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US20020082220A1 - Composition and method for the repair and regeneration of cartilage and other tissues - Google Patents

Composition and method for the repair and regeneration of cartilage and other tissues Download PDF

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Publication number
US20020082220A1
US20020082220A1 US09/896,912 US89691201A US2002082220A1 US 20020082220 A1 US20020082220 A1 US 20020082220A1 US 89691201 A US89691201 A US 89691201A US 2002082220 A1 US2002082220 A1 US 2002082220A1
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United States
Prior art keywords
blood
polymer composition
chitosan
tissue
blood component
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Abandoned
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US09/896,912
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English (en)
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Caroline Hoemann
Michael Buschmann
Marc McKee
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POLYVALOR
McGill University
Biosyntech Canada Inc
Ecole Polytechnique
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Individual
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Priority to US09/896,912 priority Critical patent/US20020082220A1/en
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Publication of US20020082220A1 publication Critical patent/US20020082220A1/en
Assigned to BIO SYNTECH CANADA INC. reassignment BIO SYNTECH CANADA INC. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: HOEMANN, CAROLINE D.
Assigned to BIO SYNTECH CANADA INC. reassignment BIO SYNTECH CANADA INC. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: MCGILL UNIVERSITY
Assigned to ECOLE POLYTECHNIQUE reassignment ECOLE POLYTECHNIQUE ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: BUSCHMANN, MICHAEL
Assigned to MCGILL UNIVERSITY reassignment MCGILL UNIVERSITY ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: MCKEE, MARC D.
Assigned to BIO SYNTECH CANADA INC. reassignment BIO SYNTECH CANADA INC. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: POLYVALOR
Assigned to POLYVALOR reassignment POLYVALOR ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: ECOLE POLYTECHNIQUE
Priority to US11/031,325 priority patent/US7148209B2/en
Priority to US11/584,870 priority patent/US20070037737A1/en
Priority to US12/901,293 priority patent/US8258117B2/en
Assigned to PIRAMAL HEALTHCARE (CANADA) LTD. reassignment PIRAMAL HEALTHCARE (CANADA) LTD. ASSET PURCHASE AGREEMENT Assignors: BIO SYNTECH CANADA INC., BIOSYNTECH, INC.
Assigned to PIRAMAL HEALTHCARE (CANADA) LTS. reassignment PIRAMAL HEALTHCARE (CANADA) LTS. CORRECTIVE TO CORRECT INCORRECT APPLICATION NUMBERS RECORDED ON 10/26/201 REEL/FRAME 025192/0144 INCLUDING 60/733,173; 12/092,498; 61/032,610; 61/262,805; 61/262,808; 61/262,786; 61/262,758; 61/262,792; 12/092,498; 12/919,889. Assignors: BIOSYNTEC CANADA INC.
Abandoned legal-status Critical Current

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Definitions

  • the invention relates to a composition and method of application to improve the repair and to regenerate cartilaginous tissues and other tissues including without limitation meniscus, ligament, tendon, bone, skin, cornea, periodontal tissues, abscesses, resected tumors, and ulcers.
  • Cartilage Structure, Function, Development, Pathology
  • Articular cartilage covers the ends of bones in diarthroidial joints in order to distribute the forces of locomotion to underlying bone structures while simultaneously providing nearly frictionless articulating interfaces. These properties are furnished by the extracellular matrix composed of collagen types II and other minor collagen components and a high content of the proteoglycan aggrecan. In general, the fibrillar collagenous network resists tensile and shear forces while the highly charged aggrecan resists compression and interstitial fluid flow.
  • the low friction properties are the result of a special molecular composition of the articular surface and of the synovial fluid as well as exudation of interstitial fluid during loading onto the articular surface (Ateshian, 1997; Higaki et al., 1997; Schwartz and Hills, 1998).
  • Articular cartilage is formed during the development of long bones following the condensation of prechondrocytic mesenchymal cells and induction of a phenotype switch from predominantly collagen type I to collagen type II and aggrecan (Hall, 1983; Pechak et al., 1986). Bone is formed from cartilage when chondrocytes hypertrophy and switch to type X collagen expression, accompanied by blood vessel invasion, matrix calcification, the appearance of osteoblasts and bone matrix production. In the adult, a thin layer of articular cartilage remains on the ends of bones and is sustained by chondrocytes through synthesis, assembly and turnover of extracellular matrix (Kuettner, 1992).
  • Articular cartilage disease arises when fractures occur due to physical trauma or when a more gradual erosion, as is characteristic of many forms of arthritis, exposes subchondral bone to create symptomatic joint pain (McCarty and Koopman, 1993).
  • cartilaginous tissues remain in the adult at several body sites such as the ears and nose, areas that are often subject to reconstructive surgery.
  • Articular cartilage has a limited response to injury in the adult mainly due to a lack of vascularisation and the presence of a dense proteoglycan rich extracellular matrix (Newman, 1998; Buckwalter and Mankin, 1997; Minas and Nehrer, 1997).
  • the former inhibits the appearance of inflammatory and pluripotential repair cells, while the latter emprisons resident chondrocytes in a matrix non-conducive to migration.
  • lesions that penetrate the subchondral bone create a conduit to the highly vascular bone allowing for the formation of a fibrin clot that traps cells of bone and marrow origin in the lesion leading to a granulation tissue.
  • the deeper portions of the granulation tissue reconstitute the subchondral bone plate while the upper portion transforms into a fibrocartilagenous repair tissue.
  • This tissue can temporarily possess the histological appearance of hyaline cartilage although not its mechanical properties (Wei et al., 1997) and is therefore unable to withstand the local mechanical environment leading to the appearance of degeneration before the end of the first year post-injury.
