EP2793908A1 - Composition, préparation, et utilisation de matériaux de membrane de chitosan dense - Google Patents

Composition, préparation, et utilisation de matériaux de membrane de chitosan dense

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Publication number
EP2793908A1
EP2793908A1 EP12859619.4A EP12859619A EP2793908A1 EP 2793908 A1 EP2793908 A1 EP 2793908A1 EP 12859619 A EP12859619 A EP 12859619A EP 2793908 A1 EP2793908 A1 EP 2793908A1
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EP
European Patent Office
Prior art keywords
chitosan
acid
composition
membrane
gel
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Withdrawn
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EP12859619.4A
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German (de)
English (en)
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EP2793908A4 (fr
Inventor
Arthur A. DECARLO
April ELLIS
Thomas P. Dooley
Maria Belousova
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Agenta Biotechnologies Inc
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Agenta Biotechnologies Inc
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Publication of EP2793908A1 publication Critical patent/EP2793908A1/fr
Publication of EP2793908A4 publication Critical patent/EP2793908A4/fr
Withdrawn legal-status Critical Current

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    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08B—POLYSACCHARIDES; DERIVATIVES THEREOF
    • C08B37/00—Preparation of polysaccharides not provided for in groups C08B1/00 - C08B35/00; Derivatives thereof
    • C08B37/0006—Homoglycans, i.e. polysaccharides having a main chain consisting of one single sugar, e.g. colominic acid
    • C08B37/0024—Homoglycans, i.e. polysaccharides having a main chain consisting of one single sugar, e.g. colominic acid beta-D-Glucans; (beta-1,3)-D-Glucans, e.g. paramylon, coriolan, sclerotan, pachyman, callose, scleroglucan, schizophyllan, laminaran, lentinan or curdlan; (beta-1,6)-D-Glucans, e.g. pustulan; (beta-1,4)-D-Glucans; (beta-1,3)(beta-1,4)-D-Glucans, e.g. lichenan; Derivatives thereof
    • C08B37/0027—2-Acetamido-2-deoxy-beta-glucans; Derivatives thereof
    • C08B37/003—Chitin, i.e. 2-acetamido-2-deoxy-(beta-1,4)-D-glucan or N-acetyl-beta-1,4-D-glucosamine; Chitosan, i.e. deacetylated product of chitin or (beta-1,4)-D-glucosamine; Derivatives thereof
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K31/00—Medicinal preparations containing organic active ingredients
    • A61K31/70—Carbohydrates; Sugars; Derivatives thereof
    • A61K31/715—Polysaccharides, i.e. having more than five saccharide radicals attached to each other by glycosidic linkages; Derivatives thereof, e.g. ethers, esters
    • A61K31/716—Glucans
    • A61K31/722—Chitin, chitosan
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61P—SPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
    • A61P17/00—Drugs for dermatological disorders
    • A61P17/02—Drugs for dermatological disorders for treating wounds, ulcers, burns, scars, keloids, or the like
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61P—SPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
    • A61P31/00—Antiinfectives, i.e. antibiotics, antiseptics, chemotherapeutics
    • A61P31/04—Antibacterial agents
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61P—SPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
    • A61P31/00—Antiinfectives, i.e. antibiotics, antiseptics, chemotherapeutics
    • A61P31/10—Antimycotics
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61P—SPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
    • A61P7/00—Drugs for disorders of the blood or the extracellular fluid
    • A61P7/04—Antihaemorrhagics; Procoagulants; Haemostatic agents; Antifibrinolytic agents
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08J—WORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
    • C08J3/00—Processes of treating or compounding macromolecular substances
    • C08J3/02—Making solutions, dispersions, lattices or gels by other methods than by solution, emulsion or suspension polymerisation techniques
    • C08J3/03—Making solutions, dispersions, lattices or gels by other methods than by solution, emulsion or suspension polymerisation techniques in aqueous media
    • C08J3/075—Macromolecular gels
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
    • C08L5/00—Compositions of polysaccharides or of their derivatives not provided for in groups C08L1/00 or C08L3/00
    • C08L5/08—Chitin; Chondroitin sulfate; Hyaluronic acid; Derivatives thereof
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08J—WORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
    • C08J2305/00—Characterised by the use of polysaccharides or of their derivatives not provided for in groups C08J2301/00 or C08J2303/00
    • C08J2305/08—Chitin; Chondroitin sulfate; Hyaluronic acid; Derivatives thereof

Definitions

  • the present invention relates to dense chitosan film or membrane materials and methods for their preparation.
  • the materials have utility in medical, scientific, and other industries.
  • biodegradable polymers have been explored as scaffolds for wound healing and tissue engineering applications and include synthetic polymers like poly-caprolactone, poly (lactic-co-glycolic acid), poly(ethylene glycol), and natural polymers such as alginate, gelatin, collagen, starch, and chitosan.
  • synthetic polymers like poly-caprolactone, poly (lactic-co-glycolic acid), poly(ethylene glycol), and natural polymers such as alginate, gelatin, collagen, starch, and chitosan.
  • naturally derived polymers are of special interest due to, as natural components of living structures, their biological and chemical similarities to natural tissues.
  • chitosan has been found as a compelling candidate in a broad spectrum of applications along with unique biological properties including biocompatibility, biodegradability to harmless saccharide products, nontoxicity, physiological inertness, remarkable affinity to proteins, in addition to antibacterial, antifungal, and haemostatic properties.
  • Chitin the source material for chitosan, is one of the most abundant organic materials, being second only to cellulose in the amount produced annually by biosynthesis. It is an important constituent of the exoskeieton in animals, especially in crustaceans, molluscs and insects. It is also the principal fibrillar polymer in the cell wall of certain fungi, and can be produced by microalgae. Deacetylated chitin derivatives have been referred to as "chitosan".
  • Chitosan is a linear polysaccharide, composed of glucosamine and N-acetyl glucosamine units linked by ⁇ (1 -4) glycosidic bonds - in essence, strings of sugar units. Depending on the source and preparation procedure, its molecular weight generally ranges from 10 kDa to over 1000 kDa.
  • the molecular weight of the chitosan polymer is routinely determined by viscosity and is expressed in terms of Centipoise (CPS) or Millipascal (mPas) units, and can range from about 5 mPas to 3000 mPas.
  • the content of glucosamine is termed as the degree of deacetylation (DD), and can range from 30% to 95%.
