US20050118230A1 - Methods and compositions for regenerating connective tissue - Google Patents

Methods and compositions for regenerating connective tissue Download PDF

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US20050118230A1
US20050118230A1 US10/971,544 US97154404A US2005118230A1 US 20050118230 A1 US20050118230 A1 US 20050118230A1 US 97154404 A US97154404 A US 97154404A US 2005118230 A1 US2005118230 A1 US 2005118230A1
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hydrogel matrix
composition
bioactive hydrogel
poly
bone
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Ronald Hill
Richard Klann
Francis Lamberti
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Encelle Inc
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Encelle Inc
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Priority to US10/971,544 priority Critical patent/US20050118230A1/en
Assigned to ENCELLE, INC. reassignment ENCELLE, INC. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: HILL, RONALD STEWART, KLANN, RICHARD CHRIS, LAMBERTI, FRANCIS V.
Publication of US20050118230A1 publication Critical patent/US20050118230A1/en
Priority to US12/039,214 priority patent/US20080145404A1/en
Priority to US12/356,213 priority patent/US20090123547A1/en
Priority to US12/356,195 priority patent/US8883184B2/en
Priority to US13/600,642 priority patent/US20120321597A1/en
Priority to US13/600,661 priority patent/US20120328700A1/en
Abandoned legal-status Critical Current

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    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
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    • A61K35/32—Bones; Osteocytes; Osteoblasts; Tendons; Tenocytes; Teeth; Odontoblasts; Cartilage; Chondrocytes; Synovial membrane
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    • A61L27/3604—Materials for grafts or prostheses or for coating grafts or prostheses containing ingredients of undetermined constitution or reaction products thereof, e.g. transplant tissue, natural bone, extracellular matrix characterised by the human or animal origin of the biological material, e.g. hair, fascia, fish scales, silk, shellac, pericardium, pleura, renal tissue, amniotic membrane, parenchymal tissue, fetal tissue, muscle tissue, fat tissue, enamel
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    • A61L27/3804—Materials for grafts or prostheses or for coating grafts or prostheses containing ingredients of undetermined constitution or reaction products thereof, e.g. transplant tissue, natural bone, extracellular matrix containing added animal cells characterised by specific cells or progenitors thereof, e.g. fibroblasts, connective tissue cells, kidney cells
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    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
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    • A61L27/44—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material having a macromolecular matrix
    • A61L27/48—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material having a macromolecular matrix with macromolecular fillers
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    • A61L2430/00—Materials or treatment for tissue regeneration
    • A61L2430/10—Materials or treatment for tissue regeneration for reconstruction of tendons or ligaments

Definitions

  • the present invention is related to methods and compositions for regenerating connective tissue, such as bone, cartilage, ligament, tendon, and the like.
  • the invention is related to methods for regenerating connective tissue through application of a hydrogel matrix, wherein the matrix is comprised of a polypeptide, such as gelatin, and a long chain carbohydrate, such as dextran.
  • Injuries to bone can be slow to heal, but such injuries generally heal on their own accord with external immobilization as needed, such as by applying a cast to the affected area.
  • more aggressive internal immobilization such as permanently reconnecting the fractured bone with screws and/or metal plates, may be required.
  • Regeneration of bone tissue over the relatively short distances generally present in bone fracture readily occurs in most healthy patients. Bone injuries beyond simple fractures, however, present greater challenges in treatment. Long segmental diaphyseal bone loss, for example, can result from multiple causes including high-energy trauma, such as blast injury, disease, such as osteomyelitis or osteonecrosis, or wide excision of malignant conditions, such as osteosarcoma. Such conditions often result in cavitation of the bone or complete loss of bone tissue across an extended length of the bone (i.e., a critical bone defect). Bone regeneration in these cases becomes increasingly challenging and sometimes impossible.
  • osteoinductive bioactive factors such as bone morphogenetic proteins (BMPs), platelet rich plasma (PRP), synthetic peptides, such as P-15 (Pepgen P-15TM, Dentsply International, York, Pa.), and bone marrow aspirates.
  • BMPs bone morphogenetic proteins
  • PRP platelet rich plasma
  • synthetic peptides such as P-15 (Pepgen P-15TM, Dentsply International, York, Pa.)
  • P-15 Pepgen P-15TM, Dentsply International, York, Pa.
  • bone marrow aspirates Such bioactive factors can be introduced into the area of bone loss through various vehicles.
  • Mechanical methods such as distraction osteogenesis, are also employed for promoting bone regeneration.
  • Distraction osteogenesis is a process involving gradual, controlled displacement of surgically created fractures resulting in simultaneous expansion of soft tissue and bone volume.
  • guided bone regeneration A somewhat less invasive technique that is used most commonly for regenerating bone around teeth is known as “guided bone regeneration.” As the tissue surrounding a bone almost always heals faster than the bone itself, the faster-healing tissue often expands into and fills the space where the bone is missing, hindering the bone regeneration.
  • guided bone regeneration a biocompatible membrane is placed between the tissue and the bone acting as a barrier, which prevents growth of the tissue into the bone. Often, a bone graft is inserted under the barrier. The membranes are typically designed to dissolve away after several weeks.
  • a variation on this procedure is known as “protected bone regeneration” and is based on the theory that three prerequisites for bone healing are required: 1) adequate blood supply, 2) abundant bone forming cells, and 3) protected healing space. See, Holmes, R. E., Lemperle, S. M., and Calhoun, C. J., “Protected Bone Regeneration,” Scientific Data Series in Resorbable Fixation , distributed by Medtronic Sofamor Danek, available on-line at http://www.macropore.com/pdf/Protected_Bone.pdf. Adequate blood supply is a known requirement for bone regeneration as it supplies the necessary oxygen and nutrients, as well as mesenchymal stem cells (the bone forming cells).
  • the healing space of the bone must also be protected from the ingrowth of surrounding tissue.
  • all of the stated prerequisites can be met through the use of a reabsorbable polymer protective sheet offering a physiologically balanced porosity for positive cellular exchange and the opportunity for vascular infiltration, while preventing interposition of adjacent soft tissues.
  • the present invention provides a method for connective tissue regeneration comprising administration of a bioactive hydrogel matrix into the site in need of connective tissue regeneration.
  • bioactive is intended to indicate the ability to facilitate a cellular or tissue response, such as, induction of vasculogenesis, promotion of cellular attachment to a scaffold material, and promotion of tissue regeneration.
  • a method for regenerating connective tissue comprises administering to a site in need of connective tissue regeneration a bioactive hydrogel matrix comprising a polypeptide and a long chain carbohydrate.
  • the polypeptide can be selected from tissue-derived polypetides or synthetic polypeptides.
  • the polypeptide is skin-derived gelatin.
  • the polypeptide is bone-derived gelatin.
  • Exemplary long chain carbohydrates include polysaccharides and sulfated polysaccharides.
  • the long chain carbohydrate is dextran.
  • the bioactive hydrogel matrix further comprises one or more components selected from the group consisting of polar amino acids, polar amino acid analogues or derivatives and divalent cation chelators, such as ethylenediaminetetraacetic acid (EDTA) or salts thereof.
  • polar amino acids such as polar amino acid analogues or derivatives
  • divalent cation chelators such as ethylenediaminetetraacetic acid (EDTA) or salts thereof.
  • the bioactive hydrogel matrix can further include one or more various structuring agents, medicaments, or other agents useful for facilitating or mediating connective tissue regeneration.
  • the bioactive hydrogel matrix can further comprise at least one osteoinductive or osteoconductive material.
  • the method is particularly useful for regenerating bone; moreover, the use of osteoinductive or osteoconductive materials is not limited to bone regeneration.
  • the bioactive hydrogel matrix further comprises at least one medicament.
  • the medicaments can include antivirals, antibacterials, anti-inflammatories, immunosuppresants, analgesics, anticoagulants, or various wound healing promotion agents.
  • the bioactive hydrogel matrix further comprises stem or progenitor cells, such as adipose-derived adult stem (ADAS) cells or mesenchymal stem cells.
  • stem or progenitor cells such as adipose-derived adult stem (ADAS) cells or mesenchymal stem cells.
  • ADAS adipose-derived adult stem
  • mesenchymal stem cells Such cells are known in the art as useful in various therapies due to their ability to differentiate into a number of cell types. ADAS cells in particular are known to differentiate into cell types including chondrocytes and osteoblasts.
  • the bioactive hydrogel matrix is at least partially contained within a three-dimensional structural framework.
  • the structural framework can be included with the bioactive hydrogel matrix prior to administration of the bioactive hydrogel matrix to the site in need of connective tissue regeneration.
  • the structural framework can be formed around the site in need of connective tissue regeneration at the time of administration of the bioactive hydrogel matrix (i.e., formed shortly before or shortly after administration of the bioactive hydrogel matrix).
  • the three-dimensional structural framework therefore, includes any material capable of providing load-bearing structural support or anatomical space for cellular infiltration and includes, for example, a metal cage, a sintered ceramic framework, a collagen sponge, or allogenic or autologous bone.
  • the structural framework can further include three dimensional structures prepared from polymeric materials, including biopolymers.
  • the bioactive hydrogel matrix can also be used in the method of the invention in a dehydrated form.
  • the bioactive hydrogel matrix retains its beneficial properties yet can be stored and transported in a solid form, being capable of re-hydration for use in the method of the present invention.
  • the bioactive hydrogel matrix is administered in a dehydrated form such that body fluids re-hydrate the bioactive hydrogel matrix.
  • the bioactive hydrogel matrix is in dehydrated form and the method further comprises re-hydrating the bioactive hydrogel matrix with a re-hydrating fluid prior to administering the bioactive hydrogel matrix to the site in need of connective tissue regeneration.
  • the bioactive hydrogel matrix can be shaped or processed into a variety of shapes and forms.
