitosan and polyanions, such as dextran sulfate or polyphosphoric acids22. Doxorubicin was encapsulated in nanoparticles of the chitosan hydrogels. This particle showed a minimal burst release and retained good in vitro cytotoxicity due to released drugs. Alginate was ionically crosslinked by immersing in aqueous solution of calcium acetate of different molarities at time. Permeability of acetaminophen in hydrated calcium alginate film was studied. Permeability depends upon the concentration of calcium acetate solution and immersion time. The highest limiting permeability was observed in film prepared using the highest concentration of calcium acetate for greater time. It is suggested that this is result of rapid croslinking of sodium alginate at the surface which in turn shows the diffusion of calcium ions into the film23. Gellan gum is a linear anionic polysaccharide produced by the microorganism Pseudomonas elodea24. Hydrophilic drug, propranolol hydrochloride was encapsulated in gellan gum beads in an aqueous environment by the ionotropic gelation method. Optimal preparation conditions allowed a very high incorporation efficiency (92%). Storage conditions (wet or dry state) and the time of storage did not modify the release of the drug25. Cross-linked calcium-gellan beads containing diclofenac sodium as model drug, using full 33 factorial design were prepared. Drug quantity, pH of cross-linking solution, and speed of agitation were selected as variables for factorial design. Studies indicate that, in addition to drug:polymer ratio, pH of cross-linking solution and speed of agitation also influence the formation and properties of calcium-gellan beads26. Thus ionotropic gelation with gellan gum seems to offer new opportunities in the field of bioencapsulation and could be useful for the encapsulation of fragile drugs. Also crosslinked chitosan and alginate films are promising for controlled drug delivery applications.
Crosslinking by crystallization: Poly (vinyl alcohol) (PVA) is a water soluble polymer. When aqueous solutions of PVA are stored at room temperature they gradually form a gel with, however, a low mechanical strength. Interestingly, once aqueous solution of this polymer undergoes freeze-thawing process a strong and highly elastic gel is formed27. Addition of alginate to the PVA solution before freeze-thawing, the gel properties could be modulated. With increase in concentration of alginate, the mechanical strength of gel increased which was associated with a decrease in release of model drug28.
Hydrophobised polysaccharides: Examples of polysaccharides reported in literature used for preparation of physically crosslinked hydrogels by hydrophobic modification are chitosan, dextran, pullulan and carboxy methyl curdlan29-35. This compound forms monodisperse hydrogel nanoparticle of 20-30 nm with high water content upon dialyzing a solution from DMSO against PBS buffer. Various proteins such as α chymotrypsin, BSA and insulin have been incorporated. As example, the hydrophobic antitumour drug adriamicin (ADR) was taken up inside the particles by simply mixing the pullulan suspension with ADR31. Slow release was observed at pH 7.4, which increases at lower pH of the medium due to increased solubility of drug. The stability of the drug was increased, however due to poor cellular uptake of the complexes and / or slow release of ADR, the invitro cytotoxicity against HeLa cells appeared rather low. Rapid complexation was also observed for insulin approximately 10 molecules of insulin were taken up inside the pullulan particles within 10 minutes after mixing32. The resulting microenvironment protected the protein effectively against the thermal denaturation aggregation and enzymatic degradation. Dissociation of insulin occurred on addition of BSA, which may provide a basis for invitro release of the insulin. Indeed the in vivo activity of insulin loaded nanoparticles was similar to that free insulin after i.v. injection. By covalent attachment of lactoside or galactoside to the pullulan backbone, nanoparticles were obtained which show binding to the receptor β-D-galactose-specific lectin RCA120, which provides a possibility for a cell-specific targeting. In vitro they were more effectively internalized than conventional nanoparticles by cells expressing galactose-specific receptors such as rat hepatocytes and HepG2 cells, in contrast to cells which lack such receptors33. Moreover, biodistribution studies showed enhanced