  • chitosan In its crystalline form, chitosan is normally insoluble in aqueous solution above pH 7, however, in dilute acids (pH ⁇ 6.0), the protonated free amino groups on glucosamine facilitate solubility of the molecule (Kim, Seo et al. 2008) .
  • chitosan has three types of reactive functional groups, an amino group as well as both primary and secondary hydroxyl groups at the C(2), C(3), and C(6) positions, respectively. These groups allow modification of chitosan for specific applications, which can produce various useful scaffolds for tissue engineering applications.
  • the chemical nature of chitosan in turn provides many possibilities for covalent and ionic modifications which allow extensive adjustment of mechanical and biological properties.
  • chitin is present within numerous taxonomic groups.
  • commercial chitins are usually isolated from marine crustaceans, such as shrimp.
  • Crustacean shells consist of 30-40% proteins, 30-50% calcium carbonate, and 20-30% chitin and also contain pigments of a iipidic nature such as carotenoids (astaxanthin, astathin, canthaxanthin, lutein and ⁇ -carotene). These proportions vary with species and with season.
  • chitin When chitin is extracted by acid treatment to dissolve the calcium carbonate followed by alkaline extraction to denature and dissolve the proteins and by a depigmentation step, a colorless to off-white product is obtained mainly by removing the astaxanthin.
  • the preparation method is a factor that affects the sample characteristics.
  • specific characteristics of these products Mw, DD
  • commercial chitins are prepared by a first step of deproteinisation followed by a second step of demineralization. In these conditions a "collapsed chitin", in which the native structure of the chitin is lost, is extracted.
  • chitosan in which the native chain and fibrous structures are intact and stabilized, is extracted when demineralization occurred in the first step.
  • Chitosan prepared by either method of chitosan extraction apply to the present invention.
  • the present invention does not restrict the source of chitosan from natural, semi-synthetic, or synthetic sources.
  • Chitosan is prepared by hydrolysis of the acetamide groups of chitin. This is normally conducted by harsh alkaline hydrolysis treatment due to the resistance of such groups imposed by the trans arrangement of the C2-C3 substituents in the sugar ring (Horton and Lineback 1965).Thermai treatments of chitin under strong aqueous alkali are usually needed to give partially deacetylated chitin (DD higher than 70%), regarded as chitosan. Usually, sodium or potassium hydroxides are used at a concentration of 30-50% w/v at high temperature (100 °C). This harsh hydroxide/heat method has the coincident effect of reducing or removing potential bacterial endotoxins, which is beneficial for biomedical applications of the resulting chitosan materials.
  • Chitosan DD can range from 56% -99% depending on chitin source and methods of chitosan preparation (Abou-Shoer 2010). Factors that affect the extent of deacetylation include concentration of the alkali, previous treatment, particle size and density of chitin. In practice, the maximal DD that can be achieved in a single alkaline treatment is about 75-85% (Roberts 1998). In general, during deacetylation, conditions must be the proper ones to deacetyiate, in a reasonable time, the chitin to yield a chitosan that is (subsequently) soluble in diluted acetic acid.
  • chitosan depolymerization can be carried out chemically, enzymaticaiiy, or physically. Chemical depolymerization is mainly carried out by acid hydrolysis using HC1 or by oxidative reaction using HNO 2 and H 2 O 2 .
  • TS tensile strength
  • % EB percentage elongation at break
  • EM elastic modulus
  • Chitosan-based scaffolds The mechanical properties of chitosan-based scaffolds are dependent on the pore sizes and pore orientations.
  • Chitosan can be formed as interconnected-porous structures by freezing and lyophilizing a chitosan solution or by processes such as an "internal bubbling process (IBP)" where CaCO-, is added to chitosan solutions to generate chitosan-CaCC gels in specific shapes by using suitable molds (Chow and Khor 2000).
  • IBP internal bubbling process
  • porous membranes varied from values similar to nonporous chitosan (approximately 30%) to greater than 100% as a function of both pore size and orientation. Porous membranes exhibited a stress-strain curve typical of composite materials with two distinct regions: a low-modulus region at low strains and a transition to a 2-3 fold higher modulus at high strains. The tensile strengths of these porous structures are reportedly in the range of 30-60 kPa (Madihally and Matthew 1999).
  • Chitosan is absent from mammals but can be degraded in vivo by several enzymes, most notably lysozyme, chitinase, and NAGase (Dalian, da Luz Moreira et ai. 2007; Kim, Seo et al. 2008) (Aranaz, Mengibar et al. 2009) (Niekraszewicz 2005). Biodegradation leads to the release of non-toxic oligosaccharides of variable length which can be subsequently incorporated into glycosaminoglycans and glycoproteins, to metabolic pathways, or be excreted.
  • Lysozyme a non-specific glycoside hydrolase present in mammalian tissues and implicated in innate immunity, seems to play a significant degradation role on chitin and chitosan.
  • the degradation kinetics seem to be inversely related to the degree of crystallinity, which is controlled mainly by the DD.
  • the distribution of acetyl groups also affects biodegradability since the absence of acetyl groups or their homogeneous distribution (random rather than block) results in very low rates of enzymatic degradation.
  • the degradation rate also affects the biocompatibility since very fast rates of degradation will liberate (and potentially accumulate) the amino sugars that can produce a mild inflammatory response.
  • Chitosan samples with low DD induce a more acute inflammatory response while chitosan samples with high DD induce a minimal response due to the low degradation rate.
  • Degradation has been shown to increase as DD decreases. In other words, in general, degradation is enhanced by increased acetylation (Lim, Song et ai. 2008).
  • Kofuji et al. investigated the enzymatic behaviors of various chitosans by observing changes in the viscosity of chitosan solution in the presence of lysozyme (Kofuji, Qian et al. 2005).
  • Chitosan shows very good biocompatibility, but this property depends on the characteristics of the sample (e.g., natural source, method of preparation, Mw and DD). Although the digestive (oral/gastrointestinal) enzymes can partially degrade chitosan, when orally administered it is not absorbed. For this reason, chitosan is considered as not bioavailable by the oral route. Chitosan has a LD50 in mice of around 16g/kg, a very high dose and consistent with negligible acute toxicity. Toxicity of chitosan is reported to depend on DD. Schipper et al.
  • chitosans with DD higher than 35% showed low toxicity, while a DD under 35% (i.e., chitin) caused dose-dependant toxicity (Schipper, Varum et al. 1996).