  • the dehydrated bioactive hydrogel matrix can be in a unitary piece capable of being shaped to precisely fit the site in need of connective tissue regeneration.
  • the dehydrated bioactive hydrogel matrix can be in particulate form.
  • the particulate dehydrated bioactive hydrogel matrix could be mixed into a solution containing other beneficial ingredients, such as stem or progenitor cells or medicaments, combined with osteoinductive or osteoconductive materials to form a putty or paste-like material for placement into the site in need of connective tissue regeneration, or used in other preparations that would be useful in the method of the invention.
  • the bioactive hydrogel matrix may be useful for the bioactive hydrogel matrix to have additional structure or strength in the absence of additives. Accordingly, the present invention further encompasses embodiments wherein the bioactive hydrogel matrix is in crosslinked form, the long chain carbohydrate being covalently crosslinked to the polypeptide. In such embodiments, the bioactive hydrogel matrix can be used alone in the method of the invention or may be used in conjunction with other components as described herein.
  • the bioactive hydrogel matrix is inserted into an area of a bone in need of repair or regeneration (i.e., a bone defect).
  • the amount of the bioactive hydrogel matrix used in the bone can vary depending upon the size of the bone defect, the form of the bioactive hydrogel matrix, and the presence or absence of additives as described herein.
  • the total amount of the bioactive hydrogel matrix used is the amount required to fill the area of bone loss.
  • the hydrogel matrix can be used for repair of soft tissue either separately or in conjunction with regeneration of nearby hard tissue, such as bone.
  • the bioactive hydrogel matrix is administered around and/or injected into the soft tissue.
  • the hydrogel matrix can be used for repair and/or regeneration of non-bone connective tissue.
  • the bioactive hydrogel matrix is administered to an area having loss of, or damage to, connective tissue, which includes tissue arising from fibroblasts, such as tendon and ligament, or chondrocytes, such as cartilage.
  • compositions are particularly useful in the regeneration of connective tissue or for treatment of patients having various connective tissue degenerative diseases. Accordingly, the compositions described herein are particularly useful in the methods of the invention also described herein.
  • the connective tissue regenerative composition comprises a three-dimensional structural framework and a bioactive hydrogel matrix at least partially contained within the three-dimensional structural framework, wherein the bioactive hydrogel matrix comprises a polypeptide and a long chain carbohydrate.
  • the bioactive hydrogel matrix preferably further comprises one or more components selected from the group consisting of polar amino acids, polar amino acid analogues or derivatives, and divalent cation chelators, such as EDTA or salts thereof.
  • the three-dimensional structural framework includes a crosslinked hydrogel matrix.
  • the three-dimensional structural framework includes a collage sponge.
  • the connective tissue regenerative composition comprises at least one osteoinductive or osteoconductive material and a bioactive hydrogel matrix comprising a polypeptide and a long chain carbohydrate.
  • the osteoinductive or osteoconductive material can be dispersed within the bioactive hydrogel matrix.
  • the osteoinductive or osteoconductive material and the bioactive hydrogel matrix can be in admixture.
  • the bioactive hydrogel matrix can be in a hydrated form or can be in a dehydrated form.
  • the connective tissue regenerative composition comprises stem or progenitor cells and a bioactive hydrogel matrix comprising a polypeptide and a long chain carbohydrate.
  • the bioactive hydrogel matrix can be in a hydrated form or can be in a dehydrated form.
  • the bioactive hydrogel matrix can be used for attaching or reattaching two or more connective tissues.
  • the method comprises: coating at least a portion of at least one of a first and second connective tissue with a bioactive hydrogel matrix comprising a polypeptide and a long chain carbohydrate; contacting the first connective tissue to the second connective tissue at a point of attachment; and attaching the first connective tissue to the second connective tissue using sutures, staples or other appropriate means.
  • a method is particularly useful for attaching connective tissue, such as tendon or ligament, to bone.
  • the method is further useful for attaching soft connective tissue to other soft connective tissue, such as tendon to tendon or ligament to ligament.
  • the bioactive hydrogel matrix is used in a method for treating degenerative diseases of the natural joint of a patient in need of treatment thereof.
  • the method comprises: applying to a joint affected by a degenerative disease, a bioactive hydrogel matrix comprising a polypeptide and a long chain carbohydrate.
  • the bioactive hydrogel matrix can include stem or progenitor cells.
  • the administering step comprises injecting the bioactive hydrogel matrix into the affected joint. The method is particularly useful for halting progression of or reversing degenerative joint diseases, such as osteoarthritis.
  • compositions and methods of the present invention are particularly useful for repairing connective tissue of the knee, such as the anterior cruciate ligament, the posterior cruciate ligament, the patellar tendon, the quadriceps tendon, and the anterior meniscofemoral ligament.
  • compositions and methods of the invention are further useful for treating a patient having an artificial joint.
  • the connective tissue regenerative compositions can be administered around the site of the artificial joint, either during placement of the artificial joint or post-surgery, to facilitate integration of the artificial joint into the surrounding tissue.
  • FIG. 1 illustrates formation of open alpha chains derived from collagen monomers
  • FIGS. 2A and 2B illustrate the effect of the association of the collagen-derived alpha chains with dextran
  • FIG. 3 illustrates the effect of other additives used in the bioactive hydrogel matrix of the invention
  • FIG. 4 graphically illustrates cellular aggregation across various cell types in the presence of the bioactive hydrogel matrix of the present invention
  • FIG. 5 illustrates the effect of the bioactive hydrogel matrix of the present invention on the expression of the BMP-2 gene as compared to expression in cells in serum free medium (SFM);
  • FIG. 6 illustrates the increased expression of connective tissue growth factor (CTGF) messenger RNA in chondrosarcoma cells treated with the bioactive hydrogel matrix of the invention as compared to cells in SFM;
  • CTGF connective tissue growth factor
  • FIG. 7 illustrates the expression of aggrecan messenger RNA in chondrosarcoma cells treated with the bioactive hydrogel matrix of the invention compared to cells in SFM;
  • FIG. 8 illustrates a crosslinked bioactive hydrogel matrix of the invention comprising dextran and gelatin
  • FIG. 9 illustrates the effect of the bioactive hydrogel matrix of the present invention on the production of BMP-2 protein as compared to production in cells in serum containing medium (SCM).
  • FIG. 10 illustrates the effect of the crosslinked bioactive hydrogel matrix of the present invention on the expression of the BMP-2 gene.
  • thermoreversible hydrogel matrix providing a cell culture medium and composition for preserving cell viability
  • U.S. Pat. No. 6,231,881 herein incorporated by reference in its entirety
  • a hydrogel matrix useful in promoting vascularization is provided in U.S. Pat. No. 6,261,587, herein incorporated by reference in its entirety.
  • the thermoreversible hydrogel matrix taught by these references is a gel at storage temperatures and molten at physiologic temperatures, and comprises a combination of a collagen-derived component, such as gelatin, a long chain carbohydrate, such as dextran, and effective amounts of other components, such as polar amino acids.
  • the present invention provides connective tissue regenerative compositions and methods of regenerating connective tissue at a site in need of connective tissue regeneration.
  • the compositions and method of the invention include a bioactive hydrogel matrix generally comprising a polypeptide and a long chain carbohydrate.
  • a polypeptide is intended to encompass any tissue-derived or synthetically produced polypeptide, such as collagens or collagen-derived gelatins.
  • collagen-derived gelatin is the preferred polypeptide component
  • other gelatin-like components characterized by a backbone comprised of sequences of amino acids having polar groups that are capable of interacting with other molecules can be used.
  • keratin, decorin, aggrecan, glycoproteins (including proteoglycans), and the like could be used to provide the polypeptide component.
  • the polypeptide component is porcine gelatin from partially hydrolyzed collagen derived from skin tissue. Polypeptides derived from other types of tissue could also be used.
  • Examples include, but are not limited to, tissue extracts from arteries, vocal chords, pleura, trachea, bronchi, pulmonary alveolar septa, ligaments, auricular cartilage or abdominal fascia; the reticular network of the liver; the basement membrane of the kidney; or the neurilemma, arachnoid, dura mater or pia mater of the nervous system.
  • Purified polypeptides including, but not limited to, laminin, nidogen, fibulin, and fibrillin or protein mixtures such as those described by U.S. Pat. No. 6,264,992 and U.S. Pat. No. 4,829,000, extracts from cell culture broth as described by U.S. Pat. No.
  • a suitable polypeptide is a fusion protein formed by genetically engineering a known reactive species onto a protein.
  • the polypeptide component preferably has a molecular mass range of about 3,000 to about 3,000,000 Da, more preferably about 30,000 to about 300,000 Da, most preferably about 50,000 to about 250,000 Da.
  • Molecular mass can be expressed as a weight average molecular mass (M w ) or a number average molecular mass (M n ). Both expressions are based upon the characterization of macromolecular solute containing solution as having an average number of molecules (n i ) and a molar mass for each molecule (M i ). Accordingly, number average molecular mass is defined by formula 1 below.
  • M n ⁇ n i ⁇ M i ⁇ n i ( 1 )
  • Weight average molecular mass (also known as molecular mass average) is directly measurable using light scattering methods and is defined by formula 2 below.
  • M w ⁇ n i ⁇ M i 2 ⁇ n i ⁇ M i ( 2 )
  • Molecular mass can also be expressed as a Z-average molar mass (M z ), wherein the calculation places greater emphasis on molecules with large molar masses.
  • Z-average molar mass is defined by formula 3 below.
  • M z ⁇ n i ⁇ M i 3 ⁇ n i ⁇ M i 2 ( 3 ) Unless otherwise noted, molecular mass is expressed herein as weight average molecular mass.
  • polymer solutions can also be physically described in terms of polydispersity, which represents the broadness of the molecular mass distribution within the solution, such distribution being the range of different molecular masses of the individual polymer molecules in the solution.