  • the natural response to repair in adult articular cartilage is that partial thickness lesions have no repair response (other than cartilage flow and localized chondrocyte cloning) while full-thickness lesions with bone penetration display a limited and failed response.
  • the bone marrow-stimulation techniques of shaving, debridement, drilling, fracturing and abrasion athroplasty permit temporary relief from symptoms but produce a sub-functional fibrocartilagenous tissue that is eventually degraded.
  • Pharmacological modulation supplying growth factors to defect sites can augment natural repair but to date insufficiently so (Hunziker and Rosenberg, 1996; Sellers et al., 1997). Allograft and autograft osteochondral tissue transplants containing viable chondrocytes can effect a more successful repair but suffer from severe donor limitations (Mahomed et al., 1992; Outerbridge et al., 1995).
  • the family of bone marrow-stimulation techniques include debridement, shaving, drilling, microfracturing and abrasion arthroplasty. They are currently used extensively in orthopaedic clinical practice for the treatment of focal lesions of articular cartilage that are full-thickness, i.e. reaching the subchondral bone, and are limited in size, typically less than 3cm 2 in area. Use of these procedures was initiated by Pridie and others (Pridie, 1959; Insall, 1967; DePalma et al., 1966) who reasoned that a blood clot could be formed in the region of an articular cartilage lesion by violating the cartilage/bone interface to induce bleeding from the bone into the cartilage defect that is avascular.
  • Abrasion arthroplasty uses motorised instruments to grind away abnormally dense subchondral bone to reach a blood supply in the softer deeper bone.
  • the microfracture technique uses a pick, or an awl, to pierce the subchondral bone plate deep enough (typically 3-4 mm), again to reach a vascular supply and create a blood clot inside the cartilage lesion.
  • Practitioners of the microfracture technique claim to observe a higher success rate than drilling due to the lack of any heat-induced necrosis and less biomechanical destabilisation of the subchondral bone plate with numerous smaller fracture holes rather than large gaps in the plate producing by drilling (Steadman et al., 1998).
  • Yet another related technique for treating focal lesions of articular cartilage is mosaicplasty or osteochondral autograft transplantation (OATS) where cartilage/bone cylinders are transferred from a peripheral “unused” region of a joint to the highly loaded region containing the cartilage lesion (Hangody et al., 1997).
  • OATS osteochondral autograft transplantation
  • Some of the problems associated with forming a good quality blood clot with these procedures are 1) the uncontrolled nature of the bleeding coming from the bone, which never fills up the cartilage lesion entirely 2) platelet mediated clot contraction occurring within minutes of clot formation reduces clot size and could detach it from surrounding cartilage (Cohen et al., 1975) 3) dilution of the bone blood with synovial fluid or circulating arthroscopy fluid and 4) the fibrinolytic or clot dissolving activity of synovial fluid (Mankin, 1974).
  • PHA polylactic acid
  • PGA polyglycolic acid
  • fibrin glues including bone morphogenetic proteins (Sellers et al., 1997; Sellers, 2000; Zhang et al. Patent WO 00/44413, 2000), angiotensin-like peptides (Rodgers and Dizerega, Patent WO 00/02905, 2000), and extracts of bone containing a multiplicity of proteins called bone proteins or BP (Atkinson, Patent WO 00/48550, 2000).
  • the cell transplantation approach possesses some potential advantages over other cartilage repair techniques in that they 1) minimise additional cartilage and bone injury, 2) reduce reliance on donors by ex vivo cell production, 3) could mimic natural biological processes of cartilage development, and 4) may provide tailored cell types to execute better repair.
  • One technique using autologous chondrocytes is in the public domain and is commercially available having been used in several thousand US and Swedish patients (http.//www.genzyme.com). In this technique chondrocytes are isolated from a cartilage biopsy of a non-load bearing area, proliferated during several weeks, and re-introduced into the cartilage lesion by injection under a sutured and fibrin-sealed periosteal patch harvested from the patient's tibia.
  • Cell transplantation for assisted cartilage repair necessarily involves a technique to deliver and retain viable and functional transplanted cells at the site of injury.
  • press-fitting may be used by preparing an implant that is slightly larger than the defect and forcing it therein (Aston and Bentley 1986; Wakatini et al., 1989; Freed et al., 1994; Chu et al., 1997; Frankel et al., 1997; Kawamura et al., 1998).
  • Press-fitting necessitates the use of a tissue that is formed ex vivo and thus not optimized for the geometric, physical, and biological factors of the site in which it is implanted.
  • Such a technique may benefit from an ability of the periosteum to stimulate cartilage formation (O'Driscoll et al., 1988 and 1994), but suffers again from the introduction of sutures and the complex nature of the operation involving periosteal harvesting and arthrotomy.
  • a desirable cell delivery vehicle would be a polymeric solution loaded with cells which solidifies when injected into the defect site, adheres and fills the defect, and provides a temporary biodegradable scaffold to permit proper cell differentiation and the synthesis and assembly of a dense, mechanically functional articular cartilage extracellular matrix.
  • compositions and methods and modifications thereof conserving the same basic principles, to aid repair of other tissues including meniscus, ligament, tendon, bone, skin, cornea, periodontal tissues, abscesses, resected tumours, and ulcers, are obvious to those who are skilled in the art.
  • Chitosan which primarily results from the alkaline deacetylation of chitin, a natural component of shrimp and crab shells, is a family of linear polysaccharides that contains 1-4 linked glucosamine (predominantly) and N-acetyl-glucosamine monomers (Austin et all. 1981).