  • Mw of chitosan did not influence toxicity (Schipper, Varum et al. 1996).
  • chitosan has been proven in vitro with myocardial, endothelial and epithelial ceils, fibroblasts, hepatocytes, chondrocytes, and keratinocytes (Aranaz, Mengibar et ai. 2009). This property seems to be related to the DD of the samples. When the positive charge of the polymer increases, the interactions between chitosan and the cells increase too, due to the presence of free amino groups. The adhesion and proliferation of keratinocytes and fibroblasts on several chitosan films with different DDs depend on both, DD and cell type.
  • Impure chitin and chitosan with residual proteins could cause allergic reactions such as hypersensitivity within some individuals.
  • the protein content in a sample depends on the source of the sample and, especially, on the method of preparation.
  • purified chitosan is non-allergenic. While 0.2-0.3 percent of the human population exhibits allergies to marine crustaceans (Osterballe, Hansen et al. 2005; Osterballe, Mortz et al. 2009), the following conclusions were drawn from a respected authority on chitosan, Dr. Riccardo Muzzarelli:
  • the major shrimp allergen has been identified as the muscle protein tropomyosin ...
  • Shrimp-derived glucosamine is safe even for individuals hypersensitive to tropomyosin.
  • Villacis et al. state that glucosamine supplements from various manufacturers to not contain clinically relevant levels of allergens [76].
  • Gray et al. clearly state that "shellfish allergy is caused by IgE antibodies to antigens in the flesh of the shellfish and not the shell; therefore it should be safe for patients with shellfish allergy to take glucosamine supplement" [77].
  • Dr. Muzzarelli states:
  • Chitosan Mw also affects the binding or agglutination of red blood cells (Mi, Shyu et al. 2001; ishihara, Obara et al. 2006; Pang, Chen et al. 2007; Aranaz, Mengibar et al. 2009; Zhang, Xia et al. 2010).
  • a comparative study has been carried out among solid-state chitosan and chitosan acetic acid physiological saline solution (Jian, Feng et al. 2008).
  • Several chitosan samples with Mw from 2000 to 400 kDa and DD from 90 to 70% were tested.
  • chitosan and its salt forms are available for use in controlling hemorrhage (e.g., acidic lyophilized chitosan sponges). These devices are typically applied to the exterior surfaces of wounds as wound dressings or "bandages” (see below re: FDA Approved Devices).
  • chitosan mucoadhesion Several factors affect chitosan mucoadhesion, such as physiological variables and the physicochemical properties of chitosan.
  • the mucus is composed of a glycoprotein called mucin, which is rich in negative charges since it has sialic acid residues.
  • mucin glycoprotein
  • chitosan is positively charged due to the acidic environment and, therefore, it can interact with mucin by electrostatic forces.
  • the extent of this union depends on the amount of sialic acid present in the mucin and on the Mw and DD of chitosan. It has been found that when the Mw of chitosan increases, the penetration in the mucin layer also increases and hence the mucoadhesion is stronger (Lehr, Bouwstra et al. 1992). On the other hand, a higher DD leads to an increase in charge density of the molecule and the adhesive properties become more relevant (He, Davis et al. 1998).
  • chitosan confers considerable antibacterial activity against a broad spectrum of bacteria (No, Park et al. 2002; Jou, Yuan et al. 2007).
  • Aimin et al. (Aimin, Chunlin et al. 1999) has shown that chitosan can reduce the infection rate of experimentally induced osteomyelitis by Staphylococcus aureus in rabbits. This is related to the cationic nature of chitosan by amino groups and to anions on the bacterial ceil wall. The interaction between positively charged chitosan and negatively charged microbial cell wall leads to the leakage of intracellular constituents.
  • Chitosan may inhibit microbial growth by acting as a chelating agent rendering metals, trace elements or essential nutrients unavailable for the organism to grow at the normal rate. Chitosan is also able to interact with flocculate proteins, but this action is highly pH-dependent. In addition, chitosan has antifungal properties. Several authors have proposed that the antimicrobial action of chitosan against filamentous fungi could be explained by a more direct disturbance of membrane function. However, it is not clear whether the antimicrobial activity of chitosan is caused by growth inhibition (fungistatic) or cell death (fungicidal).
  • Chitosan has shown a significant scavenging capacity against different radical species, the results being comparable to those obtained with commercial antioxidants.
  • Samples prepared from crab shell chitin with DD of 90, 75, and 50% where evaluated on the basis of their abilities to scavenge l,l-diphenyl-2-picrylhydrazyi (DPPH), hydroxy!, superoxide, and alkyl radicals.
  • DPPH scavenge l,l-diphenyl-2-picrylhydrazyi
  • chitosan with higher DD exhibited the highest scavenging activity (Park, Je et al. 2004).
  • chitosans of different size as well as their sulfate derivatives were assayed against superoxide and hydroxyl radicals.
  • chitosan Mw A negative correlation was found between chitosan Mw and activity.
  • the chitosan sulfated derivatives presented a stronger scavenging effect on peroxide radicals but the chitosan of lowest Mw showed more considerable ferrous ion-chelating potency than others.
  • the chelation of metal ions is one of the reasons why chitosan may be considered as a potential natural antioxidant. Chitosans may retard lipid oxidation by chelating ferrous ions present in the system, thus eliminating their pro-oxidant activity or their conversion to ferric ion (Peng 1998).
  • Chitosan a natural cationic polysaccharide and salt forms thereof (e.g., -acetate, -lactate, -chloride, -phosphate, etc.) have received considerable attentions as a nontoxic and biodegradable biopolymer for diverse applications, especially in foods, medical devices, cosmetics and hair care products, and pharmaceutics (Johnson and Nichols 2000).
  • a natural cationic polysaccharide and salt forms thereof e.g., -acetate, -lactate, -chloride, -phosphate, etc.
  • chitosan was made available over the counter as a dietary supplement or cholesterol-lowering agent in multiple nutritional supplement products due to its ability to bind fat.
  • Chitosans have been identified as versatile biopolymers of natural origin for food preservation due to their antimicrobial action against food spoilage microorganisms and antioxidant properties.
  • the pH-dependent solubility allows them to be formed into various shapes (e.g., beads, films and membranes) using aqueous processing. Beads and particles have been described for use in resins, fillers, absorbants, adsorbants, and insulation (Smith 1994)(Unger and Rohrbach 1996).