accumulation in the liver. Self assembled hydrogels nanoparticles have also been prepared from carboxy methyl curdlan, a polysaccharide having anti-tumor activity, by substitution with a hydrophobic sulfonyl urea35. Release of the anti-cancer drug all-trans retinoic acid from these nanoparticles showed first order kinetics. An increased drug-loading and degree of hydrophobic modification resulted in a slower release. Upon conjugation of lactobionic acid to the CM-curdlan, specific binding to HepG2 cells was observed in vitro. Another example of a hydrophobized polysaccharide is the water soluble glycol chitosan substituted with palmitoyl chains. They assemble into unilamellar polymeric vesicles in the presence of cholesterol36. These polymeric vesicles are found to be biocompatible and haemocompatible and capable of entrapping water-soluble drugs37. Highly porous solid materials are obtained after freeze drying, which are hydrated without swelling to 20 x its dry weight in alkaline buffer38. In contrast to most chitosan based materials, the hydration decreased in acidic environment, which was attributed to the higher erosion rate at low pH. Chitosan has been grafted with PL(G) by Qu et. al., in which the hydrophobic polyester side chains are responsible for the hydrophobic interactions in water39, 40. Reversible water uptake of the materials was observed when the pH was switched between 2.2 and 7.4, the lowest pH providing the highest swelling due to charge repulsion by protonation of the free amine groups on the polymer backbone. The maximum water uptake in the protonation form depends on the glycolic acid / lactic acid content. Other chitosan hydrogels that respond to external charges like pH or temperature have been prepared by grafting with poly(acrylic acids) (PAAc)41 or poly(N-isopropylacrylamide) (PNIPAAm)42 In addition to chitosan, also carboxy methyl dextran has been grafted with PNIPAAm chains aming at thermosensitive hydrogels43. Cloud point measurements were conducted in this case, indicating a phase transition at around 38°C, but no data on hydrogel characteristics have been reported yet.
Chemical crosslinking of polysaccharide is highly versatile method with good mechanical stability. During crosslinking counterions diffused into the polymeric and crosslinking agent reacts with polysaccharides forming either intermolecular or intramolecular linkages. Factors which affect chemical crosslinking are concentration of crosslinking agent and crosslinking time. The high concentration of crosslinking agent induces rapid crosslinking. Like physical crosslinking high counterion concentration would require longer exposure times to achieve complete crosslinking of the polysaccharides44. Chemical crosslinking is carried out by following methods.
Crosslinking by radical polymerization:
Chemical crosslinking can be carried out by radical polymerization in presence of crosslinking agent. In particular dextran is used as building block for (degradable) hydrogels. Dextran is a bacterial polysaccharide, consists essentially of -1,6 linked D-glucopyranose residues. The low molecular weight fractions of dextran (Mw between 40 and 100 kDa) have been used as plasma expander45 which has resulted in a good documentation of pharmacological activities and side effects of dextran. Dextran has therefore been investigated for the delivery of drugs, proteins and imaging agents46. Moreover, due to presence of dextranase in colon, dextran based gels are under investigation as a colon delivery system47. Research on polymerizable dextran was pioneered by Edman et al.48 who reacted dextran dissolved in water with glycidylacrylate. A hydrogel was formed after the addition of an initiator system containing of NNNN tetramethylene-diamine and ammonium peroxydisulfate to an aqueous solution of the acryldextran also containing NN methylenebisacrylamide. Enzymes were immobilized with almost full retention of their activity by an emulsion polymerization technique in microspheres of polyacryldextarn.48, 49. A method has been developed to synthesize methacrylated dextran. Dextran is dissolved in a suitable aprotic solvent (DMSO) after which derivatization with glycidylmethacrylate (GMA) catalyzed by 4-(N-N-dimethyl amino) pyridine, is carried out. Almost quantitative incorporation of GMA was found and the degree of substitution can be fully controlled. A detailed analysis by NMR50 and by the mass spectroscopy of the products obtained after enzymatic degradation51 