  • Chitosan and its amino-substituted derivatives are pH-dependent, bioerodible and biocompatible cationic polymers that have been used in the biomedical industry for wound healing and bone induction (Denuziere et al., 1998; Muzzarelli et al., 1993 and 1994), drug and gene delivery (Carreno-Gomez and Duncan, 1997; Schipper et al., 1997; Lee et al., 1998; Bernkop-Schnurch and Pasta, 1998) and in scaffolds for cell growth and cell encapsulation (Yagi et al, 1997, Eser Elcin et al., 1998; Dillon et al., 1998; Koyano et al., 1998; Sechriest et al, 2000; Lahiji et al 2000; Suh et al., 2000).
  • Chitosan is termed a mucoadhesive polymer (Bernkop-Schnurch and Krajicek, 1998) since it adheres to the mucus layer of the gastrointestinal epithelia via ionic and hydrophobic interactions, thereby facilitating peroral drug delivery.
  • Biodegradability of chitosan occurs via its susceptibility to enzymatic cleavage by chitinases (Fukamizo and Brzezinski, 1997), lysozymes (Sashiwa et al., 1990), cellulases (Yalpani and Pantaleone, 1994), proteases (Terbojevich et al., 1996), and lipases (Muzzarelli et al., 1995).
  • chondrocytes have been shown to be capable of expressing chitotriosidase (Vasios et al., 1999), the human analogue of chitosanase; its physiological role may be in the degradation of hyaluronan, a linear polysaccharide possessing some similarity with chitosan since it is composed of disaccharides of N-acetyl-glucosamine and glucuronic acid.
  • Chitosan has been proposed in various formulations, alone and with other components, to stimulate repair of dermal, corneal and hard tissues in a number of reports (Sall et al., 1987; Bartone and Adickes, 1988; Okamoto et al., 1995; Inui et al., 1995; Shigemasa and Minami, 1996; Ueno et al., 1999; Cho et al., 1999; Stone et al., 2000; Lee et al., 2000) and inventions (Sparkes and Murray, U.S. Pat. No. 4,572,906, 1986; Mosbey, U.S. Pat. No. 4,956,350, 1990; Hansson et al., U.S. Pat. No.
  • chitosan One technical difficulty that chitosan often presents is a low solubility at physiological pH and ionic strength, thereby limiting its use in a solution state.
  • dissolution of chitosan is achieved via the protonation of amine groups in acidic aqueous solutions having a pH ranging from 3.0 to 5.6.
  • Such chitosan solutions remain soluble up to a pH near 6.2 where neutralisation of the amine groups reduces interchain electrostatic repulsion and allows attractive forces of hydrogen bonding, hydrophobic and van der Waals interactions to cause polymer precipitation at a pH near 6.3 to 6.4.
  • a prior invention (Chenite Patent WO 99/07416; Chenite et al., 2000) has taught that admixing a polyol-phosphate dibasic salt (i.e. glycerol-phosphate) to an aqueous solution of chitosan can increase the pH of the solution while avoiding precipitation.
  • a polyol-phosphate dibasic salt i.e. glycerol-phosphate
  • chitosan solutions of substantial concentration (0.5-3%) and high molecular weight (> several hundred kDa) remain liquid, at low or room temperature, for a long period of time with a pH in a physiologically acceptable neutral region between 6.8 and 7.2.
  • This aspect facilitates the mixing of chitosan with cells in a manner that maintains their viability.
  • C/PP chitosan/polyol-phosphate
  • NN-dicarboxylmethyl chitosan sponges have been soaked with BMP7 and placed into osteochondral defects of rabbits (Mattioli-Belmonte, 1999).
  • some improved histochemical and immunohistochemical outcome was observed, however, incomplete filling of the defect with repair tissue and a significant difficulty in retaining the construct within the defect appeared to be insurmountable problems.
  • the present invention overcomes these issues and presents several novel solutions for the delivery of compositions for the repair of cartilage and other tissues.
  • This macromolecular environment or matrix should 1) be amenable to loading with active biological elements (cells, proteins, genes, blood, blood components) in a liquid state 2) then be injectable into the defect site to fill the entire defect or region requiring cartilage growth 3) present a primarily nonproteinaceous environment to limit cell adhesion and cell-mediated contraction of the matrix, both of which induce a fibrocytic cellular phenotype (fibrous tissue producing) rather than chondrocytic cellular phenotype (cartilaginous tissue producing) and which can also disengage the matrix from the walls of the defect 4) be cytocompatible, possessing physiological levels of pH and osmotic pressure and an absence of any cytotoxic elements 5) be degradable but present for a sufficiently long time to allow included biologically active elements to fully reconstitute a cartilaginous tissue capable of supporting mechanical load without degradation
  • active biological elements cells, proteins, genes, blood, blood components
  • One aim of the present invention is to provide a new composition for use in repair and regeneration of cartilaginous tissues.
  • compositions for use in repair, arm regeneration, reconstruction or bulking of tissues of cartilaginous tissues or other tissues such as meniscus, ligament, tendon, bone, skin, cornea, periodontal tissues, abscesses, resected tumors, and ulcers.
  • a polymer solution that can be mixed with biological elements and placed or injected into a body site where the mixture aids the repair, regeneration, reconstruction or bulking of tissues.
  • Repaired tissues include for example without limitation cartilage, meniscus, ligament, tendon, bone, skin, cornea, periodontal tissues, abscesses, resected tumors, and ulcers.
  • the biological elements are preferably based on blood, blood components or isolated cells, both of autologous or non-autologous origin.
  • a method for repairing a tissue of a patient comprising the step of introducing into said tissue a temperature-dependent polymer gel composition such that said composition adhere to the tissue and promote support for cell proliferation for repairing the tissue.
  • the composition preferably comprises at least one blood component.
  • a method for repairing a tissue of a patient comprising the step of introducing a polymer composition in said tissue, said polymer composition being mixable with at least one blood component, said polymer composition when mixed with said blood component results in a mixture, said mixture turning into a non-liquid state in time or upon heating, said mixture being retained at the site of introduction and adhering thereto for repairing the tissue.