  • the use of chitosan coating as a protective barrier to extend the storability of many fruits and vegetabl es has been widely documented.
  • chitosan Due to its biological properties, chitosan has been employed in research and/or commercial products in wound healing management (e.g., wound dressings and "bandages"), implantable device systems such as orthopedic and periodontal composites, scaffolds for tissue regeneration, and drug- and DNA-delivery systems.
  • wound healing management e.g., wound dressings and "bandages”
  • implantable device systems such as orthopedic and periodontal composites, scaffolds for tissue regeneration, and drug- and DNA-delivery systems.
  • Chitosan as a biodegradable natural biopolymer, has served as a biocompatible wound dressing for many years.
  • Chitosan-based materials are highly biocompatible without toxicity and with only an early, mild, macrophage-dominated inflammatory response.
  • the unique chemical and biological properties, biodegradation characteristics, and biocompatibiiity of chitosan make it attractive in biomedical applications.
  • Chitosan-containing products are currently available on the medical market, typically as US FDA Class I medical device wound dressings or "bandages" to promote wound healing. Chitosan-based products have been used perhaps even more extensively internationally than in the United States.
  • FDA Approved Devices Purified chitosan is a component in multiple US FDA- approved Class I medical and dental devices, and in most cases as the principal component. It has been used in various finished product forms, such as granules, a film component of bandages and gauze, and a lyophilized "sponge". Examples of FDA 510(k) Premarket Notification cleared Class I products include HemCon Bandage, HemCon Dental Dressing, HemoHalt Hemostasis Pad Wound Dressing, Aquanova Super- Absorbent Dressing, CELOX Topical Hemostatic Granules in Soluble Bag, and ChitoGauze.
  • Chitosan is considered as Generally Accepted as Safe (GRAS) as a food additive at the level of "self-affirmed” by various manufacturers of chitosan (e.g., Primex). To the best of our knowledge, a GRAS designation at the higher level of "no comment" following a full FDA review has not yet occurred. Chitosan is considered by the scientific community to be safe for use in foods, albeit with one caveat— ingested chitosan has affinity for dietary lipids and can reduce lipid uptake from the gastrointestinal tract.
  • GRAS Generally Accepted as Safe
  • Tissue engineering is a multidisciplinary science, including fundamental principles from materials engineering and molecular/cellular biology in efforts to develop biological substitutes for failing tissues and organs.
  • tissue engineering seeks to fabricate living replacement parts for the body.
  • Langer and Vacanti (Langer and Vacanti 1993) reported that the most common approach for engineering biological substitutes is based on living cells, signal molecules, and polymer scaffolds.
  • the cells synthesize matrices of new tissue as well as function on behalf of the diseased or damaged tissues, while the scaffold provides the suitable environment for the ceils to be able to effectively accomplish their missions such as adherence, proliferation, and differentiation.
  • the function of the signal molecules is to facilitate and promote the cells to regenerate new tissue.
  • the scaffolds provide not only temporaiy three- dimensional frameworks to form the designed tissues, but also space filling and controlled release of bioactive signal molecules.
  • the scaffold should meet the following requirements: (1) biocompatibility with the tissues, and an environment that promotes cellular adhesion, (2) biodegradability at the optimal rate corresponding to the rate of new tissue formation, (3) nontoxicity and non-immunogenicity, (4) optimal mechanical properties, and (5) adequate porosity and morphology for transporting of gases, metabolites, nutrients and signal molecules both within the scaffold and between the scaffold and the local environment,
  • Chitosan is one of the most promising biomaterials in tissue engineering because it offers a distinct set of advantageous physico-chemical and biological properties that qualify them for tissue regeneration in various kinds of organs such as skin, bone, cartilage, liver, nerve and blood vessel.
  • Recent studies in regenerative tissue engineering suggest the use of scaffolds to support and organize damaged tissue because three-dimensional matrices provide a more favorable ambient for cellular behavior. Due to their low immunogenic activity, controlled biodegradability and porous structure, chitosan scaffolds are promising materials for the design of tissue engineered systems.
  • the degradability of a scaffold plays a crucial role on the long-term performance of tissue-engineered cell/material constructs because it affects many cellular processes, including ceil growth, tissue regeneration, and host response. If a scaffold is used for tissue engineering of the skeletal system, degradation of the scaffold biomaterial should be relatively slow, as it has to maintain the mechanical strength until tissue regeneration is completed or nearly so. The degradation rate also inherently affects both the mechanical and solubility properties over time.
  • Min et al. Min, Lee et ai. 2004
  • Min etin and chitosan nano fibers with an average diameter of 110 nm and their diameters ranged from 40 to 640 nm by the SEM image analysis.
  • Bhattarai et al. Bhattarai et al. (Bhattarai, Edmondson et al. 2005) further concluded that these chitosan-based nanofibers promoted the adhesion of chondrocyte and osteoblast cells and maintained characteristic cell morphology.
  • Chitin and chitosan activate immunocytes and inflammatory ceils (e.g., PMNs and macrophages), fibroblasts and angio-endothelial cells. These effects are related to the DD of the samples, chitin presenting a weaker effect than chitosan.
  • Okamoto and coworkers reported that chitosan influenced ail stages of wound repair in experimental animal models (Okamoto, Shibazaki et al. 1995). In the inflammatory phase, chitosan has unique hemostatic properties that are independent of the normal clotting cascades.
  • these polymers can also stimulate the proliferation of fibroblasts and modulate the migration behavior of neutrophils and macrophages modifying subsequent repair processes such as fibroplasias and re-epitheiialization (Okamoto, Shibazaki et al. 1995; Kosaka, aneko et al. 1996).
  • Kosaka et al. reported that the cell binding and cell-activating properties of chitosan play a crucial role in its potential actions.
  • Chitosan oligomers have also exhibited wound-healing properties (Minagawa, Okamura et al. 2007). It is suggested that their wound-healing properties are due to their ability to stimulate fibroblast production by affecting the fibroblast growth factor. Subsequent collagen production further facilitates the formation of connective tissue (Howling, Dettmar et al. 2001).
  • chitin oligosaccharides in wound healing as well as their capacity against chronic bowel disease has been studied (Deters, Petereit et al. 2008).
  • the wound healing effect of chitosan oligomers and monomers is of great interest because in vivo lysozyme degrades chitosan polymer to these smaller molecules.