  • polydispersity is equal to 1 (i.e., M n equals M w ), the polymer is said to be monodisperse.
  • a truly monodisperse polymer is one where all polymer molecules within the solution are of a single, identical molecular mass. As M n changes with M w , the polydispersity changes, always being greater than 1.
  • the polydispersity of a given polymer solution can affect the physical characteristics of the polymer, and, therefore, the interaction of the polymer with another polymer.
  • the polypeptide used according to the present invention has a polydispersity close to 1.
  • the polypeptide has a polydispersity of 1 to about 4, more preferably, about 1 to about 3, most preferably about 1.1 to about 2.4.
  • the polypeptide used in the bioactive hydrogel matrix of the invention is preferably a gelatin, such as collagen derived gelatin.
  • Collagen is a major protein component of the extracellular matrix of animals. Early in fetal development, a more open form of collagen (compared to tightly bound mature collagen) is associated with large carbohydrate molecules, and serves as the predominant tissue scaffolding. It is believed that attachment of differentiated or incompletely differentiated cells of mesenchymal origin to this polar, proteoglycan-like, collagen scaffolding results in a specific host tissue response. This response is to guide the differentiation of mesenchymal tissue.
  • Collagen is assembled into a complex fibrillar organization.
  • the fibrils are assembled into bundles that form the fibers.
  • the fibrils are made of five microfibrils placed in a staggered arrangement.
  • Each microfibril is a collection of collagen rods.
  • Each collagen rod is a right-handed triple-helix, each strand being itself a left-handed helix.
  • Collagen fibrils are strengthened by covalent intra- and intermolecular cross-links which make the tissues of mature animals insoluble in cold water. When suitable treatments are used, collagen rods are extracted and solubilized where they keep their conformation as triple-helices.
  • collagen solutions are extensively heated, or when the native collagen containing tissues are subjected to chemical and thermal treatments, the hydrogen and covalent bonds that stabilize the collagen helices are broken, and the molecules adopt a disordered conformation.
  • breaking these hydrogen bonds the polar amine and carboxylic acid groups are now available for binding to polar groups from other sources or themselves.
  • This material is gelatin and is water-soluble at 40-45° C.
  • gelatin is a form of denatured collagen, and is obtained by the partial hydrolysis of collagen derived from the skin, white connective tissue, or bones of animals.
  • Gelatin may be derived from an acid-treated precursor or an alkali-treated precursor.
  • Gelatin derived from an acid-treated precursor is known as Type A
  • gelatin derived from an alkali-treated precursor is known as Type B.
  • the macromolecular structural changes associated with collagen degradation are basically the same for chemical and partial thermal hydrolysis. In the case of thermal and acid-catalyzed degradation, hydrolytic cleavage predominates within individual collagen chains. In alkaline hydrolysis, cleavage of inter- and intramolecular cross-links predominates.
  • the gelatin used in the present invention is skin-derived gelatin or bone derived gelatin.
  • the gelatin has a molecular mass of about 80,000 Da to about 200,000 Da.
  • it is preferred that the gelatin have a polydispersity of 1 to about 3.
  • the gelatin has a polydispersity of about 1.1 to about 2.4.
  • the polypeptide such as gelatin
  • the gelatin concentration is approximately 0.75 mM.
  • the above concentrations provide a non-flowable phase at storage temperature (below about 33° C.) and a flowable phase at treatment temperature (about 35 to about 40° C.).
  • the bioactive hydrogel matrix of the present invention also comprises a long chain carbohydrate.
  • long chain carbohydrate is generally intended to encompass any polysaccharide or sulfated polysaccharide consisting of more than about 10 monosaccharide residues joined to each other by glycosidic linkages.
  • the phrase is also intended to encompass other long chain carbohydrates, including heterosaccharides, and specific classes of carbohydrates, such as starches, sugars, celluloses, and gums.
  • the long chain carbohydrate may consist of the same monosaccharide residues, or various monosaccharide residues or derivatives of monosaccharide residues. Dextran, a preferred polysaccharide, solely comprises glucose residues.
  • glycosaminoglycans GAGs
  • glucosaminoglycans glucosaminoglycans
  • suitable viscosity, molecular mass and other desirable properties may be utilized in the present invention.
  • glycosaminoglycan any glycan (i.e., polysaccharide) comprising an unbranched polysaccharide chain with a repeating disaccharide unit, one of which is always an amino sugar.
  • These compounds as a class carry a high negative charge, are strongly hydrophilic, and are commonly called mucopolysaccharides.
  • This group of polysaccharides includes heparin, heparan sulfate, chondroitin sulfate, dermatan sulfate, keratan sulfate, and hyaluronic acid. These GAGs are predominantly found on cell surfaces and in the extracellular matrix.
  • glucosaminoglycan is intended any glycan (i.e. polysaccharide) containing predominantly monosaccharide derivatives in which an alcoholic hydroxyl group has been replaced by an amino group or other functional group such as sulfate or phosphate.
  • glucosaminoglycan poly-N-acetyl glucosaminoglycan, commonly referred to as chitosan.
  • exemplary polysaccharides that may be useful in the present invention include dextran, heparan, heparin, hyaluronic acid, alginate, agarose, carageenan, amylopectin, amylose, glycogen, starch, cellulose, chitin, chitosan and various sulfated polysaccharides such as heparan sulfate, chondroitin sulfate, dextran sulfate, dermatan sulfate, or keratan sulfate.
  • the long chain carbohydrate preferably has a molecular mass of about 2,000 to about 8,000,000 Da, more preferably about 20,000 to about 1,000,000 Da, most preferably about 200,000 to about 800,000 Da. In one embodiment, the long chain carbohydrate has a molecular mass of approximately 500,000 Da.
  • the long chain carbohydrate used according to the present invention has a polydispersity close to 1.
  • the polypeptide has a polydispersity of 1 to about 3, more preferably, about 1.1 to about 2.4.
  • Dextran typically comprises linear chains of ⁇ (1 ⁇ 6)-linked D-glucose residues, often with ⁇ (1 ⁇ 2)- or ⁇ (1 ⁇ 3)-branches.
  • Native dextran produced by a number of species of bacteria of the family Lactobacilliaceae, is a polydisperse mixture of components.
  • Dextrans have been widely used as plasma substitutes and blood extenders, are considered fully biocompatible, and are metabolizable. Dextrans are available in a wide range of average molecular masses, varying from about 4,000 to about 40,000,000 Da.
  • the dextran used in the invention has a molecular mass of about 200,000 to about 800,000 Da, most preferably about 300,000 to about 600,000 Da. In one preferred embodiment, the dextran has a molecular mass of approximately 500,000 Da. Dextrans have varying rates of resorption in vivo from about two to about 20 days depending on their molecular mass.
  • the long chain carbohydrate such as dextran
  • dextran is present at a concentration of about 0.1 mM.
  • dextran derivatives such as dextran sulfate and dextran phosphate
  • the derivatives are free radical polymerizable, preferably photopolymerizable derivatives, such as acrylates.
  • the composition can be injected as a viscous liquid and polymerized in situ to form a solid material.
  • the dextran can also be selected to degrade at a rate which approximates ingrowth of new bone or tissue.
  • compositions that include free radical polymerizable groups may also include polymerization initiators, such as photoinitiators, such as benzoin ethers, and thermally activatable initiators, such as azobisisobutyronitrile (AIBN) and di-t-butyl ether.
  • polymerization initiators such as photoinitiators, such as benzoin ethers
  • thermally activatable initiators such as azobisisobutyronitrile (AIBN) and di-t-butyl ether.
  • Free radical polymerization initiators, and conditions for carrying out free radical polymerizations are well known to those of skill in the art, and any of such methods are encompassed by the present invention.
  • gelatin and dextran are components of the bioactive hydrogel matrix of the present invention.
  • the terms “gelatin” and “dextran” are used throughout with the understanding that various alternatives as described above, such as other polypeptides and other long chain carbohydrates readily envisioned by those skilled in the art, are contemplated by the present invention.
  • the present invention is intended to provide a matrix scaffolding designed to maximize the polar amino acid hydrogen bonding sites found in alpha chains derived from collagen.
  • alpha chains or gelatin, are preferably derived from pig gelatin, and stabilized by 500,000 Da molecular mass dextran, or other long chain carbohydrates, added while the alpha chains are heated.
  • the positively charged polar groups of the collagen-derived alpha chains are then able to associate with the negatively charged —OH groups of the repeating glucose units found in the dextran.
  • the gelatin and the dextran form a proteoglycan-type structure.
  • FIGS. 1-3 illustrate the interaction between the various components of the preferred embodiment of the matrix of the invention and interaction between the matrix and the tissue of a patient.
  • FIG. 1 illustrates the creation of polar alpha chains 15 from tropocollagen 10 derived from mature collagen. Heating tropocollagen 10 disrupts the hydrogen bonds that tightly contain the triple stranded monomers in mature collagen. By breaking these hydrogen bonds, the polar amine and carboxylic acid groups are now available for binding to polar groups from other sources or themselves.
  • FIGS. 2A-2B illustrate stabilization of the matrix monomeric scaffolding by the introduction of a long chain carbohydrate 20 , such as dextran.
  • a long chain carbohydrate 20 such as dextran.
  • the alpha chain 15 will form hydrogen bonds between the amino and carboxylic acid groups within the linear portion of the monomer and fold upon itself, thus limiting available sites for cellular attachment.
  • the long chain carbohydrate 20 serves to hold the alpha chain 15 open by interfering with this folding process.
  • the bioactive hydrogel matrix can further comprise one or more components useful for enhancing the bioadhesiveness of the hydrogel matrix.
  • components useful for enhancing the bioadhesiveness of the hydrogel matrix include polar amino acids, polar amino acid analogues or derivatives, divalent cation chelators, and combinations thereof.
  • all of the bioactive hydrogel matrix ingredients are provided in admixture.