revealed that under the selected conditions the reaction of GMA and dextran was a transesterification resulting in a dextran derivative with the methacyrlate group directly attached to the dextran chain. The synthetic procedure developed was also suitable to derivatize other compounds with methacrylate groups, among which are inulin52 and sucrose53. Meth(acrylate) groups can also be introduced in water-soluble polymers using (meth)acryloyl chloride,54,55 methacrylic anhydride,56 and by the subsequent reaction of dextran with bromoacetyl bromide and sodium acrylate57. Moreover, using enzymes as catalyst, (meth) acrylic groups have been introduced in mono and disaccharides, which can be used for synthesis of hydrogels58, 59, 60. The synthesis is carried out in anhydrous pyridine and products are normally obtained in a high yield. In contrast to chemical methods, enzymatic synthesis results in a very good regeoselectivity. A polymerizable dextran derivative was obtained by reaction of dextran with maleic anhydride. These dextran derivatives can be converted into a hydrogel by UV-induced polymerization of the vinyl groups. The gels were not degradable under physiological conditions. They did, however, exhibit a strong pH dependant swelling behavior due to the presence of carboxylic acid groups in the network61. In synthesis of methacrylated dextran derivatives the polymerizable groups are connected via a) hydrolytically sensitive group(s) to a dextran backbone. The hydrolysable groups are either a carbonated ester or lactic acid groups. After polymerization these derivatives the gel degraded under physiological conditions due to the presence of (carbonate) ester groups in the crosslinks, yielding dextran, lactic acid and short fragments of Poly(2 hydroxy ethyl methacrylate) (pHEMA) as degradation products62. Chitosan undergoes crosslinking by radical induced polymerization in presence of potassium persulfate at 60°C, leading to extensive crosslinking of fragmented chains on subsequent cooling at 4°C. As a result a possible conformation change leading to higher crystallinity, as evidenced by IR, X-ray and CNMR was observed. Chitosan crosslinking leads to formation of permanently covalent network, which may allow the free diffusion of water/bioactive material and also enhance the mechanical properties. Chemical crosslinks are formed by irreversible covalent links as in covalently crosslinked chitosan. Thus allow drug delivery to be efficiently controlled63.
Crosslinking by aldehyde:
In order to establish crosslinking, rather drastic conditions have to be applied (low pH, high temperature etc.). This has especially been investigated for the preparation of crosslinked amine containing polysaccharides64. Because glutaraldehyde is a toxic compound that even at low concentration shows cell growth inhibition, alternatives has been developed. Crosslinking of gelatin using polyaldehydes obtained by partial oxidation of dextran has been reported65. These gels were designed for application in wound treatment and epidermal growth factor (EGF) was incorporated to promote wound healing. The release rate of EFC decreased with increase in storage time which was ascribed to the ongoing processes of both chemical crosslinking and physical structuring of the hydrogel matrix. Poly(aldehydeguloronate) obtained by oxidation with periodate of partially depolymerized alginate, can be crosslinked with adipic acid dihydrazide and converted into a hydrogel. The swelling and degradation of the gel could be controlled by the amount of adipic acid dihydrazide66. These hydrogel films have therefore potential to act as a delivery matrix for sustained release of drug at wound sites67. The procedure for the preparation of crosslinked chitosan microspheres coated with polysaccharides or lipid for intelligent drug delivery system is reported. The microspheres were prepared with an inverse emulsion of 5-FU or its derivative solution of hydrochloric acid of chitosan in toluene containing SPAN 80. Chitosan was crosslinked with Schiff’s salt formation by adding glutaraldehyde toluene solution. At the same time, the amino derivatives of 5-FU were immobilized, obviously resulting in an increase in the amount of drug within the microspheres. The microspheres were coated with anionic polysaccharides (e. g. carboxymethylchitin, etc.) through a polyion complex formation reaction. The results revealed that the coating layers of microspheres were effective barriers to 5-FU release68.