  • Chitosan-based implants have been found to evoke a minimal foreign body reaction, with little or no fibrous encapsulation. The typical course of healing is with formation of normal granulation tissue, often with accelerated angiogenesis. Chitosan possesses the properties favorable for promoting rapid dermal regeneration and accelerating wound healing suitable for applications extending from simple wound dressings to sophisticated artificial skin matrices. During the course of chitosan implant degradation by maerophage-like cells, the chitosan has been reported to stimulate an anti-inflammatory cytokine cascade (Cheilat, Grandjean- Laquerriere et a!, 2005).
  • the transepidermal water loss (TEWL) rate for normal skin is 204 g/m 2 per day, while that for injured skin with a compromised stratum corneum and epidermis can range from 279 g/m 2 per day for a "first-degree" burn to 5138 g/m" per day for a granulating wound lacking the epidermis.
  • the water vapor permeability of a wound dressing should prevent both excessive dehydration as well as buildup of exudate. It was recommended that a rate of 2500 g/m 2 per day, which being in the mid-range of loss rates from injured skin, would provide an adequate level of moisture without risking wound dehydration.
  • the water loss data for fabricated asymmetric chitosan membranes ranged from 2109 to 2792 g/m per day depending on the per-evaporation time before membrane casting (Mi, Shyu et al. 2001).
  • the high porosity of the sponge-like sublayer increases the adsorption of water vapor and the decreased thickness of dense skin layer increases the diffusion of water molecule, thus resulting in the increased water vapor transmission rate.
  • chitosans An important application of chitosans in industry is the development of drag delivery systems such as nanoparticles, hydrogels, microspheres, films and tablets. As a result of its cationic character, chitosan is able to react w r ith polyanions giving rise to polyelectrolyte complexes. Pharmaceutical applications include nasal, ocular, oral, vaginal, parenteral, and transdermal drug delivery. Three main characteristics of chitosan to be considered are: Mw, DD, and purity. When chitosan chains become shorter (low Mw chitosan), they can be dissolved directly in water, which is particularly useful for specific biomedical applications, when pH should stay at around 7.0, or slightly lower (ca. 5.5-6.5) for dermatologic or consumer skincare applications.
  • chitosan In drug delivery, the selection of an ideal type of chitosan with certain characteristics is useful for developing sustained drug deliver ⁇ ' systems, prolonging the duration of drug activity. improving therapeutic efficiency and reducing side effects.
  • the phvsicochemical characteristics of chitosan are important for the selection of the appropriate chitosan as a material for drug delivery vehicles.
  • the DD controls the degree of crystallinity and hydrophobicity in chitosan due to variations in hydrophobic interactions which control the loading and release characteristics of chitosan matrices (Draget 1996). Zhang et al. also reported that a high chitosan DD and narrow polymer Mvv distribution were shown to be critical for the control of particle size distribution (Zhang, Oh et al. 2004).
  • the amount of drug released is similar for films that contained low and medium Mw chitosan, but lower for the ones prepared with high Mw chitosan. This behavior is predictable, taking into account the direct relationship between the molar mass of chitosan and the viscosity of its solution. By increasing the viscosity of the polymer, the diffusion of the drug through the formed gel layer into the release medium was retarded (Ei-Kamel, Ashri et al. 2007).
  • chitosan Due to its positive charge, chitosan has the ability to interact with negatively charged molecules such as DNA. This property was used for the first time in 1995 to prepare a non- viral vector for a gene delivery system (MacLaughlm, Mumper et al. 1998). The use of chitosan as non-viral vector for gene delivery offers several advantages compared to viral vectors. Mainly, chitosan does not produce endogenous recombination, oncogenic effects and only mild immunological reactions. Moreover, chitosan/plasmid DNA complexes can be easily prepared at low cost.
  • the Mw of chitosan is a key parameter in the preparation of chitosan/DNA complexes since transfection efficiency correlates strongly with chitosan Mw.
  • High molecular weight chitosan renders very stable complexes but the transfection efficiency is very low.
  • recent studies have examined the use of low Mw chitosans and oligomers in gene deliver ⁇ ' vectors. It appears that a fine balance must be achieved between extracellular DNA protection (better with high Mw) versus efficient intracellular unpackaging (better with low Mw) in order to obtain high levels of transfection.
  • Lavertu et al. studied several combinations of Mw and DD of chitosan finding two combinations of high transfection efficiency using a chitosan of 10 kDa and DD of 92 and 80%, respectively (Lavertu, Methot et al. 2006).
  • Kiang et al. studied the effect of the degree of chitosan deacetyiation on the efficiency of gene transfection in chitosan-DNA nanoparticles (Kiang, Wen et al. 2004). Highly deacetylated chitosan (above 80%) releases DNA very slowly. They suggest that the use of chitosan with a DD below 80% may facilitate the release of DNA since it lowers the charge density, may increase steric hindrance in complexing with DNA, and is known to accelerate degradation rate. They reported an increase in luciferase reporter gene expression when the DD was decreased from 90% to 70%. Formulations with 62% and 70% deacetyiation led to luciferase transgenic expression two orders of magnitude higher than chitosan with 90% deacetyiation.
  • a chitosan membranes or films is as a barrier membrane to separate tissue layers during surgery.
  • Three methods are typically used to produce membrane- like or film-like chitosan structures of low to high density. These preparation methods are solvent casting, phase separation, and immersion-precipitation phase inversion (Madihally and Matthew 1999; Hong, Wei et al. 2007).
  • chitosan solutions of varying concentrations e.g., 2-4% w/v
  • chitosan solutions of varying concentrations (e.g., 2-4% w/v) are prepared by dissolving the appropriate amount of chitosan powder (e.g., 75-90% DD / 400-500 mPas) in a 1% (v/v) acetic acid solution.
  • the chitosan solution is cast into custom silicone mold cavities. At this point the three different methodologies, described below, diverge one from another.
  • the casted acidic chitosan solution is frozen at -20°C overnight and then freeze dried at -40°C at 10 x 10 " ' mBar for 48 hours.
  • the freeze-dried chitosan material is then de-molded and treated with IN NaOH for 4 h to stabilize the chitosan polymer network, repeatedly washed with distilled water and then placed in a 50°C oven for drying.
  • the phase separation method results in a relatively low density porous "sponge" with a pore size that can be controlled (Mi, Shyu et al. 2001) (No et al. 2002).