  • the bioactive hydrogel matrix preferably includes one or more polar amino acids in an effective amount to increase the rigidity of the hydrogel matrix and allow direct administration of the hydrogel matrix, such as through injection, to a site in need of connective tissue regeneration.
  • polar amino acids are commonly defined and intended to include tyrosine, cysteine, serine, threonine, asparagine, glutamine, asparatic acid, glutamic acid, arginine, lysine, and histidine.
  • the amino acids are selected from the group consisting of cysteine, arginine, lysine, histidine, glutamic acid, aspartic acid.
  • the polar amino acids are preferentially present in a concentration of about 3 to about 150 mM, preferably about 10 to about 65 mM, and more preferably about 15 to about 40 mM.
  • the added polar amino acids comprise L-glutamic acid, L-lysine, and L-arginine.
  • the final concentration of L-glutamic acid is generally about 2 to about 60 mM, preferably about 5 to about 40 mM, most preferably about 10 to about 30 mM. In one embodiment, the concentration of L-glutamic acid is about 20 mM.
  • the final concentration of L-lysine is generally about 0.5 to about 30 mM, preferably about 1 to about 15 mM, most preferably about 1 to about 10 mM. In one embodiment, the concentration of L-lysine is about 5.0 mM.
  • the final concentration of L-arginine is generally about 1 to about 40 mM, preferably about 1 to about 30 mM, most preferably about 5 to about 20 mM. In one embodiment, the final concentration of arginine is about 15 mM.
  • amino acid is intended all naturally occurring alpha amino acids in both their D and L stereoisomeric forms, and their analogues and derivatives.
  • An analog is defined as a substitution of an atom or functional group in the amino acid with a different atom or functional group that usually has similar properties.
  • a derivative is defined as an amino acid that has another molecule or atom attached to it. Derivatives would include, for example, acetylation of an amino group, amination of a carboxyl group, or oxidation of the sulfur residues of two cysteine molecules to form cystine.
  • the bioactive hydrogel matrix of the invention can include one or more polar amino acid analogues or derivatives.
  • amino acids used in the bioactive hydrogel matrix of the present invention can also be present as dipeptides, which are particular beneficial for delivery of amino acids having decreased water solubility, such as L-glutamine.
  • amino acids added to the hydrogel matrix can include dipeptides, such as L-alanyl-L-glutamine.
  • the concentration range for L-alanyl-L-glutamine is preferably about 0.001 to about 1 mM, more preferably about 0.005 to about 0.5 mM, most preferably about 0.008 to about 0.1 mM. In one particular embodiment, the final concentration of L-alanyl-L-glutamine is about 0.01 mM.
  • the added amino acids can also include L-cysteine, which is advantageous in many regards. Cysteine is useful for providing disulfide bridges, further adding support and structure to the bioactive hydrogel matrix and increasing its resistance to force.
  • the final concentration of L-cysteine is generally about 5 to about 5000 ⁇ M, preferably about 10 to about 1000 ⁇ M, most preferably about 100 to about 1000 ⁇ M. In one embodiment, the final concentration of cysteine is about 700 ⁇ M.
  • L-cysteine also acts as a nitric oxide scavenger or inhibitor. Nitric oxide inhibitors include any composition or agent that inhibits the production of nitric oxide or scavenges or removes existing nitric oxide.
  • Nitric oxide a pleiotropic mediator of inflammation, is a soluble gas produced by endothelial cells, macrophages, and specific neurons in the brain, and is active in inducing an inflammatory response. Nitric oxide and its metabolites are known to cause cellular death from nuclear destruction and related injuries.
  • the bioactive hydrogel matrix can optionally include one or more additional nitric oxide inhibitors, such as aminoguanidine, N-monomethyl-L-arginine, N-nitro-L-arginine, cysteine, heparin, and mixtures thereof.
  • additional nitric oxide inhibitors such as aminoguanidine, N-monomethyl-L-arginine, N-nitro-L-arginine, cysteine, heparin, and mixtures thereof.
  • the final concentration of nitric oxide inhibitors is generally about 5 to about 500 ⁇ M, preferably about 10 to about 100 ⁇ M, most preferably about 15 to about 25 ⁇ M. In one embodiment, the final concentration is about 20 ⁇ M.
  • intact collagen can be optionally added to the bioactive hydrogel matrix to provide an additional binding network and provide additional support to the matrix.
  • the final concentration of the intact collagen present in the hydrogel matrix is from about 0 to about 5 mM, preferably about 0 to about 2 mM, most preferably about 0.05 to about 0.5 mM.
  • the bioactive hydrogel matrix may optionally include one or more divalent cation chelators, which increase the rigidity of the matrix by forming coordinated complexes with any divalent metal ions present. The formation of such complexes leads to the increased rigidity of the matrix by removing the inhibition of hydrogen bonding between —NH 2 and —COOH caused by the presence of the divalent metal ions.
  • a preferred example of a divalent cation chelator that is useful in the present invention is ethylenediaminetetraacetic acid (EDTA) or a salt thereof.
  • the concentration range for the divalent cation chelator, such as EDTA is generally about 0.01 to about 10 mM, preferably 1 to about 8 mM, most preferably about 2 to about 6 mM. In a one embodiment, EDTA is present at a concentration of about 4 mM.
  • EDTA is also an example of another group of compounds useful as additives for the bioactive hydrogel matrix, superoxide inhibitors.
  • Superoxide is a highly toxic reactive oxygen species, whose formation is catalyzed by divalent transition metals, such as iron, manganese, cobalt, and sometimes calcium. Highly reactive oxygen species such as superoxide (O 2 ⁇ ) can be further converted to the highly toxic hydroxyl radical (OH ⁇ ) in the presence of iron.
  • the bioactive hydrogel matrix can include one or more superoxide inhibitor.
  • trace mineral nutrients and salts thereof such as zinc sulfate
  • Zinc has beneficial wound healing effects that are particularly useful in the present invention.
  • the concentration range for zinc is generally about 0.005 mM to about 3 mM, preferably about 0.01 to about 2 mM, most preferably about 0.02 to about 1 mM. In one particular embodiment, the final concentration of zinc is about 0.03 mM.
  • the bioactive hydrogel matrix is preferably based upon a physiologically compatible buffer, one embodiment being Medium 199, a common nutrient solution used for in vitro culture of various mammalian cell types (available commercially from Sigma Chemical Company, St. Louis, Mo.).
  • the buffer can be further supplemented with additives and additional amounts of some medium components, such as supplemental amounts of polar amino acids as described above.
  • the bioactive hydrogel matrix can also be formulated in other buffered solutions, including buffered solutions regarded as simplified in relation to Medium 199.
  • buffered solutions regarded as simplified in relation to Medium 199.
  • a phosphate buffer formulated to yield physiological osmotic pressures after hydrogel matrix compounding can be prepared using 1.80 mM KH 2 PO 4 and 63 mM Na 2 HPO 4 .
  • the bioactive hydrogel matrix of the present invention is particularly useful for repairing and regenerating connective tissue because of the open structure of the hydrogel matrix and the inherent ability of the hydrogel matrix to interact with physiological material.
  • FIG. 3 illustrates the effect of polar amino acids and/or L-cysteine added to stabilize the monomer/carbohydrate units 25 by linking the exposed monomer polar sites to, for example, arginine's amine groups or glutamic acid's carboxylic acid groups. Furthermore, disulfide linkages can be formed between L-cysteine molecules (thereby forming cystine), which in turn forms hydrogen bonds to the monomeric alpha chains 15 .
  • the stability imparted by the polar amino acids, polar amino acid analogues and derivatives, and intact collagen is particularly advantageous for maintaining the open structure of the gelatin and keeping the active sites available for therapeutic benefit.
  • EDTA or a salt thereof is also present to chelate divalent cations and thereby prevent divalent cations from being preferentially attracted to the exposed polar groups of the monomer/carbohydrate units 25 to the exclusion of the polar amino acids.
  • nitric oxide inhibitors such as aminoguanidine and cysteine
  • superoxide inhibitors such as EDTA
  • the matrix serves as a biocompatible device capable of increasing vascularization and promoting wound healing and local tissue regeneration, even in the case of large areas of bone loss. Because the matrix promotes tissue-specific regeneration, as occurs during embryogenesis and fetogenesis where similar types of scaffolding are present, it has now been discovered that the matrix of the invention can be used to successfully treat bone injuries that are typically non-responsive to conventional treatments, such as long segmental diaphyseal bone loss, cavitation, and simple fractures in patients having abnormally low ability to regenerate bone tissue. Furthermore, it has been discovered that the bioactive hydrogel matrix of the present invention can be used to successfully treat additional types of injuries often known to be difficult to treat or slow to heal, such as injuries to non-bone connective tissues, such as tendon, ligament, and cartilage.
  • bioactive hydrogel matrix of the invention exhibits a remarkable ability to bind to and hence promote cell aggregation across multiple cell types.
  • Treatment of cultured osteoblasts (human osteosarcoma cell line SAOS-2) with the bioactive hydrogel matrix resulted in approximately 80% cellular aggregation.
  • cells were treated with the bioactive hydrogel matrix of the invention, and cells (control) were treated with gelatin alone.
  • Cell types tested were fibroblasts, osteoblasts, chondrocytes, and adipocytes. The cells were stained with trypan blue and visually inspected.
  • the cells treated with the bioactive hydrogel matrix were evident as large clumps (i.e., aggregates), while the control cells (those treated with gelatin alone) were evident as single cells and not aggregated.
  • previous similar studies with fibroblasts indicated the binding and aggregation also did not occur after treatment with dextran alone.
  • FIG. 4 provides quantification of the aggregation of the cells in the study described above.
  • all four cell types demonstrated approximately 80% aggregation.
  • the cells treated with gelatin alone demonstrated less than 30% aggregation.