  • the polymer can be a modified or natural polysaccharide, such as chitosan, chitin, hyaluronan, glycosaminoglycan, chondroitin sulfate, keratan sulfate, dermatan sulfate, heparin, or heparin sulfate.
  • chitosan such as chitosan, chitin, hyaluronan, glycosaminoglycan, chondroitin sulfate, keratan sulfate, dermatan sulfate, heparin, or heparin sulfate.
  • the polymer composition may comprise a natural, recombinant or synthetic proteinsuch as soluble collagen or soluble gelatin or a polyamino acids, such as for example a polylysine.
  • a natural, recombinant or synthetic protein such as soluble collagen or soluble gelatin or a polyamino acids, such as for example a polylysine.
  • the polymer composition may comprise polylactic acid, polyglycolic acid, a synthetic homo and block copolymers containing carboxylic, amino, sulfonic, phosphonic, phosphenic functionalities with or without additional functionalities such as for example without limitation hydroxyl, thiol, alkoxy, aryloxy, acyloxy, and aroyloxy.
  • the polymer composition is preferably initially dissolved or suspended in a buffer containing inorganic salts such as sodium chloride, potassium calcium, magnesium phosphate, sulfate, and carboxylate.
  • inorganic salts such as sodium chloride, potassium calcium, magnesium phosphate, sulfate, and carboxylate.
  • the polymer composition may be dissolved or suspended in a buffer containing an organic salt such as glycerol-phosphate, fructose phosphate, glucose phosphate, L-Serine phosphate, adenosine phosphate, glucosamine, galactosamine, HEPES, PIPES, and MES.
  • an organic salt such as glycerol-phosphate, fructose phosphate, glucose phosphate, L-Serine phosphate, adenosine phosphate, glucosamine, galactosamine, HEPES, PIPES, and MES.
  • the polymer composition has preferably a pH between 6.5 and 7.9 and an osmolarity adjusted to a physiological value between 250 mOsm/L and 600 mOsm/L.
  • the blood component may be for example without limitation whole blood, processed blood, venous blood, arterial blood, blood from bone, blood from bone-marrow, bone marrow, umbilical cord blood, or placenta blood. It may also comprise erythrocytes, leukocytes, monocytes, platelets, fibrinogen, thrombin or platelet rich plasma free of erythrocytes.
  • the blood component can also comprise an anticoagulant such as citrate, heparin or EDTA.
  • an anticoagulant such as citrate, heparin or EDTA.
  • a pro-coagulant such as thrombin, calcium, collagen, ellagic acid, epinephrine, adenosine diphosphate, tissue factor, a phospholipid, and a coagulation factor like factor VII to improve coagulation/solidification at the site of introduction.
  • the blood component may be autologous or non-autologous.
  • the polymer composition is preferably used in a ratio varying from 1:100 to 100:1 with respect to the blood component.
  • the polymer composition and the blood component are preferably mechanically mixed using sound waves, stirring, vortexing, or multiple passes in syringes.
  • the tissue that can be repaired or regenerated is for example without limitation cartilage, meniscus, ligament, tendon, bone, skin, cornea, periodontal tissue, abscesses, resected tumors, or ulcers.
  • the site of introduction in the body may be surgically prepared to remove abnormal tissues. Such procedure can be done by piercing, abrading or drilling into adjacent tissue regions or vascularized regions to create channels for the polymer composition to migrate into the site requiring repair.
  • a chitosan solution for use n cell delivery to repair or regenerate a tissue in vivo, said chitosan solution comprising 0.5-3% w/v of chitosan and being formulated to be thermogelling, said solution being mixed with cells prior to being injected into a tissue to be repaired or regenerated.
  • the solution may be induced to thermogel by addition of phosphate, glycerol phosphate or glucosamine, just to name a few for example.
  • the chitosan solution has a pH between 6.5 to 7.8.
  • the cells may be selected for example from the group consisting of primary cells, passaged cells, selected cells, platelets, stromal cells, stem cells, and genetically modified cells.
  • a carrier solution such as a solution containing hyaluronic acid, hydroxyethylcellulose, collagen, alginate, or a water-soluble polymer.
  • a gelling chitosan solution for use in culturing cells in vitro, said chitosan solution comprising 0.5-3% w/v of chitosan and being formulated to be thermogelling, said solution being is mixed with cells prior to being cultured in vitro.
  • the polymer composition contains between 0.01 and 10% w/v of 20% to 100% deacetylated chitosan with average molecular weight ranging from 1 kDa to 10 Mda and a blood component.
  • a polymer composition for use in repairing a tissue, and the use thereof.
  • the composition may also be used for the manufacture of a remedy for tissue repair.
  • polymer or “polymer solution”, both interchangeable in the present , application are intended to mean without limitation a polymer solution, a polymer suspension, a polymer particulate or powder, and a polymer micellar suspension.
  • repair when applied to cartilage and other tissues is intended to mean without limitation repair, regeneration, reconstruction, reconstitution or bulking of tissues.