  • Freezing of a chitosan solution produces two or more distinct phases - typically water freezing into ice with displacement of the chitosan biomaterial into a separate solid phase. Another step is required to remove the frozen solvent (typically ice), and hence produce the low- density porous sponge, which is a form commonly used in wound dressings. This is accomplished without disturbing the fibrous structure by a freeze-drying (i.e., iyophilization) and/or a freeze substitution step.
  • a freeze-drying i.e., iyophilization
  • the casted acidic chitosan solution is simply dried in an oven at 50°C to remove the solvent, leaving a chitosan membrane.
  • the chitosan membranes are treated with IN NaOH for 4 h, repeatedly washed with distilled water to remove any traces of reacting agents and then placed in an oven at 50°C for drying.
  • the solvent on the surface of the polymer solution vaporizes faster than that of the inside, so the concentration of polymer increases quickly to form the layer shaped by means of the colloid particle. After the forming of the surface layer, vaporizing of the solvent slows down.
  • the chitosan solubility is not enough to maintain the system as a homogeneous solution and results in phase separation.
  • Solvent separating from the homogeneous solution forms a polymer-poor phase surrounded by a polymer-rich phase.
  • the exchange of acidic solvent with neutralizing base stabilizes the polymer network.
  • the immersion-precipitation phase inversion (IPPI) method the casted acidic chitosan solution is (partially) dehydrated in an oven at 50°C for 1 hour to form an asymmetric membrane, subsequently the chitosan polymer in the membrane is stabilized by immersion into a 0.2 M NaOH solution for 24 hours. The resulting membrane is then washed repeatedly with deionized water and then freeze-dried for 48 hours.
  • IPPI immersion-precipitation phase inversion
  • chitosan sponges are described in the prior art: (1) for uncompressed lyophilized neutralized sponge (Zhang, Cheng et al. 2006; Seda Tigli, Karakecili et al. 2007; Blan and Birla 2008); and
  • Electrospinning followed by rolling (Yeo, Jeon et al. 2005; Li and Hsieh 2006; Park, Kang et al. 2006). Electrospinning produces thin, neutralized chitosan fibers that can be blended together in a layered web product. Electrospinning technology does not apply to the present invention described herein.
  • Chitosan structures can be strengthened by cross-linking chemically with or without the requirement for light activation (Masuoka, Ishihara et al. 2005; Obara, Ishihara et al. 2005).
  • cross-linking methods can increase the density of chitosan to the high- density range of the present invention described herein.
  • Asymmetric air-drying increases the density of a chitosan solution by evaporation of acidic solvent from the exposed surface of the chitosan solution. As the solvent is removed, the density of the chitosan on the exposed surface increases.
  • This method of increasing chitosan density can result in a dense, membrane-like chitosan device.
  • a particular problem with this method is the uneven nature of surface evaporation of a solution within a mold, and the limited density that can be achieved without compression.
  • An additional problem with manufacturing dense chitosan membrane structures by the use of air drying alone is that swelling of the dried membrane upon wetting is excessive and clinically problematic for materials intended as dense and thin barrier membranes. Therefore, unlike the prior art, the present invention describes a novel method of creating a high-density membrane-like chitosan material that circumvents current problems.
  • Chitosan prepared as described in the prior art can result in a film, membrane, or sponge that is of insufficient density or other physical properties for medical use.
  • chitosan prepared with a density ⁇ 0.6 mg/cm' has insufficient strength to reliably support robust suturing and handling during surgical placement.
  • This high-density chitosan film or membrane provides the necessary strength and handling qualities to be reliably applied in the clinic.
  • the high-density chitosan films or membranes of the present invention have excellent tensile strength, suture retention (i.e., reistance to suture pull-out), elasticity, suitable thickness, and shape memory (i.e., conformability) for use in the medical fields, yet with limited swelling upon rehydration.
  • the most common include compression of a lyophilized chitosan sponge. While the lyophilized chitosan scaffold can be compressed to a high density using sufficient pressure, the limitation of this common procedure is that the compressed lyophilized scaffold retains shape memory upon rewetting and recoils excessively to a clinically unacceptable thickness as a membrane. Limiting the recoil thickness after wetting and maintaining sufficient density in a membranous structure is not possible by this method of compressing a lyophilized sponge, and therefore not suitable for creating a dense membrane with enough strength for clinical handling and suturing.
  • the present invention describes a new method of creating a dense chitosan membrane of approximately 0.6-1.6 g/cm 3 that is less than 2 mm thick and the invention eliminates the common step of sponge fabrication prior to compression.
  • the essence of the present invention is the making and use of a membranous chitosan material that is denser than a lyophilized chitosan sponge with additional properties such as adequate tensile strength, suture retention (i.e., resistance to suture pull-out), elasticity, and sufficient shape memory (i.e., conformability), yet with limited swelling upon rehydration that is distinct from previously described chitosan materials.
  • the present invention does not restrict the source of chitin or chitosan from natural, semi-synthetic, or synthetic sources.
  • the key steps of producing the present invention are:
  • a strong base familiar to those practiced in the science of chemistry preferably sodium hydroxide of 1-2 molarity, is preferred to polymerize the frozen chitosan suspension from the outside of the frozen chitosan suspension towards the inside before chitosan is lost from the surface and the uniform chitosan structure is altered.
  • Dehydration is preferably performed after exchanging the strong base within the solidified chitosan gel with an aqueous buffer or water. Dehydration is preferably performed under vacuum in the presence of heat. Dehydration is preferably performed by loss of the solvent phase (e.g., water, aqueous buffer) through a semipermeable membrane (e.g., Cellophane or a similar cellulosic material), while under vacuum in the presence of heat. Compression is preferably with a minimal linear pressure of 25 inches of Hg dispersed evenly over the chitosan gel.
  • solvent phase e.g., water, aqueous buffer
  • a semipermeable membrane e.g., Cellophane or a similar cellulosic material
  • An important unique aspect of the present invention is combining the processes of compression and dehydration so that dehydration of the gel occurs during compression.
  • Another unique aspect of the invention is the neutral or alkaline pH of the gel during dehydration.
  • a novel chitosan structure having a density of greater than 0.6g/cm 3 methods of making the composition, and methods of using the composition for the medical uses described in the background of this document.
  • the method of making the chitosan structure can be characterized by the following three sequential steps:
  • the resulting high-density chitosan film or membrane composition has a density greater than 0.6 g/cm 3 , and more preferably greater than 0.8 g/cnr ⁇
  • the chitosan starting material used in the acidic solution is approximately 70-95% DD.