  • the binding of the bioactive hydrogel matrix to cells as evidenced by the aggregation is believed to be the first key step in the action of the bioactive hydrogel matrix on cellular activity.
  • the aggregation is a result of the cells interacting with the open polar co-polymer structure of the bioactive hydrogel matrix.
  • the bioactive hydrogel matrix of the invention also exhibits additional action necessary for bone regeneration.
  • BMP-2 bone morphogenetic protein-2
  • TGF transforming growth factor
  • BMP-2 is a member of the transforming growth factor (TGF) beta superfamily of proteins and a key regulator of osteoblast differentiation.
  • TGF transforming growth factor
  • BMP is known to stimulate wound healing and includes various bone morphogenetic proteins in addition to BMP-2. This alteration and increase of gene activity is indicative of the ability of the matrix to produce healing of bone fractures.
  • FIG. 5 This activity of the bioactive hydrogel matrix in stimulating BMP-2 production is illustrated in FIG. 5 , which demonstrates an acute and dramatic increase in BMP-2 gene expression after a 40 minute treatment with the bioactive hydrogel matrix as compared to a control.
  • FIGS. 6 and 7 illustrate the effects of treatment of cultured chondrocytes (cells leading to the production of tendon, ligament, and cartilage) with the bioactive hydrogel matrix of the invention in causing a greater than 3-fold increase in Connective Tissue Growth Factor (CTGF) and aggrecan gene expression.
  • CTGF is a profibrotic protein induced by TGF beta and is a key regulator of chondrocyte proliferation and differentiation. It is an early marker of chondrogenesis expressed at the highest levels in vivo during chondrocyte growth.
  • Aggrecan is a major cartilage extracellular matrix (ECM) component and a marker for the chondrocyte phenotype.
  • FIG. 6 again illustrates an acute and marked increase in CTGF gene expression in the presence of the bioactive hydrogel matrix.
  • FIG. 7 illustrates a similar increase in aggrecan gene expression and also illustrates a more prolonged effect of such increase.
  • the bioactive hydrogel matrix of the present invention can further be in a dehydrated form.
  • This is a particularly advantageous form of the bioactive hydrogel matrix increasing the practical usefulness of the hydrogel matrix, providing for ease of storage and transportation, and preserving the shelf-life of the hydrogel matrix and compositions made using the hydrogel matrix.
  • Any method generally known in the art for dehydrating materials normally in a hydrated state would be useful according to the present invention, so long as it is not detrimental to the connective tissue regenerative properties of the hydrogel matrix as described herein.
  • one preferred method of dehydrating the bioactive hydrogel matrix is freeze drying.
  • Other methods of preparing dehydrated biopolymers, such as spray-drying or speed-vac can also be used and are known to those skilled in the art.
  • Freeze drying generally comprises the removal of water or other solvent from a frozen product through sublimation, which is the direct transition of a material (e.g., water) from a solid state to a gaseous state without passing through the liquid phase. Freeze drying allows for the preparation of a stable product being readily re-hydratable, easy to use, and aesthetic in appearance.
  • the freeze drying process consists of three stages: 1) pre-freezing, 2) primary drying, and 3) secondary drying.
  • freeze drying involves a phase change from solid to gaseous
  • material for freeze drying must first be adequately pre-frozen.
  • the pre-freezing method and the final frozen product temperature can both affect the ability to successfully freeze dry the material. Rapid cooling forms small ice crystals. While small crystals are useful in preserving structure, they result in a product that is more difficult to freeze dry. Slower cooling results in larger ice crystals and produces less restrictive channels in the matrix during the drying process. Pre-freezing to temperatures below the eutectic temperature, or glass transition temperature, is necessary for complete drying of hydrogels. Inadequate freezing may produce small pockets of unfrozen material remaining in the product which may expand and compromise the structural stability of the freeze dried product.
  • One example of equipment useful in preparing freeze dried hydrogels is the FreeZone 12 Liter Freeze Dry System with Stoppering Tray Dryer (Labconco Kansas City, Mo.). With such system, tubes with porous caps containing hydrogels are frozen to ⁇ 30° C. at a cooling rate of 0.05° C./min using the cooling shelf unit of the freeze dryer and are held at ⁇ 30° C. for 12 hours. A vacuum is applied to the frozen hydrogel at ⁇ 30° C. for 24 hours before the temperature is incrementally increased to ⁇ 10° C. at a rate of 0.25° C./minute. The hydrogel is held under vacuum at ⁇ 10° C. for at least 12 hours before the temperature is further increased to 20° C. at a rate of 0.05° C./minute.
  • the dehydrated bioactive hydrogel matrix can comprise the bioactive hydrogel matrix in any of the embodiments described herein. Furthermore, the bioactive hydrogel matrix can be used in preparing any of the connective tissue regenerative compositions described herein prior to being dehydrated. Therefore, the present invention also encompasses dehydrated connective tissue regenerative compositions.
  • the bioactive hydrogel matrix can be prepared as described herein and then dehydrated to form a single mass.
  • the single mass can then be customized for specific uses.
  • the dehydrated hydrogel matrix could be sliced into wafer-like slices of varying dimensions.
  • the dehydrated hydrogel matrix could also be ground to a particulate form.
  • the dehydrated hydrogel matrix could also be cut to various shapes and dimensions for specified uses, such as pre-formed plugs for use in bone cavitation.
  • the dehydrated bioactive hydrogel matrix could be formed to a standardized shape and size and packaged for various uses.
  • the pre-packaged dehydrated bioactive hydrogel matrix could then be customized to a desired shape and size at the time of use.
  • the dehydrated hydrogel matrix can be shaped around a central mandrel to form porous tubes useful for tissue regenerative guidance conduits. These can be wrapped around specific sites which may require or benefit from guided tissue regeneration. Dehydrated hydrogels can also be partially rehydrated to form putties and pastes appropriate for filling bony voids caused by surgery or trauma.
  • the dehydrated hydrogel matrix when re-hydrated, retains is connective tissue regenerative properties as described herein and can be used according to the methods of the invention as effectively as a freshly prepared bioactive hydrogel matrix of the invention.
  • the re-hydration of the hydrogel matrix can be performed according to various methods, all of which are encompassed by the invention.
  • the dehydrated bioactive hydrogel matrix is re-hydrated immediately prior to use, such as by contacting with water or a physiologically compatible buffer solution, such as Medium 199.
  • the dehydrated bioactive hydrogel matrix could be placed in the site in need of connective tissue regeneration and then contacted with re-hydrating fluids, such as water or a physiologically compatible buffer solution.
  • the dehydrated hydrogel matrix could be placed in the site in need of connective tissue regeneration and then re-hydrated through contact with natural body fluids.
  • bioactive hydrogel matrix of the present invention is useful in multiple types of tissue repair, it is particularly advantageous in areas where tissue repair or regeneration is especially difficult. As described previously, such is often the case with bone regeneration and repair of non-bone connective tissue.
  • Connective tissue is a generalized term for mesodermally derived tissue that may be more or less specialized. Many types of tissue can fall under the term, such as bone, cartilage, dura mater, tendon, and ligament. The term can also be used for less specialized tissue that is rich in components such as collagen and proteoglycans, and that surrounds other more highly ordered tissues and organs.
  • the bioactive hydrogel matrix is especially useful in the regeneration of bone, particularly in situations where bone repair does not occur or where more rapid healing of a bone defect would be beneficial to a patient.
  • the bioactive hydrogel matrix can be inserted into the area of the bone loss and allowed to remain in place to facilitate healing of the wound and regeneration of bone in the area of the loss.
  • the matrix provides multiple regenerative functions as described above.
  • the matrix interacts with osteocytes leading to more rapid formation of bone tissue.
  • the matrix also promotes osteoblast gene expression as demonstrated by the increased production of BMP-2.
  • the presence of the matrix in the wound site also inhibits ingrowth of non-bone tissue into the wound inhibiting the formation of new bone tissue.
  • the presence of the matrix also promotes vascularization, which is necessary for the rapid growth of new bone tissue in providing nutrients, growth factors, oxygen, and other components necessary to bone regeneration.
  • stem cells are found in bone marrow, and these adult stem cells can be induced to differentiate into bone tissue or other types of connective tissue, including cartilage, and important adjacent tissues, such as neurons and skeletal muscle.
  • progenitor cells which are precursors giving rise to cells of a particular cell type, are also useful for inducing bone tissue growth, or other connective tissue growth, where applicable.
  • interacting with those cells in the areas surrounding bone injury could stimulate stem or progenitor cells in the injured area to differentiate into bone cells, further hastening the regeneration of the bone.
  • the present invention in one aspect, is a method for regenerating connective tissue comprising administering a bioactive hydrogel matrix comprising a polypeptide and a long chain carbohydrate, as described herein, to a site in need of connective tissue regeneration.
  • a bioactive hydrogel matrix comprising a polypeptide and a long chain carbohydrate, as described herein, to a site in need of connective tissue regeneration.
  • the polypeptide is a gelatin
  • the long chain carbohydrate is dextran.
  • the bioactive hydrogel matrix as used in the method of the invention can include one or more of the additional components previously noted herein. Additionally, the bioactive hydrogel matrix can incorporate further components facilitating the regeneration of connective tissue according to the method of the invention.
  • the present invention provides various connective tissue regenerative compositions.
  • the compositions comprise a bioactive hydrogel matrix as described herein and at least one additional component useful for accomplishing the methods of the invention. Accordingly, any of the compositions described herein can be used in the various methods of the invention.
  • the bioactive hydrogel matrix further comprises at least one osteoinductive or osteoconductive material.
  • osteoinductive is meant materials that lead to a mitogenesis of undifferentiated perivascular mesenchymal cells leading to the formation of osteoprogenitor cells (i.e., cells with the capacity to form new bone).