Crosslinking by addition reaction:
Polysaccharides can be crosslinked with 1,6-hexa-methylenediisocyanate or 1,6-hexanedibromide and many other reagents. The network properties can be easily tailored by the concentration of the dissolved polysaccharide and the amount of crosslinking agent. The crosslinking reactions are preferably carried out in organic solvents, because water can also react with the crosslinking agent. Further, since the crosslinking agents are generally speaking very toxic, the gels have to be extracted extensively to remove traces of unreacted agents. Once these matrices are aimed for the release of pharmaceutically active agent, they have to be loaded after the gel formation and extraction process. This means that protein molecules can be loaded in meshes of the gels which are larger than the protein and these systems therefore show typically first-order release. This often results in a limited duration of the release. Finally, between the polymer chains, linkages are established which are stable. This means that degradation only occurs once the polymer backbone is degraded by enzymes69, 70, 71.
Crosslinking by condensation reaction:
A very efficient reagent to crosslink polysaccharides with amide bonds is NN-(3-dimethylaminopropyl)-N-ethyl carbodiimide. In order to obtain alginate gels with better mechanical properties than the ionically crosslinked gels, Mooney et al. developed a method to a covalently crosslink this polymer. Alginate and PEG-diamines were crosslinked using N-ethyl carbodiimide. The mechanical properties could be controlled by the amount of PEG-diamine in the gel and molecular weight of PEG72.
Characterization of crosslinked polysaccharides:
Characterization of crosslinked polysaccharides were done by infrared spectroscopy, X-ray diffractometry, scanning electron microscopy and by water uptake methods44, 63.
1. R. L. Whistler, J. N. Bemiller, Industrial Gums, 3rd edition, academic press, Newyork, 1993.
2. M. Glickman, Origins and classification of hydrocolloids, Food Hydrocolloids, 3, CRC Press, Boca Raton, Florida, 1982, 1, 3-18.
3. D. A. Rees, The shape of molecules, Carbohydrates Polymers, 1967, 57.
4. P. A. Sanford, A. Laskin, Extra cellular microbial polysaccharides-a critical review, American Chemical Society, Washington, D. C., USA, 190-210.
5. N.A. Peppas (Ed), Hydrogels in medicine and pharmacy, Vol. I, II, III, CRC Press, Boca Raton , FL , 1986.
6. J. M. Rosiak, F. Yoshii, Hydrogels and their medical applications, Nucl. Instrum. Methods Phy. Res. B, 1999, 151, 56-64.
7. I. Y. Galaev, B. Mattiasson, Smart polymers and what they could do in biotechnology and medicine, Trends Biotechnol., 1999, 17, 335-340.
8. S.P. Baldwin, W. M. Saltzman, Materials for protein delivery in tissue engineering, Adv. Drug Deliv. Rev., 1998, 33, 71-86.
9. W. R. Gombotz, D. K. Pettit, Biodegradable polymers for protein and peptide drug delivery, Bioconjug. Chem., 1995, 6, 332-351.
10. N. A. Peppas, P. Bures, W. Leobandung, H. Ichikawa, Hydrogels in pharmaceutical formulations, Eur. J. Pharm. Biopharm., 2000, 50, 27-46.
11. N. A. peppas, Y. Huang, M. Torres-Lugo, J. H. ward, J. Zhang, Physicochemical foundations and structural design of hydrogels in medicine and biology, Annu. Rev. Biomed. Eng. , 2000, 2, 9-29.
12. S. H. Gehrke, Synthesis and properties of hydrogels used for drug delivery, Drugs Pharm. Sci., 2000, 102, 473-546.
13. K. Park, W. S. W. Shalaby, H. Park (Eds), Biodegradable Hydrogels For Drug Delivery, Technomic, Basle , 1993.
14. Bauer, Kurt Heinz, Betzing, Juergen. inventors; BASF Assignee, Crosslinked polysaccharides, process for their preparation and their use. US patent 5688776.1997 Nov. 18.
15. P. Gacesa, Alginates, Carbohydr. Polym. 1988, 8, 161-182.
16. M.F.A. Goosen, G.M. O’Shea, H. M. Gharapetian, S. Chou, A. M. Sun, Optimization of microencapsulation parameters: semipermiable microcapsules as a bioartificial pancrease, Biotechnol. Bioeng., 1985, 27, 146-150.