  • FIGS. 1A to 1 F are schematic representation of the mixing of polymer solution with cells and in vitro solidification and culture for cartilage growth;
  • FIGS. 2A to 2 C illustrate the viability of chondrocytes after encapsulation and culture in a chitosan/glycerol-phosphate gel
  • FIGS. 3A to 3 E illustrates cartilage formation within chitosan gel in vitro, as measured by glycosaminoglycan (GAG) accumulation;
  • FIG. 4 illustrates a RNase protection analysis of cartilage-specific mRNAs expressed by primary chondrocytes cultured in chitosan gel for 0, 14 and 20 days;
  • FIGS. 5 illustrates a western blot analysis of cartilage-specific proteins expressed by primary chondrocytes cultured in chitosan gel for 0, 14 and 20 days;
  • FIG. 6 illustrates a mechanical behavior of gel discs cultured with and without chondrocytes
  • FIG. 7 is a schematic representation of polymer mixing with cells and subcutaneous injection into mice
  • FIGS. 8A and 8B illustrate a toluidine blue histology of cartilage grown subcutaneously in nude mice
  • FIG. 9 illustrates a RNase protection analysis of cartilage-specific mRNAs expressed in in vivo implants of chitosan gel with or without primary chondrocytes
  • FIG. 10 illustrates a western blot analysis of cartilage-specific proteins expressed in vivo in mouse implants of chitosan gel harboring primary chondrocytes
  • FIG. 11 illustrates the mechanical properties of cartilage implants grown subcutaneously in nude mice
  • FIGS. 12A and 12B illustrate adhesion of thermogelling chitosan solution to chondral only defects in ex vivo porcine femoral condyles of intact joints;
  • FIGS. 13A and 13B illustrate loading of thermogelling chitosan solution to chondral defects in rabbits, and 24 hours residence in vivo;
  • FIG. 14 illustrates the retention of thermogelling chitosan solution in chandral defects in rabbits, 24 hours after injection;
  • FIG. 15A is a schematic representation showing the preparation, mixing and in vitro solidification of a blood/polymer mixture
  • FIGS. 15B and 15C illustrate the liquid blood/polymer solidification in vitro, in an agarose well. (FIG. 15B) or tube (FIG. 15C) composed of glass or plastic;
  • FIG. 16 illustrates an average solidification time of a blood/chitosan mixture versus blood alone using blood from three different species
  • FIG. 17A illustrates a clot contraction of blood, or blood/polymer mixtures, as measured by plasma release with time, after deposition in a glass vial;
  • FIGS. 17B and 17C illustrate the physical appearance of solid blood and blood/polymer mixtures, 28 hours post-contraction, in glass tubes (FIG. 17B) or as free-swelling discs cast in agarose wells and incubated in Tyrode's buffer (FIG. 17C);
  • FIG. 18 illustrates an admixture of liquid chitosan, but not other liquid polysaccharide solutions, reversing heparin-mediated anti-coagulation
  • FIGS. 19A to 19 C illustrate an histology of blood/polymer mixture
  • FIGS. 20A and 20B illustrates viability of leukocytes and platelets after mixing with a chitosan solution
  • FIG. 21 illustrates a prolonged release of blood proteins from an in vitro-formed blood/polymer mixture versus blood alone
  • FIGS. 22A to 22 C illustrate the preparation, mixing and injection of polymer/blood mixture to improve healing of articular cartilage defects
  • FIGS. 22D and 22E are a schematic representation of therapy to heal human articular cartilage
  • FIGS. 23A and 23B illustrate enhanced chemotaxis of repair cells originating from bone marrow and migrating towards the cartilage defect, 1 week after delivery of the blood/polymer mixture to a chondral defect with bone-penetrating holes;
  • FIGS. 24A and 24B illustrate the growth of hyaline cartilage in defects treated with a blood/polymer mixture versus growth of fibrotic tissue in untreated defects.
  • the polymer When combined with blood or blood components the polymer could be in an aqueous solution or in an aqueous suspension, or in a particulate state, the essential characteristics of the polymer preparation being that 1) it is mixable with blood or selected components of blood, 2) that the resulting mixture is injectable or can be placed at or in a body site that requires tissue repair, regeneration, reconstruction or bulking and 3) that the mixture has a beneficial effect on the repair, regeneration, reconstruction or bulking of tissue at the site of placement.
  • the cells may be resuspended in a physiological buffer, or other cell carrier suspension such as cellulose in an isotonic buffer, prior to mixing with the chitosan solution.
  • a physiological buffer or other cell carrier suspension such as cellulose in an isotonic buffer
  • FIGS. 2 - 6 a physiological buffer
  • FIGS. 8 - 11 bin vivo
  • Chitosan (0.22 g, 85% deacetylated) as an HCl salt powder was sterilized by exposure to ultraviolet radiation in a biological laminar flow hood and then dissolved in 7.5 ml H 2 O resulting in a pH near 5.0.
  • D(+)-glucosamine (0.215 g, MW 215.6) was dissolved in 10 ml of 0.1M NaOH and filter sterilized using a 22 ⁇ m pore size disk filter.
  • Glycerol phosphate (0.8 g, MW 297 including 4.5 mole water per mole glycerol phosphate) was dissolved in 2.0 ml of H 2 O and filter sterilized using a 22 ⁇ m pore size disk filter.
  • a solution is prepared by dissolving 150 mg hydroxyethyl cellulose (Fluka) and 6 ml DMEM (Dulbecco's modified Eagles Medium), and filter sterilized using a 22 ⁇ m pore size disk filter.
  • a cell pellet is resuspended with 2 ml of hydroxyethyl cellulose-DMEM solution, and admixed into the chitosan-glycerol phosphate solution.
  • the chitosan solution mixed with 2 ml of hydroxyethyl cellulose-DMEM solution with no cells was generated.
  • this solution is heated to 37° C. it transforms into a solid hydrogel similarly to the thermogelling solution disclosed in a previous invention (Chenite et al. Patent WO 99/07416).
  • this previous invention did not demonstrate that cell viability was maintained throughout the thermogelling process in this chitosan solution, and thus did not enable the use of this chitosan solution for cell delivery, tissue repair and tissue regeneration.
  • FIG. 1A a cell pellet is resuspended and admixed (FIG. 1B) into the liquid chitosan gel solution at 4° C.