  • the present invention also allows for DD from 56%-99%.
  • the chitosan is present as chitosan base.
  • the chitosan may be present as a salt such as chitosan acetate, chitosan succinate, chitosan adipate, chitosan chloride, chitosan glutamate, chitosan lactate, chitosan aspartate, chitosan pyruvate, chitosan phosphate, chitosan glycolate, chitosan ascorbate, chitosan salicylate, chitosan formate, or chitosan malate.
  • a salt such as chitosan acetate, chitosan succinate, chitosan adipate, chitosan chloride, chitosan glutamate, chitosan lactate, chitosan aspartate, chitosan pyruvate, chitosan phosphate, chitosan glycolate,
  • the chitosan starting material has an average viscosity of approximately 400-500 Centipoise (CPS) or Millipascai (mPas).
  • CPS Centipoise
  • mPas Millipascai
  • the present invention contemplates chitosan starting material viscosities from about 5 to 3000 mPas.
  • the chitosan is soiubilized in 1% acetic acid.
  • the present invention considers acidic solvents other than acetic acid and solvent percentage ranging from 0.1 %- 10%.
  • acidic solvents other than acetic acid and solvent percentage ranging from 0.1 %- 10%.
  • an appropriate organic acid with pH less than 5.0 such as formic, giycolic, citric, or lactic acid would also be suitable.
  • Other suitable acids include hydrochloric acid, glutamic acid, aspartic acid, ascorbic acid, pyruvic acid, malic acid, maleic acid, fumaric acid, glucuronic acid, sorbic acid, and folic acid.
  • the chitosan concentration in the solution is 2-4%.
  • the present invention contemplates chitosan concentrations of 0.1% to 25%.
  • the chitosan is solubilized in acidic solvent for 7 days prior to forming a neutralized chitosan gel (either with or without a freezing step prior to neutralization).
  • the present invention considers chitosan solutions prepared immediately, or up to 2 years prior to forming the neutralized chitosan gel (either with or without a freezing step prior to neutralization).
  • the chitosan solution is poured into a form or mold in an amount at a thickness of approximately 0.3-0.5 g chitosan solution per square cm of the form or mold area.
  • the present invention contemplates chitosan solution amounts as low as 0.1 g/cm2 or as high as 10 g/cm2 within the mold or form prior to freezing.
  • the chitosan solution is allowed to degas by applying vibration to the solution through the mold or form. Vibration time is preferably 10 minutes. However, the present invention contemplates vibration times from 1 second to 10 days. In an alternative embodiment, the present invention contemplates degassing the chitosan solution using an applied vacuum.
  • the chitosan solution is frozen in the moid or form to become a solidified chitosan suspension.
  • the chitosan solution is frozen at approximately -80°C for lh.
  • the chitosan solution is frozen at approximately -20°C for 16h.
  • the present invention contemplates freezing of the chitosan solution at temperatures ranging from 0°C to -276°C for times ranging from 1 minute to 365 days, sufficient to freeze the chitosan solution.
  • the present invention also contemplates the possibility of not freezing the chitosan solution at this stage of the process.
  • the solidified (if frozen) chitosan suspension is de-molded (removed from the mold) while solid and subsequently immersed in a base, such as 1 -2M sodium hydroxide, while solid, for 24 h to completely neutralize the acidic solvent within the solidified chitosan suspension, producing a polymerized gel.
  • a base such as 1 -2M sodium hydroxide
  • the present invention contemplates any one of several bases known to those practiced in the science of chemistry, such as sodium hydroxide or potassium hydroxide, having a strength ranging from 0.1 M to 10M, with an immersion period ranging from 1 minute to 3 months.
  • Alternative hydroxides may be used, and they include calcium hydroxide and magnesium hydroxide.
  • the neutralized chitosan gel with a basic pH is washed for 24h in deionized or distilled H 2 0 or aqueous buffer solution to remove the basic solution to become pH neutral or substantially neutral (e.g. pH 5-11, 5-9 or 5.5-7.5).
  • the present invention contemplates a washing period from 1 minute to 3 months.
  • the present invention also contemplates using continuous flow of deionized or distilled H 2 0 or aqueous buffer solution during this rinsing step.
  • the present invention also contemplates not washing the neutralized chitosan gel at all.
  • the liquid is removed from the neutralized chitosan gel while concurrently compressing the chitosan.
  • Dehydration is preferably performed with the use of a vacuum and heat.
  • Compression is preferably performed with a minimal linear pressure of 25 inches of Hg and is preferably dispersed evenly over the chitosan gel to obtain a uniform membrane.
  • compression is contemplated using a minimal linear pressure of 5-500, 10 to 100, or 20 to 50 inches of Hg.
  • Dehydration and compression are preferably performed at a temperature of 80°C.
  • the present invention contemplates dehydrating and compressing the chitosan gel at temperatures ranging from 2°C to 150°C, 40° to 120° C, or 50° to 100°C.
  • dehydration and physical compression can occur in the presence of a vacuum, either by itself or with added heat, in a process known as outgassing.
  • the vacuum applied is preferably less than atmospheric pressure, and as low as 0.6, 0.4 or 0.2 atmospheres.
  • Dehydration and compression are preferably performed for a period of 4 hours.
  • the present invention contemplates the performance of dehydration and compression for periods of time ranging from 1 minute to 3 months.
  • the neutralized chitosan gel is placed on or inside a semi-permeable membrane, prior to application of vacuum dehydration.
  • the semipermeable membrane subsequently facilitates loss of water vapor under vacuum, while preserving the integrity of the dehydrating and dehydrated polymeric chitosan.
  • the semipermeable membrane is selectively permeable for water, while retaining the molded chitosan gel within the margins or boundaries of the semi-permeable membrane, and may be a Cellophane or other cellulosic membrane or another material.
  • the dehydrated high-density chitosan film or membrane may be subsequently removed from the semi-permeable membrane used during the dehydration process.
  • the neutralized and polymerized chitosan gel is immersed in a glycerol solution for a period of time ranging from 1 second to 10 days, then placed on or inside a semi-permeable membrane for vacuum dehydration.
  • the glycerol solution contains approximately 5% to 20% or 10% glycerol in water or in aqueous buffer.
  • the present invention may use glycerol concentrations ranging from 1% to 50% during this process.
  • the resulting chitosan structure preferably takes the form of a film or membrane having a thickness less than 10 mm, 5 mm, 2 mm, 1 mm, or even 0.5 mm.