17. W. R. Gombotz, S. F. Wee, Protein release from alginate matrices, Adv. Drug. Deliv. Rev., 1998, 31, 267-285.
18. A. Polk, B. Amsden, K. DeYao, T. Peng, M. F. A. Goosen, Controlled release of albumin from chitosan- alginate microcapsules, J. Pharm. Sci., 1994, 83, 178-185.
19. L.S. Liu, S.Q. Liu, S.Y. Ng, M. Froix, T. Ohno, J. Heller, Controlled release of interleukin-2 for tumour immunotherapy using alginate/Chitosan porous microspheres, J. Controlled Release, 1997, 43, 65-74.
20. A. Chenite, C.Chaput, D. Wang, C. Combes, M. D. buschmann, C. D. Hoemann, J. C. Leroux, B. L/ Atkinson, F. Binette. A Selmani, Novel injectable neutral solutions of chitosan from biodegradable gels in situ, Biomaterials, 2000, 21, 2155-2161.
21. K. S. Hosain, K. Miyanaga, H. Maeda, N. Nemoto, Sol-gel transition behavior of pure carrageenan in both salt free and added salt states, Biomacromolecules, 2001, 2, 42-449.
22. K. A. Janes, M. P. Fresneau, A. Marazuela, A. Fabra, M. J. Alonso, Chitosan nanoparticles as delivery system for doxorubicin, J. Controlled Release, 2001, 73, 255-267.
23. T. N. Julian, G. W. Radebaugh, S. J. Wisniewski, Permeability characteristics of calcium alginate films, J. Controlled Release, 1988, 7, 165-169.
24. K. S. Kang, G. T. Veeder, P. J. Mirrasoul, T. Kaneko, I. W. Cottrell, Agar-like polysaccharide produced by Pseudomonas species: production and basic properties, Appl.Environ. Microbiol., 1982, 43, 1086–1091.
25. F. Kedzierewicz, C. Lombry, R. Rios, M. Hoffman, P. Maincent, Effect of the formulation on the in-vitro release of propranolol from gellan beads, International Journal of Pharmaceutics, 1999, 178, 129–136.
26. Sachin Patil, Sameer Sharma, Anagha Nimbalkar and Atmaram Pawar, Study of formulation variables on properties of drug-gellan beads by factorial design, Drug Development and Industrial Pharmacy, 2006, 32, 315–326.
27. F. Yokoyama, I. Masada, K. Shimamura, T. Ikawa, K. Monobe, Morphology and structure of highly elastic poly (vinyl alcohol) hydrogel prepared by repeated freezing-and-melting, Colloid. polym. Sci., 1986, 264, 595-601.
28. A. Takamura, F. Ishii, H. Hidaka, Drug release from poly (vinyl alcohol) gel prepared by freeze- thaw procedure, J. Controlled Release, 1992, 20, 21-27.
29. K. Akiyoshi, S. Deguchi, N. Moriguchi, S. Yamaguchi, J. Sunamoto, Self-aggregates of hydrophobized polysaccharides in water – formation and characterization of nanoparticles, Macromolecules, 1993, 26, 3062-3068.
30. K. Akiyoshi, S. Deguchi, H. Tajima, T. Nshikawa, J. Sunamoto, Microscopic structure and thermoresponsiveness of a hydrogel nanoparticle by self assembly of a hydrophobized polysaccharide, Macromolecules, 1997, 30, 857-861.
31. K. Akiyoshi, I. tanuguchi, H. fukui, J. Sunamoto, Hydrogel nanoparticle formed by hydrophobized polysaccharide. Stabilization of adriamycin by complexation, Eur. J. Pharm. Biopharm., 1996, 42, 286-290.
32. K. Akiyoshi, S. Kobayashi, S. Shichibe, D. Mix, M. Baudys, S. W. Kim, J. Sunamoto, Self assembled hydrogel nanoparticle of cholesterol-bearing pullulan as a carrier of protein drugs: Complexation and stabilization of insulin, J. controlled release, 1998, 54, 313-320.