  • FIGS. 1C and 1D the liquid solution is poured into a tissue culture petri and allowed to solidify at 37° C. for 30 minutes, after which the solid gel with cells is washed with DMEM, and discs cored using a biopsy punch.
  • FIG. 1E 1000 ⁇ m pore mesh grids are placed in 48-well plates.
  • the chitosan gel discs with cells are placed in culture in individual wells,
  • a gel harboring cells formed after a 20 minute incubation at 37° C. Using a biopsy punch, 6 mm diameter 1 mm thick discs were cored from the gel and placed in culture for up to 3 weeks. Discs were cultured individually in 48-well tissue culture plates with sterile nylon 1000 ⁇ M meshes beneath to allow media access to all surfaces. Over 90% of the encapsulated cells were viable immediately after encapsulation, and throughout the culture period (FIGS. 2A to 2 C). Samples were incubated in calcein AM and ethidium homodimer-1 to reveal live (green) and dead (red) cells. Freshly isolated chondrocytes (FIG.
  • FIG. 2A shows cells with typical chondrocyte morphology from the middle of the gel.
  • the chitosan gel matrix was also found to bind Toluidine blue (FIG. 3C). This property enabled to observe the lattice structure of the gel, after employing an aldehyde fixation. Interestingly, the pericellular ring of GAC observed around the chondrocytes contained little Achitosan matrix, the latter appearing to have been degraded by chondrocyte-produced factors (FIG. 3D).
  • Primary calf chondrocytes were encapsulated in chitosan gel at 2 ⁇ 10 7 primary chondrocytes per ml and cultured as 6 mm discs for up to 20 days. Primary calf chondrocytes were encapsulated and cultured in 2% agarose and analyzed in parallel.
  • RNA analysis of type II collagen and aggrecan mRNA expressed by the encapsulated chondrocytes revealed high levels at 14 and 22 days of culture (FIG. 4, lanes 4 and 5) that were comparable to those levels observed in articular chondrocytes in cartilage (FIG. 4, lane 6).
  • RNA A mixture of antisense 32 P-labeled RNA probes complementary to bovine type II collagen, aggrecan, and GAPDH was hybridized with tRNA (lane 1), or total RNA, from bovine kidney (lane 2), from primary chondrocytes (10 7 /ml) cultured in chitosan gel for 0 days (lane 3) 14 days (lane 4) or 20 days (lane 5), or adult bovine articular cartilage (lane 6). Samples were treated with RNase A and T1, then submitted to electrophoresis and autoradiography. Protected bands showing the presence of individual transcripts are as indicated. The maintenance of the chondrocyte phenotype in the chitosan/glycerol-phosphate gel is shown by the continued expression of aggrecan and type II collagen.
  • Results show the accumulation of cartilage-specific proteins CP2 and link at 14 and 20 days, as well as the persistence of PCNA expression through culture day 20, as a marker for cell proliferation.
  • Discs containing primary bovine articular chondrocytes were mechanically evaluated at days 4 and 13 of culture using unaxial unconfined compression stress relaxation tests. By comparing to control gels with no cells, a significant, cell-dependent degree of stiffening was observed even at day 4 and became much more dramatic at day 13 (FIG. 6).
  • Discs ( ⁇ 5 mm diameter) from days 4 , 13 and 19 of culture were mechanically tested in unconfined compression by applying 5 ramps of 10% the disk thickness ( ⁇ 1.5 mm) during 10 seconds and holding that displacement during subsequent stress relaxation (the 2nd ramp from 10-20% is shown in the graph).
  • the gel discs without cells displayed a weak behavior while cell-laden gels became evidently stiffer with time in culture and more characteristically viscoelastic, like articular cartilage.
  • Athymic mice (CD1 nu/nu) were subjected to dorsal, subcutaneous injections of 100 to 300 ⁇ l of chitosan gel described in Example 1, containing 10 million calf articular chondrocytes per ml (FIG. 7), A cell pellet of primary calf chondrocytes was admixed with liquid chitosan gel at 4° C. to achieve a concentration of 1 to 2 ⁇ 10 7 cells/ml, and injected in liquid form as 100 ⁇ l subcutaneous dorsal implants in anesthetized nude mice. In situ gelling was apparent by palpation 5 to 10 minutes post-injection.
  • Control mice were similarly injected with chitosan gel alone. A palpable gel was formed within 10 minutes of injection. Implants were recovered at 21, 48, and 63 days post-injection. Toluidine blue staining revealed the gross production of GAG-rich extracellular matrix by the implants containing cells (FIG. 8A). No GAG accumulation was seen in implants of chitosan gel alone (FIG. 8B). Primary calf chondrocytes at 2 ⁇ 10 7 cells/ml liquid chitosan gel were injected in liquid form as 100 ⁇ l subcutaneous dorsal implants in anesthetized nude mice.
  • Cartilage-specific proteins were detected in in vivo implants with primary chondrocytes from days 48 and 63 post-injection (FIG. 10). No cartilage-specific proteins were detected in implants with chitosan gel only (FIG. 10). Total proteins were extracted, separated by SDS-PAGE, and immunoblotted with antisera recognizing vimentin, PCNA, the C-propeptide of type II collagen, or cartilage link protein.
  • Samples analysed include chitosan gel with no cells (lane 1), bovine kidney (lane 2), two distinct in vivo nude mouse implants of chitosan gel only at day 63 (lanes 3 and 4), of in viva implants of chitosan gel with 2 ⁇ 10 7 calf chondrocytes per ml gel at days 48 (lane 5) or day 63 (lane 6), 2-week calf cartilage (lane 7), or adult bovine cartilage (lane 8).
  • Results show the accumulation of cartilage-specific extracellular matrix proteins CP2 and link, in only those chitosan gel implants carrying chondrocytes.
  • PCNA means “proliferating cell nuclear antigen”.