  • osteoconductive is meant materials that facilitate blood vessel incursion and new bone formation into a defined passive trellis structure. Various compounds, minerals, proteins, and the like are known to exhibit osteoinductive or osteoconductive activity. Accordingly, any of such materials would be useful according to the present invention.
  • any of the following could be used for their osteoinductive or osteoconductive ability according to the present invention: demineralized bone matrix (DBM), bone morphogenetic proteins (BMPs), transforming growth factors (TGFs), fibroblast growth factors (FGFs), insulin-like growth factors (IGFs), platelet-derived growth factors (PDGFs), epidermal growth factors (EGFs), vascular endothelial growth factors (VEGFs), vascular permeability factors (VPFs), cell adhesion molecules (CAMs), calcium aluminate, hydroxyapatite, coralline hydroxyapatite, alumina, zirconia, aluminum silicates, calcium phosphate, tricalcium phosphate, calcium sulfate, polypropylene fumarate, bioactive glass, porous titanium, porous nickel-titanium alloy, porous tantalum, sintered cobalt-chrome beads, ceramics, collagen, autologous bone, allogenic bone, xenogenic bone, coralline, and derivates
  • alumina is meant the commonly held definition of materials comprised of the natural or synthetic oxide of aluminum, which may be exemplified in various forms, such as corundum.
  • Bioactive glasses generally contain silicon dioxide (SiO 2 ) as a network former and are characterized by their ability to firmly attach to living tissue.
  • bioactive glasses available commercially and their manufacturers include Bioglass® (American Biomaterials Corp., USA, 45% silica, 24% calcium oxide (CaO), 24.5% disodium oxide (Na 2 O), and 6% pyrophosphate (P 2 O 5 )), Consil® (Xeipon Ltd., UK), NovaBone® (American Biomaterials Corp.), Biogran® (Orthovita, USA), PerioGlass® (Block Drug Co., USA), and Ceravital® (E.Pfeil & H. Bromer, Germany). Corglaes® (Giltech Ltd., Ayr, UK) represents another family of bioactive glasses containing pyrophosphate rather than silicon dioxide as a network former. These glasses contain 42-49 mole % of P 2 O 5 , the remainder as 10-40 mole % as CaO and Na 2 O.
  • the osteoinductive or osteoconductive material is preferably present at a volume concentration of about 0.01 percent to about 90 percent based upon the total volume of the connective tissue regenerative composition. Such concentration is further dependent upon the ability to form compositions having suitable putty or paste-like properties.
  • the osteoinductive or osteoconductive material is present at a volume concentration of about 50 percent to about 80 percent, based upon the total volume of the connective tissue regenerative composition.
  • a composition according to the invention comprises a 75% volume/volume mixture of osteoinductive or osteoconductive material, such as calcium sulfate, and bioactive hydrogel matrix (e.g., 12 mL calcium sulfate to 4 mL hydrogel matrix).
  • osteoinductive or osteoconductive material such as calcium sulfate
  • bioactive hydrogel matrix e.g., 12 mL calcium sulfate to 4 mL hydrogel matrix
  • the bioactive hydrogel matrix and the osteoinductive or osteoconductive materials can be variously combined.
  • the osteoinductive or osteoconductive materials and the hydrogel matrix are in admixture, which can be according to any means generally known to one of skill in the art.
  • the bioactive hydrogel matrix could be prepared, and the osteoinductive or osteoconductive material (e.g., powdered calcium phosphate) could be poured into and mixed into the hydrogel matrix by mechanical mixing means. The mixture could be flowable or could be substantially thickened to a putty or paste-like consistency.
  • the bioactive hydrogel matrix could be dehydrated and, preferentially, in particulate or pelletized form.
  • the particulate dehydrated bioactive hydrogel matrix could be mixed with an osteoinductive or osteoconductive material to form a substantially uniform mixture.
  • the osteoinductive or osteoconductive material could be in the form of a putty or paste, and the particulate dehydrated bioactive hydrogel matrix kneaded or otherwise mixed therein.
  • the bioactive hydrogel matrix of the invention can further comprise at least one medicament useful for treating patients having connective tissue damage or in need of connective tissue regeneration.
  • the medicament can be any medicament useful in facilitating the healing and regenerative process.
  • medicaments useful according to the invention include, but are not limited to, antivirals, antibacterials, anti-inflammatories, immunosuppressants, analgesics, anticoagulants, and wound healing promotion agents.
  • the bioactive hydrogel matrix can further comprise stem or progenitor cells, such as ADAS cells, which are known to be capable of differentiating into adipogenic, osteogenic, chondrogenic, and myogenic lineages.
  • stem or progenitor cells such as ADAS cells, which are known to be capable of differentiating into adipogenic, osteogenic, chondrogenic, and myogenic lineages.
  • stem or progenitor cells can be beneficial for stimulating and increasing connective tissue regrowth, particularly bone and cartilage.
  • the presence of the stem or progenitor cells can be beneficial for stimulating and increasing growth of surrounding tissue, providing support for the damaged connective tissue.
  • stem or progenitor cells are present at a concentration of about 10,000 to about 1,000,000 cells per ml of hydrogel matrix, more preferably about 50,000 to about 750,000 cells per ml of hydrogel matrix, most preferably about 100,000 to about 500,000 cells per ml of hydrogel matrix. In one particular embodiment, the final concentration is about 250,000 cells per ml of hydrogel matrix.
  • the bioactive hydrogel matrix includes stem cells and progenitor cells.
  • the progenitor cells are osteoprogenitor cells.
  • the bioactive hydrogel matrix could be in a particulate, dehydrated form and the particles mixed into a solution containing stem or progenitor cells, such as ADAS or mesenchymal stem cells.
  • the bioactive hydrogel matrix includes a three-dimensional structural framework.
  • the bioactive hydrogel matrix of the present invention becomes flowable at physiological temperatures.
  • the bioactive hydrogel matrix it is beneficial, in certain embodiments, for the bioactive hydrogel matrix to include structural components.
  • the bioactive hydrogel matrix is at least partially contained within the three-dimensional structural framework. Accordingly, the structural framework can take on various embodiments.
  • the three-dimensional structural framework includes a scaffold or cage-like structure at least partially containing the bioactive hydrogel matrix.
  • a scaffold or cage-like structure at least partially containing the bioactive hydrogel matrix.
  • the scaffold or cage-like structure spans the area of bone loss and encloses the bioactive hydrogel matrix within the area of bone loss.
  • the three-dimensional structural framework could be a cylindrical metal mesh, such as titanium mesh.
  • the three-dimensional structural framework can include materials that are non-bioreabsorbable (i.e., persist in the body in a virtually unchanged state or must be later removed).
  • the three-dimensional structural framework includes a bioreabsorbable material that persists in the body long enough to perform its structure-providing function, later being broken down through natural body processes or being incorporated into the newly formed bone.
  • the three-dimensional structural framework includes calcium-containing or calcified materials easily incorporated into newly formed bone.
  • the three-dimensional structural framework is at least partially internal to the bioactive hydrogel matrix.
  • the three-dimensional structural framework preferably comprises a material capable of physically or chemically interacting with the hydrogel matrix.
  • the three-dimensional structural framework provides an array of structural formations for providing support and structure to the bioactive hydrogel matrix.
  • the three-dimensional structural framework be a structure that provides support and simultaneously provides a space, or network of spaces, for cellular infiltration. It is particularly beneficial for the three-dimensional structural framework to include a porous structure, such as a collagen or gelatin sponge. Any commercially available collagen sponge would be useful generally in the present invention. Examples of commercially available collagen sponges include the Avitene UltrafoamTM collagen sponge (available from Davol, Inc., a subsidiary of C.R.
  • the three-dimensional structural framework can be a single unit having an inherent three-dimensional structure.
  • the structural framework can be shaped as desired to precisely fit into the site in need of connective tissue regeneration. This is particularly beneficial in cases of long segmental diaphyseal bone loss or bone cavitation.
  • the structural framework can be precisely shaped and sized to the bone loss segment or cavitation to fill the space.
  • the bioactive hydrogel matrix is retained in the bone loss segment or cavitation for an extended time period to facilitate bone regeneration by being at least partially contained within the structural framework.
  • the structural framework, with the hydrogel matrix contained therein can optionally be sutured into place.
  • the three-dimensional structural framework can comprise various materials useful for providing structure and support and having an inherent three dimensional structure.
  • the three-dimensional structural framework can be a structure substantially in the form as found in nature, such as coralline or natural sponge. Further, the three-dimensional structural framework can be a fabricated structure made from materials not naturally exhibiting a three-dimensional structure but being formed into such a structure, such as, for example, sintered calcium phosphate.
  • the three-dimensional structural framework can comprise one or more polymeric materials that have been made, through processing (such as casting, molding, or sintering), into a three-dimensional structure, particularly having a series or network of pores or cavities throughout the structure for allowing cellular infiltration.
  • a three-dimensional structural framework examples include, but are not limited to, metals, calcium salts, coralline, bioactive glass, sponges, ceramics, collagen, keratin, fibrinogen, alginate, chitosan, hyaluronan, and other biologically-derived polymers.
  • the three-dimensional structural framework can also comprise degradable and non-degradable polymers, such as those commonly used in tissue engineering applications.
  • non-degradable polymers include polyethylene, poly(vinylidene fluoride), poly(tetrafluoroethylene), poly(vinyl alcohol), poly(hydroxyalkanoate), poly(ethylene terephthalate), poly(butylene terephthalate), poly(methyl methacrylate), poly(hydroxyethyl methacrylate), poly(N-isopropylacrylamide), poly(dimethyl siloxane), polydioxanone, and polypyrrole.
  • Exemplary degradable polymers include poly(glycolic acid), poly(lactic acids), poly(ethylene oxides), poly(lactide-co-glycolides), poly(s-caprolactone), polyanhydrides, polyphosphazenes, poly(ortho-esters), and polyimides.