33. K. Akiyoshi, I. tanuguchi, J. Sunamoto, Self-aggregate nanoparticles of cholesteryl and galactoside groups-substituted pullulan and their specific binding to galactose specific lectin, RCA120, Macromol. Chem. Phys., 1999, 200, 1555-1560.
34. K. Akiyoshi, E. C. Kang, S. Kurumada, J. Sunamoto, Controlled association of amphiphilic polymers in water: thermosensitive nanoparticles formed by self-assembly of hydrophobically modified pullulans and poly(N-iso-propylacrylamides), Macromolecules, 2000, 33, 3244-3249.
35. K. Na, K. H. Park, S. W. Kim, Y. H. Bae, Self-assembled hydrogel nanoparticles from curdlan derivatives: characterization, anticancer drug release and interaction with a hepatoma cell line (HepG2), J. Controlled Release, 2000, 69, 225-236.
36. I. F. Uchegbu, A. G. Schatzlein, L. Tetley, A. I. Gray, J. Sludden, S. Siddique, E. Mosha, Polymeric chitosan based vesicles for drug delivery, J. Pharm. Pharmcol., 1998, 50, 453-458.
37. J. Sludden, I. F. Uchegbu, A. G. Schatzlein, The encapsulation of bleomycin within chitosan based polymeric vesicles does not alter its biodistribution, J. Pharm. Pharmcol., 2000, 52, 377-382.
38. L. Noble, A. I. Gray, L. Sadiq, I. F. Uchegbu, A non-covelently crosslinked chitosan based hydrogel, Int. J. Phar., 1992, 192, 173-182.
39. X. Qu, A. Wirsen, A. C. Albertsson, Structural change and swelling mechanism of pH sensitive hydrogel based on chitosan and D,L,Lactic acid, J. Appl. Polym. Sci., 1999, 74, 3186-3192.
40. X. Qu, A. Wirsen, A. C. Albertsson, Novel pH sensitive chitosan hydrogel swelling behavior and states of water, Polymer, 2000, 41, 4589-4598.
41. M. Yazdani-Pedram, J. Retuert, R. Quijada, Hydrogels based on modified chitosan, I- Synthesis and swelling behavior of poly(acrylic acid) grafted chitosan, Macromol. Chem. Phys., 2000, 201, 923-930.
42. S. Y. Kim, S. M. Cho, Y. M. Lee, S. J. Kim, Thermo- and pH sensitive behavior of graft copolymer and blend based on chitosan and N-isopropylacrylamide, J. Appl. Polym. Sci., 2000, 78, 1381-1391.
43. K. M. Huh, J. Hashi, t. Ooya, N. Yuvi, Synthesis and characterization of dextran grafted with poly-N-iso-propylacrylamide-co-N,N-dimethyl acrylamide, Macromol. Chem. Phys., 2000, 201, 613-619.
44. R. L. Carmen., B. Roland, Mechanical, water uptake and permeability properties of crosslinked chitosan glutamate and alginate films. J. Controlled release, 1997, 44,215-225.
45. L. Thoren, The dextran, clinical data, Dev. Biol. Stand., 1981, 48, 157-167.
46. R. Mehvar, Dextran for targeted and sustained delivery of therapeutic and imaging agents, J. Controlled release, 2000, 69, 1-25.
47. H. Brondsted, C. Anderson, L. Hovgaard, Crosslinked dextran, a new capsule material for colon targeting of drugs, J. Controlled Release, 1998, 53, 7-13.
48. P. Edman, B. Ekman, I. Sjoholm, Immobilization of proteins in microspheres of polydextran, J. Pharm. Sci., 1980, 69, 838-842.
49. I. P. Sjoholm, P. Edman, The use of biocompatible microparticles as carriers of enzymes and drugs in vivo, in: S. S. Davies, L. Illum, J. G. Vie, E. Tomlinson (Eds.), Microspheres and drug therapy. Pharmaceutical immunological and Medical Aspects, Elsevier, Amsterdam , 1984, 245-262.