  • CP refers to type 2 collagen C pro-peptide and link refers to cartilage link protein.
  • the equilibrium modulus at 20% and 50% compression offset is shown for the 48 day implant containing cells compared to a control disk left in vitro during a 42 day period.
  • the in vivo grown chondrocyte laden gel has developed substantial mechanical stiffness during 48 days due to the synthesis and assembly of a functional cartilage matrix (FIG. 8A).
  • the articulating cartilage surface was opposed and simulated joint motions were performed after which the gel was observed to remain in the cartilage defect (FIG. 12B).
  • the gel not only remained in the defect but also adhered to the surrounding bone and cartilage surfaces and did not contract.
  • liquid chitosan gel was deposited in 6 mm diameter full-thickness cartilage detects (FIG. 12A) and allowed to solidify at 37° C. for 30 minutes in a humidified incubator. The joint was then closed, and joint motion simulated for several minutes. The chitosan gel adhered to and was retained in all of the defects after simulated joint motion (FIG. 12B).
  • a live New Zealand White rabbit was anesthetized, and a 3 ⁇ 4 mm chondral-only defect created in the trochlea of the femoral patellar groove.
  • Several microfracture holes were introduced with a 16 gauge needle.
  • Liquid thermogelling chitosan was loaded into the defect and allowed to gel for 5 minutes in situ (FIG. 13A). The joint was closed, and the rabbit allowed to recover with unrestricted motion for 24 hours before sacrifice and joint dissection (FIG. 13).
  • FIG. 14 Histological analysis revealed the retention of this thermogelling chitosan gel in the very thin cartilage layer of the rabbit (only about 0.8 mm thick). The gel adhered firmly to surrounding bone and cartilage tissue, demonstrating good retention, thereby enabling its use as an injectable thermogelling polymer delivery vehicle for the repair of cartilage and other tissues.
  • the joint and defect shown in FIG. 13B (filled with thermogelling chitosan, and residing 24 hours in viva) was fixed, embedded in LR White plastic resin, sectioned, and stained with Toluidine Blue. A cross-section of the defect reveals retention of the chitosan gel in situ, as well as adherence to cartilage and bone surfaces in the defect.
  • FIG. 15A Blood and polymer are admixed in a recipient, resulting in a homogenous liquid blend of blood and polymer.
  • peripheral blood from either rabbit artery, or human or equine vein was drawn into a sterile 10 ml syringe.
  • a 20-gauge needle was attached to the syringe, and inserted through the rubber stopper of the vial. 6 ml of peripheral blood was admitted to the vial.
  • the vial was vortex mixed for 10 seconds at full speed. Following any of these mixing techniques, the resulting mixture was deposited into a 4 ml borosilicate glass vial at room temperature, a plastic vial at 37° C., or an agarose well (FIGS. 15B and 15C), or an articular cartilage defect ex vivo.
  • the same treatment was performed with peripheral whole blood only.
  • a vacutainer vial of EDTA-treated blood was drawn to measure CBC and platelet number. All blood samples tested displayed normal CBC and platelet counts for the respective species. Regardless of the species, the prepared blood/polymer, solidified and adhered strongly to the walls of the glass vial within 2.5 to 18 minutes after mixing (FIG. 16). Mixed whole peripheral blood solidified in general more slowly compared to blood/chitosan gel (FIG. 16). Separate samples of blood, with or without liquid chitosan gel, were mixed and solidification time was measured by the number of minutes elapsed between mixing, and achieving a solid adherent mass in the original mixing vial, or secondary recipient.
  • a heparin blood/chitosan in glycerol phosphate buffer mixture was also analyzed. 500 ⁇ l of each sample was deposited into a 4 ml glass tube at 37° C. At distinct time points, all excluded plasma was removed from each tube and weighed, to determine the amount of clot contraction. All samples except blood/chitosan glycerol phosphate mixtures contracted to 30-50% of their original volume. Blood/chitosan mixtures contracted minimally maintaining approximately 90% of their initial volume.
  • a clot contraction test was performed on an array of blood/polymer samples, using several controls (FIGS. 17A, 17B and 17 C).
  • One group of controls consisted of non-agitated whole peripheral blood, or agitated whole peripheral blood, or whole peripheral blood agitated 3:1 (volume:volume) with phosphate-buffered saline. These samples were compared with experimental samples containing 3 volumes whole peripheral blood agitated with 1 volume of distinct 1.5% polysaccharide solutions dissolved in PBS (alginate, hydroxyethyl cellulose, or hyaluronic acid).
  • FIG. 17A Another sample consisted of 3 volumes whole peripheral blood mixed with 1 volume chitosan-glycerol phosphate solution. At intervals up to 18 hours after solidification, the excluded serum for each condition was measured in triplicate, as an indication of degree of contraction.
  • Peripheral blood admixed with the polysaccharides alginate, hydroxyethyl cellulose, or hyaluronic acid contracted to 40%-50% of the original mass (FIG. 17A).
  • the blood/chitosan gel samples showed negligible contraction, with contraction to 90% of the original mass (FIG. 17A).
  • samples shown include blood (1), or mixed blood (2), blood/PBS (3), blood/chitoman in glycerol-phosphate (4), heparin blood/chitosan (5), blood/alginate (6), blood/hydroxyethyl cellulose (7), and blood/hyaluronic acid (8).
  • chitosan in glycerol-phosphate solution 1.5% chitosan in glycerol-phosphate solution, or three distinct 1.5% polysaccharide solutions, were admixed at a ratio of 1 volume polysaccharide solution, to 3 parts whole peripheral blood. 500 ⁇ l of each sample was deposited in a glass borosilicate tube and allowed to solidify for 60 minutes at 37° C. Different polysaccharides include hyaluronic acid-PBS (1), hydroxyethyl cellulose-PBS (2), alginate-PBS (3), and chitosan-glycerol phosphate (4). As a control, heparin blood only was analyzed (5). After 60 minutes, the tubes were laid horizontally and photodocumented. Only the mixture of chitosan-glycerol phosphate and heparinised blood became solid.