  • the three-dimensional structural framework comprises a crosslinked hydrogel matrix.
  • a crosslinked bioactive hydrogel matrix comprising a polypeptide, such as gelatin, and a long-chain carbohydrate, such as dextran.
  • FIG. 8 An example of a crosslinked bioactive hydrogel matrix comprising dextran and gelatin is provided in FIG. 8 wherein dextran 20 is covalently crosslinked to gelatin 15 by linkages 70 , thereby forming a crosslinked network 50 .
  • the linkages 70 either result from reaction of functional groups on the gelatin 15 with functional groups on the dextran 20 , or result from reaction of a bifunctional crosslinker molecule with both the dextran 20 and gelatin 15 .
  • one method of crosslinking gelatin and dextran is to modify the dextran molecules 20 , such as by oxidation, in order to form functional groups suitable for covalent attachment to the gelatin 15 .
  • This stabilized cross-linked bioactive network 50 yields therapeutically useful gels and pastes that are insoluble in physiologic fluids at physiological temperatures.
  • Crosslinked hydrogel matrices as useful according to the present invention can be prepared by various methods.
  • one of the polypeptides and long chain carbohydrates is modified to form reactive groups suitable for crosslinking.
  • the dextran or other long chain carbohydrate component can be modified, such as by oxidation, in order to cross-link with the polypeptide component.
  • One known reaction for oxidizing polysaccharides is periodate oxidation.
  • the basic reaction process utilizing periodate chemistry is well known and appreciated by those skilled in the art.
  • Periodate oxidation is described generally in Affinity Chromatography: A Practical Approach , Dean, et al., IRL Press, 1985 ISBN0-904147-71-1, which is incorporated by reference in its entirety.
  • the oxidation of dextran by the use of periodate-based chemistry is described in U.S. Pat. No. 6,011,008, which is herein incorporated by reference in its entirety.
  • polysaccharides may be activated by the oxidation of the vicinal diol groups.
  • long chain carbohydrates such as dextran
  • this is generally accomplished through treatment with an aqueous solution of a salt of periodic acid, such as sodium periodate (NaIO 4 ), which oxidizes the sugar diols to generate reactive aldehyde groups (e.g. dialdehyde residues).
  • NaIO 4 sodium periodate
  • This method is a rapid, convenient alternative to other known oxidation methods, such as those using cyanogen bromide.
  • Dextran activated by periodate oxidation may be stored at 4° C. for several days without appreciable loss of activity.
  • a Schiff base is a name commonly used to refer to the imine formed by the reaction of a primary amine with an aldehyde or ketone.
  • the aldehyde groups formed on the cellulosic surface react with most primary amines between pH values from about 4 to about 6.
  • the Schiff's base links form between the dialdehyde residues of the dextran and the free amino groups on the gelatin.
  • the crosslinked product may subsequently be stabilized (i.e.
  • borohydride such as sodium borohydride (NaBH 4 ) or sodium cyanoborohydride (NaBH 3 CN).
  • NaBH 4 sodium borohydride
  • NaBH 3 CN sodium cyanoborohydride
  • the residual aldehyde groups may be consumed with ethanolamine or other amine containing species to further modify the crosslinked matrix.
  • Other methods known to those skilled in the art may be utilized to provide reactive groups on either one or both of the polypeptide and long-chain carbohydrate.
  • periodate chemistry is preferentially used with dextran to form a multifunctional polymer that can then react with gelatin and other components, such as polar amino acids, present during the manufacturing process.
  • the periodate reaction leads to the formation of polyaldehyde polyglycans that are reactive with primary amines.
  • polypeptides and long chain carbohydrates may form covalent hydrogel complexes that are colloidal or covalently crosslinked gels.
  • Covalent bonding occurs between reactive groups of the dextran and reactive groups of the gelatin component.
  • the reactive sites on the gelatin include amine groups provided by arginine, asparagine, glutamine, and lysine.
  • hydrogels can be readily prepared at temperatures from about 34° C. to about 90° C. Additionally, the hydrogels can be prepared at a pH range of from about 5 to about 9, preferably from about 6 to about 8, and most preferably from about 7 to about 7.6.
  • biomimetic scaffolding materials By controlling the extent of dextran activation and the reaction time, one can produce stabilized biomimetic scaffolding materials of varying viscosity and stiffness.
  • biomimetic is intended compositions or methods imitating or simulating a biological process or product. Some biomimetic processes have been in use for several years, such as the artificial synthesis of vitamins and antibiotics. More recently, additional biomimetic applications have been proposed, including nanorobot antibodies that seek and destroy disease-causing bacteria, artificial organs, artificial arms, legs, hands, and feet, and various electronic devices.
  • the biomimetic scaffolding materials of the present invention yield therapeutically useful gels and pastes that are stable at about 37° C., or body temperature.
  • biomimetic crosslinked hydrogel matrices are particularly useful as a three-dimensional structural framework as described herein.
  • the crosslinked hydrogel matrix provides the structure and support required, remains stable and maintains its three-dimensional structure at physiological temperatures, and can remedially provide many of the same connective tissue regenerative properties of the non-crosslinked bioactive hydrogel matrix of the invention.
  • a multifunctional crosslinking agent may be utilized as a reactive moiety that covalently links the gelatin and dextran chains.
  • Such bifunctional crosslinking agents may include glutaraldehyde, epoxides (e.g., bis-oxiranes), oxidized dextran, p-azidobenzoyl hydrazide, N-[ ⁇ -maleimidoacetoxy]succinimide ester, p-azidophenyl glyoxal monohydrate, bis-[ ⁇ -(4-azidosalicylamido)ethyl]disulfide, bis[sulfosuccinimidyl]suberate, dithiobis[succinimidyl proprionate, disuccinimidyl suberate, 1-ethyl-3-[3-dimethylaminopropyl]carbodiimide hydrochloride, and other bi
  • polyacrylated materials such as ethoxylated (20) trimethylpropane triacrylate
  • ethoxylated (20) trimethylpropane triacrylate may be used as a non-specific photo-activated crosslinking agent.
  • Components of an exemplary reaction mixture would include a thermoreversible hydrogel held at 39° C., polyacrylate monomers, such as ethoxylated (20) trimethylpropane triacrylate, a photo-initiator, such as eosin Y, catalytic agents, such as 1-vinyl-2-pyrrolidinone, and triethanolamine. Continuous exposure of this reactive mixture to long-wavelength light (>498 nm) would produce a crosslinked hydrogel network.
  • the crosslinked hydrogel matrix can further comprise various additional components (in addition to the polypeptide and long chain carbohydrate) to enhance the crosslinked matrix by providing further stability or functional advantages.
  • additional components can include any compound, especially polar compounds, that, when incorporated into the crosslinked hydrogel matrix, enhance the hydrogel matrix by providing further stability or functional advantages.
  • Preferred additional components for use with the stabilized crosslinked hydrogel matrix include polar amino acids, polar amino acid analogues and derivatives, intact collagen, and divalent cation chelators. Suitable concentrations of each particular preferred additional component are the same as noted above in connection with the bioactive hydrogel matrix of the present invention. Polar amino acids, EDTA, and mixtures thereof, are particularly preferred.
  • the additional components can be added to the hydrogel matrix composition before or during the crosslinking of the polypeptide and long chain carbohydrate.
  • the bioactive hydrogel matrix of the invention is in a crosslinked form, the three-dimensional structural framework thus being inherent to the hydrogel matrix itself.
  • the bioactive hydrogel matrix of the invention is first prepared, and the three-dimensional structural framework, in the form of a separate, crosslinked hydrogel matrix, as described above, is added to the non-crosslinked hydrogel matrix.
  • Such addition can include physical admixture of the two hydrogels to form a composition comprising a bioactive hydrogel matrix of the invention and a three-dimensional structural framework, in the form of a crosslinked hydrogel matrix.
  • dehydrated cross-linked bioactive hydrogel matrix formulations can be used with the non-crosslinked hydrogel matrix or for providing structural support generally.
  • the non-crosslinked hydrogel matrix can be mixed with dehydrated crosslinked hydrogel matrix in the form of disks, rods, cylinders, granules, or other suitable geometric forms.
  • Such compositions provide additional support to the surrounding tissue, and increase the localized residence time of the non-crosslinked hydrogel matrix.
  • the bioactive hydrogel matrix/three-dimensional structural framework composition could also include osteoinductive or osteoconductive materials, stem or progenitor cells (such as ADAS or mesenchymal stem cells), or medicaments as described herein.
  • stem or progenitor cells such as ADAS or mesenchymal stem cells
  • medicaments as described herein.
  • any of these combinations could be used according to the methods of the invention.
  • bioactive hydrogel matrix includes a three-dimensional structural framework
  • methods of the invention wherein the bioactive hydrogel matrix includes a three-dimensional structural framework are intended to encompass situations wherein the three-dimensional structural framework is included with the bioactive hydrogel matrix prior to administration of the composition. Further, the methods encompass situations wherein the three-dimensional structural framework is included with the bioactive hydrogel matrix after administration of the bioactive hydrogel matrix.
  • the methods and compositions of the invention as described herein are useful in the repair and regeneration of connective tissue, particularly bone, cartilage, ligament, and the like. As such, the methods and compositions of the invention are particularly useful in various treatments involving portions of the human body particularly susceptible to connective tissue damage or degeneration.
  • the bioactive hydrogel matrix can be used in the surgical attachment or reattachment of one or more connective tissues. Because of the generally decreased vascularization of connective tissue types, healing times related to injury repair are typically long in duration. Administration of the bioactive hydrogel matrix to the injured site during repair of the connective tissue damage can improve integration of the tissues resulting in a much stronger repair and decreased healing time. This is particularly true in the reattachment of tendon or ligament to bone. Similar effects would be expected in the repair of torn ligaments or torn tendons.
  • the present invention provides a method for reattaching connective tissues to one another.