50. W. N. E. van Dijk-Wolthuis, J. J. Kettenes-van den Bosch, A. van der Kerk-van Hoof, W. E. Hennik, Reaction of dextran with glycidyl methacrylate: an unexpected transesterification, Macromolecules, 1997, 30, 3411-3413.
51. O. Franssen, R. D. van Ooijen, D. de Boer, R. A. A. Maes, J. N. Herron, W. E. Hennik, Enzymatic degradation of methacrylates dextrans, Macromolecules, 1997, 30, 7408-7413.
52. B. Stubbe, B. Maris, G. van den Mooter, S. C. de Smedt, J. Demeester, The in vitro evaluation of azo-containing polysaccharides gels for colon delivery, J. Controlled Release, 2001, 75, 103-114.
53. L. Ferreira, M. M. Vidal, C. F. G. C. Geraldes, M. H. Gil, Prepartion and characterization of gels based on sucrose modified with glycidyl methacryalate, Carbohydr. Polym., 2000, 41, 15-24.
54. E. Marsano, E. Bianchi, S. Gagliardi, F. Ghioni, Hydroxy-propyl-cellulose derivatives: phase behavior of hydroxyl-propylcellulose methacrlate, Polymer, 2000, 41, 533-538.
55. L. K. Huang, R. C. Metha, P. P. DeLucca, Evaluation of a statistical model for formation of poly(acryloyl hydroxyl-ethyl starch) microspheres, Pharm. Res., 1997, 14, 475-482.
56. S. H. Kim, C. C. Chu, Synthesis and characterization of dextran-methacrylate hydrogels and structural study by SEM, J. Biomed. Mater. Res., 2000, 49, 517-527.
57. S. H. Kim, C. Y. Won, C. C. Chu, Synthesis and characterization of dextran-based hydrogel prepared by photocrosslinking , Carbohydr. Polym., 1999, 40, 183-190.
58. N. S. Patil, J. S. Dordick, D. G. rethwisch, Macroporous poly(sucrose acrylate) hydrogels for controlled release of macromolecules, Biomaterials, 1996, 17, 2343-2350.
59. B. D. Martin, R. J. Linhardt, J. S. Dordick, Highly swelling hydrogels from ordered galactose-based polyacrylates, Biomaterials, 1998, 19, 69-76.
60. N. S. Patil, Y. Li, D. G. rethwisch, J. S. Dordick, Sucrose diacrylate: A unique chemically and biologically degradable crosslinker for polymeric hydrogels. J. Polym. Sci., Part A Polym. Chem., 1997, 35, 2221-2229.
61. S. H. Kim, C. Y. Won, C. C. Chu, Synthesis and characterization of dextran-maleic acid based hydrogel, J. Biomed. Mater. Res., 1999, 46, 160-170.
62. W. N. E. van Dijk-Wolthuis, S. K. Y. Tsang, J. J. Kettenes-van den Bosch, W. E. hennink, A new class of polymerizable dextrans with hydrolysable groups: hydroxyethyl methacryalated dextran with and without oligolactate spacer, Polymer, 1997, 38, 6235-6242.
63. V. Keelara Harish Prashant, N. Rudrapatnam tharanatham, Crosslinked chitosan-preparation and characterization, Carbohydr. Res., 2006, 341, 169-173.
64. S. R. Jameela, A. Jaykrishnan, Glutarldehyde crosslinked chitosan as a long acting biodegradable drug delivery vehicle: studies on the in vitro release of mitoxantrone and in vivo degradation of microspheres in rat muscle, Biomaterials, 1995, 16, 769-775.
65. J. P. Draye, B. Delaey, A. van de Voorde, A. van den Bulcke, B. Bogdanov, E. Schacht, In vitro release characteristics of bioactive molecules from dextran dialdehyde cross-linked gelatin hydrogel films, Biomaterials, 1998, 19, 99-107.
66. K. Y. lee, K. H. Bouhadir, D. J. Mooney, Degradation behavior of covalently crosslinked Poly(aldehyde guluronate) hydrogels, Macromolecules, 2000, 33, 97-101.