  • FIG. 19A Histological sections of solid blood/polymer samples showed that mixtures were homogenous, that red blood cells did not hemolyse after mixing or solidification, and that platelets became activated and were functional (as evidenced by the generation of a dense fibrin network)
  • FIG. 19C A solidified mixture of blood/chitosan was fixed, embedded in LR White plastic, sectioned, and stained with Toluidine Blue.
  • FIG. 19A at 20 ⁇ magnification, global homogeneous mixing is apparent.
  • FIG. 19B at 100 ⁇ magnification, intermixed pools of red blood cells and chitosan hydropolymer is apparent.
  • 2000 ⁇ magnification by environmental electron scanning microscopy
  • the presence of fibrin fiber network throughout the blood/chitosan composite is evident.
  • FIG. 20 Some leukocytes remained viable a number of hours following mixing and solidification (FIG. 20). Peripheral whole blood was mixed with chitosan gel and allowed to solidify. In FIG. 20A, 60 minutes post-solidification, the plug was placed in viability stain with calcein AM/ethidium homodimer-1 to reveal live white blood cells (green cells, large arrows), live platelets (green cells, small arrows), and dead white blood cells (red nuclei). In FIG. 20B, a distinct sample was fixed at 180 minutes post-solidification, embedded in LR-White, and submitted to Transmission Electron Microscopy. Active phagocytosis by peripheral monocytes (arrow head), reflecting cell viability, is evident in TEM micrographs at 3 hours post-mixing and solidification.
  • Serum proteins were released more slowly more sustained from the blood/chitosan samples compared with blood samples (FIG. 21). These data suggest that blood and platelet-derived proteins involved in wound healing are released in a more sustained and prolonged manner from blood/chitosan-filled defects, compared with blood clot-filled defects.
  • Solid discs of blood/chitosan gel, or blood only were generated from 150 ⁇ l initial liquid volume. Resulting discs were washed in 1 ml PBS for 3 hours, then transferred successively at 4, 5, 7, and 19 hours for a total of four additional 1 ml PBS washes. After 3 or 19 hours of washing, representative discs were extracted with GuCl to solubilise total retained proteins.
  • Soluble proteins were precipitated from equal volumes of GuCl extracts or PBS washes, separated on SDS-PAGE gels, and stained for total proteins using Sypro Orange. Comparatively, more proteins were retained in the blood/polymer discs than the blood discs throughout the 19 hour wash period. Comparatively, a slower and more prolonged release of serum proteins into the PBS washes was seen for blood/chitosan than blood over the 19 hour wash period.
  • FIG. 22D A similar treatment in human patients is schematized in FIG. 22D, where prepared cartilage defects receive an arthroscopic injection of liquid blood/polymer that solidifies in situ.
  • an arthroscopic injection of liquid polymer is mixed with bone-derived blood at the defect site (FIG. 22E).
  • FIG. 22D the patient blood is mixed with the polymer ex vivo, and delivered to a prepared defect by arthroscopic injection, or (FIG. 22E) the polymer is delivered arthroscopically or during open knee surgery and mixed at the defect site with patient blood issuing from the defect.
  • 750 ⁇ l blood was drawn into a sterile 1 cc syringe.
  • a second syringe holding 250 ⁇ l of chitosan-glycerol phosphate solution (1.5% chitosan/70 mM HCl/135 mM ⁇ -glycerol phosphate) was interconnected with the blood-containing syringe with a sterile plastic connector.
  • the syringes were pumped back-and-forth 40 times.
  • the mix was drawn into one syringe, to which a 20-gauge needle was attached. After purging half of the mix, one drop (about 25 ⁇ l) was deposited into the defect.
  • a chondral defect with microdrill holes was created in both femoral patellar grooves of an adult New Zealand White rabbit, one of which was filled with blood/chitosan gel, and another left untreated. At 51 or 56 days after healing, the joints were fixed, processed in LR-white, and Toluidine blue stained.
  • repair tissue from the blood/chitosan-treated defect had the appearance of metachromatically staining hyaline cartilage, which adhered to the defect surfaces, and filled the defect.
  • repair tissue from the untreated defect had the appearance of fibro-cartilage, with practically no metachromatic staining for GAG, and only partial defect filling.
  • Examples include: 1) altered chitosan concentration and mixing ratio with blood 2) altered choice of aqueous solution by changing buffer type and species concentration 3) an aqueous suspension of chitosan aggregates 4) a particulate chitosan powder combined with a proper mixing technique to distribute these particle throughout the blood and partly dissolve them other polymers may be used such as 1) another polysaccharide like hyaluronan if its anti-coagulant effect is overcome by formulating it in a procoagulating state (such as by using a low concentration or combining it with thrombin) and 2) a protein polymer such as polylysine or collagen could be used to achieve similar effects.
  • these and other formulations are considered part of the present invention since they possess the characteristics of the polymer preparation of the present invention being that 1) it is mixable with blood or selected components of blood, 2) that the resulting mixture is injectable or can be placed at or in a body site that requires tissue repair, regeneration, reconstruction or bulking and 3) that the mixture has a beneficial effect on the repair, regeneration, reconstruction or bulking of tissue at the site of placement.
  • Hyc A., J. Malejczyk, A. Osiecka, and S. Moskalewski. 1997. Immunological response against allogeneic chondrocytes transplanted into joint surface defects in rats. Cell Transplantation 6, no. 2: 119-24.

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US7148209B2 (en) 2006-12-12
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