  • the method generally comprises coating at least a portion of at least one of the connective tissues with the bioactive hydrogel matrix according to any of the various embodiments of the present invention, contacting the connective tissues, and, optionally, suturing the connective tissues together.
  • suturing or use of other attachment aids, such as staples, glues, and adhesive strips
  • at least a portion of the bioactive hydrogel matrix can be in crosslinked form.
  • the improved repair/regeneration supplied by the bioactive hydrogel matrix would be beneficial to a large number of patients. While relatively moderate numbers of patients suffer from large areas of bone loss, the matrix could also be used to treat injuries that are very common in occurrence, such as a torn anterior cruciate ligament (ACL), rotator cuff injuries, damaged cartilage in knees and other joints, and other such injuries that would be readily obvious to one of ordinary skill in the art.
  • ACL anterior cruciate ligament
  • rotator cuff injuries damaged cartilage in knees and other joints, and other such injuries that would be readily obvious to one of ordinary skill in the art.
  • bioactive hydrogel matrix of the invention further would be expected to be beneficial for improved performance of any bioreabsorbable tissue anchors.
  • the bioactive hydrogel matrix could be used in a combination therapy with other known reattachment devices.
  • a torn connective tissue such as a tendon
  • sutures, staples, glues, or the like could be reattached using sutures, staples, glues, or the like, with at least one piece of the torn connective tissue being coated at the area of the tear with a bioactive hydrogel matrix of the present invention to facilitate re-growth of connective tissue at the injury site and hasten reattachment of the connective tissue.
  • the matrix is useful in treating degenerative diseases, such as osteoarthritis, of the natural joint of a patient.
  • Osteoarthritis is characterized by degeneration of the articular cartilage, hypertrophy of bone at the margins, and changes in the synovial membrane of the affected joint.
  • Treatment of the affected joint with the bioactive hydrogel matrix of the invention, especially prior to complete loss of cartilage in the joint, can stabilize the progression of the degeneration and even promote repair/regeneration of cartilage within the joint and regeneration of marginal bone structure.
  • the bioactive hydrogel matrix of the invention provides an effective, minimally invasive treatment, the hydrogel matrix being capable of injection directly into the affected joint.
  • the bioactive hydrogel matrix can be in many of the various compositions as provided herein.
  • the bioactive hydrogel matrix further comprises one or more medicaments, osteoinductive or osteoconductive materials, or stem or progenitor cells.
  • the bioactive hydrogel matrix is useful in promoting the healing and effectiveness of artificial joint replacements.
  • the matrix is inserted into the area surrounding the artificial joint, particularly where the artificial joint is in contact with the natural tissue of the patient.
  • the hydrogel matrix facilitates the integration of the artificial joint into the surrounding tissue promoting faster healing of the surgical site and greater duration of the effectiveness of the artificial joint.
  • a therapeutic amount of the matrix of the invention is administered to a patient suffering from connective tissue injury, particularly an injury to bone, cartilage, tendon, or ligament.
  • the patient can be any animal, including mammals such as dogs, cats and humans.
  • the term “therapeutic amount” refers to the amount required to promote tissue repair/regeneration as evidenced by, for example, the formation of new bone tissue across an area previously lacking in bone tissue.
  • the therapeutic amount will be primarily determined by the size and type of injury being treated.
  • the volume of bioactive hydrogel matrix applied is about 1 to about 60 mL, but could be greater, especially in large injuries, such as, for example, an area of great bone loss in a large bone, such as a femur.
  • the therapeutic amount is sufficient to provide a uniform scaffolding for cellular attachment and differentiation in the area where tissue regeneration is needed.
  • the non-crosslinked version of the hydrogel matrix is typically warmed to a temperature of about 35 to about 40° C. prior to administration in order to liquefy the matrix.
  • the bioactive hydrogel matrix used according to the methods of the present invention for regenerating connective tissue may be comprised solely of the polypeptide and long chain carbohydrate as described herein.
  • the hydrogel matrix may incorporate additional components, such as the polar amino acids, polar amino acid analogues and derivatives, and cation chelators, as described above.
  • Table 1 below lists particularly preferred components of the matrix of the present invention along with suitable concentrations as well as preferred concentrations for each component. Note that the concentrations listed in Table 1 for gelatin and dextran would also be suitable for alternative polypeptide and long chain carbohydrate components.
  • Bioactive hydrogel matrices prepared having the preferred components and concentrations provided in Table 1 would also be particularly suitable for use in the preparation of any of the connective tissue regenerative compositions as described herein.
  • the bioactive hydrogel matrix was compounded to yield a final formulation as described above in Table 1.
  • Modified Medium 199 (2.282 L) was placed into a stirred beaker. To the beaker were added L-cysteine, L-glutamic acid, L-lysine, L-alanyl-L-glutamine, and EDTA. While stirring, the solution was heated to 50° C. Next, dextran was added, followed by the addition of gelatin. NaOH (10%) was used to adjust the pH of the matrix solution to a final pH of 7.50 ⁇ 0.05. Finally, additional L-glutamic acid, L-arginine, and L-cysteine were added followed by the addition of zinc sulfate. The amounts of each component used were the amounts necessary to bring the final concentration of each component to the preferred concentration provided in Table 1.
  • the in vivo effect of the matrix on bone repair was examined using the critical size defect model in the rabbit ulna.
  • a defect in a rabbit ulna was created in which the length of the defect was purposefully made to be three times the diameter of the bone, i.e., a 15 mm defect was created in each ulna (the diameter of the bone was approximately 4 mm). It is well documented in the literature that defects of this size will not spontaneously heal (i.e., a critical size defect).
  • Seven rabbits had 15 mm defects surgically created in the ulna of each forelimb. Further, the periosteum of the radius parallel to the defect was scraped off.
  • the defect in one forelimb was treated with the bioactive hydrogel matrix, and the other was treated with a collagen sponge soaked with the bioactive hydrogel matrix. The muscle surrounding the bone defect was sutured closed and the limb tightly wrapped.
  • the forelimbs of the rabbit were x-rayed to document the size of the defect, with follow-up X-rays taken at two-week intervals to 10 weeks of total testing.
  • Micro CT scans and histological examination were also performed at 10 weeks. Radiographs of defect sites were scored for calcification on a 0 to 4 scale. Mineralization within the defect treated with the bioactive hydrogel matrix alone in combination with the collagen sponge was noted as early as two weeks after the procedure, and by six weeks, clear and dramatic mineralization was evident within the area of removed bone.
  • the bioactive hydrogel matrix in the collagen sponge tended to increase calcification compared to the hydrogel matrix alone, but the differences were not statistically significant. New bone formation within the defects was confirmed by both micro CT scans and histopathology performed at 10 weeks.
  • the tendons treated with the bioactive hydrogel matrix appeared thicker than the control tendons. Further, the tendons treated with the bioactive hydrogel matrix had an average increase in stiffness over the control tendons of about 17.2% compared to a decrease of 4.5% in stiffness of the 2 tendons treated with the collagen sponge soaked with saline.
  • Human osteosarcoma cells were plated in T75 flasks, allowed to grow to confluency, and then shifted to serum-free medium (SFM) for three days. At this point cultures were treated for 40 minutes at 37° C. with either the bioactive hydrogel matrix of the invention or serum-free medium as a control. Cultures were rinsed and re-fed with serum-free medium and sampled over a subsequent 24 hour period for extraction of nucleic acids. Messenger RNA from these preparations was used to create complementary DNA using reverse transcription, and specific DNA sequences were amplified and quantified using real-time polymerase chain reaction methods.
  • SFM serum-free medium
  • BMP-2 bone morphogenetic protein-2
  • BMP-2 protein was also measured in these cell cultures following identical culture and hydrogel matrix treatment methods, with the exception that serum-containing medium (SCM) was used to avoid loss of analyte by adsorption to culture surfaces.
  • SCM serum-containing medium
  • cultures were sampled over a 3-day period following either 40 or 120-minutes treatment by removal of medium and snap freezing the culture to release cell-associated protein for analysis. Resulting samples were analyzed by enzyme-linked immunosorbent assay (ELISA) using a commercial BMP-2 detection kit (R&D Systems, Minneapolis, Minn.).
  • ELISA enzyme-linked immunosorbent assay
  • treatment with the bioactive hydrogel matrix increased BMP-2 protein levels over controls within 24 hours post-treatment and provided as much as a 3-fold increase over controls by day 3.
  • a putty containing 2.4 g calcium sulfate and 1.5 g demineralized bone matrix (DBM) was prepared and used to incorporate particulate dehydrated bioactive hydrogel matrix. After briefly hand-kneading the material, about 0.5 g of particulate dehydrated bioactive hydrogel matrix (equivalent to about 3 mL of fully hydrated hydrogel matrix) was incorporated into the putty. The putty was mixed and kneaded to uniformity, and the putty retained the ability to fill a bony defect created in a synthetic bone.
  • DBM demineralized bone matrix
  • an injectable calcium sulfate formulation was prepared using the bioactive hydrogel matrix of the invention rather than the conventional water base (12 g calcium sulfate powder and 4 mL of the bioactive hydrogel matrix).
  • the material had a prolonged set time (over 2 hours to solidify), and during the early stages of setting was judged to be suitable for filling a bony defect.
  • the bioactive hydrogel matrix was mixed with a granulated tricalcium phosphate ceramic to form a moldable putty easily packed into a bony defect.

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US20120328700A1 (en) 2012-12-27
US20080145404A1 (en) 2008-06-19
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CA2543255C (fr) 2014-08-12
EP1677846B1 (fr) 2014-08-20
US20090124552A1 (en) 2009-05-14
US20120321597A1 (en) 2012-12-20
WO2005042048A2 (fr) 2005-05-12
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AU2004285480A1 (en) 2005-05-12
US8883184B2 (en) 2014-11-11

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