67. Y. Luo, R. K. Kirker, G. D. Prestwich, Crosslinked hyaluronic acid hydrogels films: new biomaterials for drug delivery, J. Controlled release, 2000, 69, 169-184.
68. K. D. Yao, T. Peng, J. J. Yu, M. X. Xu, M. F. A. Goosen, Microcapsules /microspheres related to chitosan, J. M. S. Rev. Macromol. Chem. Phys., 1995, C-35, 155-180.
69. H. Brondsted, L. Hovgaard, L. Simonsen, Dextran hydrogels for colon specific drug delivery. Comparative release study of hydrocortisone and prednisolone sodium phosphate, Stp. Pharma. Sci., 1995, 5, 65-69.
70. S. H. Gehrke, L. H. Uhden, J. F. McBride, Enhanced loading and activity retention of bioactive proteins in hydrogel delivery system, J. Controlled release, 1998, 55, 21-33.
71. T. Coviello, M. Grassi, G. Rambone, E. Santucci, M. Carafa, E. Murtas, F. M. Riccieri, F. Alhaique, A novel hydrogel system from sleroglucan: synthesis and characterization, J. Controlled Release, 1999, 60, 367-378.
72. P. Eiselt, K. Y. Lee, D. J. Mooney, Rigidity of two-component hydrogels prepared from alginate and poly(ethylene glycol) diamines, Macromolecules, 1999, 32, 5561-5566.
Department of Pharmaceutics, Shree Santkrupa College of Pharmacy, A/P Ghogaon, Tal. Karad, Dist. Satara.
D. R. Jadge
Shree Santkrupa College of Pharmacy, A/P Ghogaon, Tal. Karad, Dist. Satara. 415111.
Hydrogels as controlled drug delivery systems: Synthesis, crosslinking, water and drug transport mec
Hi bloggers here iam with my first topic of the month of july "HYDROGEL DRUG DELIVERY HOLDS PROMISE IN FUTURE OF MEDICINE" INTRODUCTION:
Microencapsulation of Hemoglobin in Chitosan-coated Alginate Microspheres Prepared by Emulsification
Chitosan-coated alginate microspheres prepared by emulsification/internal gelation were chosen as carriers for a model protein, hemoglobin (Hb),
Hydrogel nanoparticles have gained considerable attention in recent years as one of the most promising Nanoparticulate drug delivery systems owing to their unique potentials via combining the characteristics Hydrogel system (e.g., hydrophilicity and extremely high water content) with a nanoparticle (e.g., very small size). Several polymeric hydrogel nanoparticulate systems have been prepared and characterized in recent Years, based on both natural and synthetic polymers, each with its own advantages and drawbacks. Among the natural polymers, chitosan and alginate have been studied extensively for preparation of Nanoparticles and from synthetic group, hydrogel nanoparticles based on poly (vinyl alcohol), poly (ethylene oxide), poly (ethyleneimine), poly (vinyl pyrrolidone), and poly-N-isopropylacrylamide have been reported With different characteristics and features with respect to drug delivery. Regardless of the type of polymer Used, the release mechanism of the loaded agent from hydrogel nanoparticles is complex, while resulting from three main vectors, i.e., drug diffusion, hydrogel matrix swelling, and chemical reactivity of the drug/ Matrix. Several cross linking methods have been used in the way to form the hydrogel matix structures which can be classified in two major groups of chemically- and physically-induced cross linking.
The purpose of this study was to examine the effect of charge ratio on the formation and properties of the chitosan (CS)–dextran sulfate (DS) nano
Preparation and in vitro evaluation of mucoadhesive chitosan microspheres of amlodipine besylate for
Chitosan, a naturally linear biopolyaminosaccharide is derived from alkaline deacetylation of chitin which is the second abundant polysaccharide
Chitosan Gels for the Vaginal Delivery of Lactic Acid: Relevance of Formulation Parameters to Mucoad
The aim of this work was to assess the effect of formulation parameters of a mucoadhesive vaginal gel based on chitosan and lactic acid, and to h