  • the density of the structure preferably exceeds 0.6 g/cm 3 , and may be up to 1.6 g/cm 3 . In another preferred embodiment the density of the structure exceeds 0.8 g/cm 3 , and may be up to 1.6 g/cm 3 .
  • the film or membrane can also be characterized by its pH, which preferably ranges from 5.0 to 9.5.
  • the film or membrane can be chopped up or ground and used as particulates, but is preferably used as a film or membrane due to its excellent physical properties (e.g., tensile strength, elasticity, and resistance to suture pull-out).
  • the chitosan film or membrane of this invention does not require a chemical or light-induced cross-linking step, and yet attains a dehydrated density of > 0.6 g/cm 3 and more preferably > 0.8 g/cnr'.
  • a chemical or light-induced cross-linking step might provide some benefit(s), such as reduced biodegradation potential.
  • the resulting dense chitosan structures of the present invention have physical properties that are beneficial for use in biomedical procedures in an animal, mammal, or human, such as surgically implanted films or membranes.
  • the dense chitosan materials demonstrate excellent physical characteristics. ASTM International standard methods have been established for the evaluation of these physical parameters for thin films or membranes (ASTM 2002; ASTM 2006).
  • the present invention discloses a composition comprising chitosan in a film or membrane having a density greater than 0.6 g/cm 3 , and more preferably greater than 0.8 g/cm J .
  • the chitosan composition has a pH of from 5.0 to 9.5.
  • the chitosan composition includes glycerol.
  • the invention provides methods of treatment using the structures of the present invention, and can thus be defined as a method of treatment comprising: providing a chitosan composition having a density greater than 0.6 g/cm 3 ; and placing said composition on or within an animal.
  • the animal is a mammal or human
  • the structure is hydrated in water or a buffered aqueous solution and in the presence or absence of one or more compounds selected from a pharmaceutical, a biologic agent, a nucleic acid, a vaccine, an immune effector, or a salt thereof prior to use.
  • the chitosan composition serves as a physical barrier film or membrane to separate tissue layers within an animal.
  • the film or membrane on or within the animal, mammal, or human resorbs over time, and the rate thereof is in part dependent upon the DD and thickness of the material.
  • the chitosan composition serves as an anti-infective physical barrier film or membrane on or within an animal.
  • the chitosan film or membrane is permeable to small molecules in w r ater or aqueous solution.
  • the physical properties e.g., tensile strength, elasticity, and resistance to suture pull-out
  • clinical handling characteristics e.g., wet-ability, conformability to surgical implant sites, and suture-ability
  • ultra- freezing a chitosan solution of approximately 0.3-0.5 g/cm 2 in the moid at -80 °C for an hour ultimately results in polymerization of the chitosan on the exposed top surface with a woven, fibrillar, porous, structure at that surface when examined by microscopy or scanning electron microscopy.
  • the resulting dehydrated film or membrane has an overall density > 0.6 g/cm 3 and more preferably > 0.8 g/cm 3 and is somewhat asymmetric, with a smoother, less fibrillar surface on the alternate, bottom, side.
  • ultra- freezing at -80 °C for significantly more than an hour can result in physical cracking of the frozen chitosan gel and of the final membrane structure.
  • the freezing of the chitosan solution within the mold at -20 °C prior to neutralization reduces the extent of woven structure of the final membrane structure. Regardless of freezing temperature, the resulting membrane has a density > 0.6 g/cm 3 .
  • the resulting compressed and dehydrated membrane In the absence of freezing the chitosan solution prior to neutralization, the resulting compressed and dehydrated membrane has no visible woven, fibrillar structure. Regardless of freezing or lack thereof, the resulting membrane has a density > 0.6 g/cm J .
  • chitosan films or membranes with high density living mammalian cells were seeded and maintained on the membranes for at least 3 days in culture. Cell binding and cell compatibility were observed on both sides of the membrane. Evidence of proliferation and cell migration were also demonstrated. Keratinocyte migration was most evident on the smoother surface (i.e., bottom side while in the mold) relative to the more porous surface (i.e., top side while in the mold) as measured by microscopic image analysis. These results provide evidence of in vitro biocompatibility.
  • the soft tissue can facilitate differential rates of healing on the opposite sides of the film or membrane.
  • the rates of resorption in vivo are similarly anticipated to be dependent upon the percentage of DD and/or thickness of dense chitosan films or membranes.
  • the rates of degradation can be "controlled" at least in part by varying the percentage of DD and/or thickness.
  • the dense chitosan films or membranes of the present invention when tested with an array of experimental variables from production batch to batch (e.g., amount of starting chitosan solution, dry membrane thicknesses of less than 1 mm and typically 0.2 to 0.6 mm, percentage of DD from 70% to 95%, source materials from different vendors, post-drying process modifications if any, etc.) yield in tests using an Instron machine the following typical ranges of physical properties: (a) maximum tensile load of approximately 2 to 14 N ( ⁇ 2.5 mm minimum width); (b) maximum tensile stress of approximately 20 to 140 MPa ( ⁇ 2.5 mm minimum width); and (c) suture pull-out maximum load of approximately 0.5 to 4.5 N ( ⁇ 5 mm width).
  • an array of experimental variables from production batch to batch e.g., amount of starting chitosan solution, dry membrane thicknesses of less than 1 mm and typically 0.2 to 0.6 mm, percentage of DD from 70% to 95%, source materials from different vendors, post-drying
  • the resulting film or membrane has high density similar to film or membrane produced without this glycerol solution step, and with beneficial high tensile strength, resistance to suture pull-out, and handling characteristics, for instance flexibility and ease of cutting.
  • This combination of attributes i.e., physical properties and clinical handling characteristics
  • N-Acetyl-D-glucosamine oligosaccharides induce mucin secretion from colonic tissue and induce differentiation of human keratinocytes.

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Abstract

L'invention concerne une composition de chitosan exceptionnellement dense et un nouveau procédé pour la production de la structure de chitosan dense. Le nouveau procédé de production utilise la compression coïncidant et le vide sur un polymère de chitosan neutralisé qui conduit à un matériau de film ou de membrane de chitosan exceptionnellement dense. La composition de film ou de membrane de chitosan dense possède de multiples qualités physiques et attrayantes cliniquement pour une variété d'applications médicales sur ou dans les animaux, les mammifères ou les humains.
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