Patent Grant
10245306
Defects of articular joints are significant sources of pain, discomfort and disability. These defects, such as full-thickness chondral defects, may be associated with osteoarthritis or other disease, traumatic injury and/or age or use-related degeneration of articular cartilage. Morbidity associated with defects of hyaline cartilage comprised by articular joints is responsible for significant economic, health and social costs.
Current treatments for repair or amelioration of joint problems include microfracture, abrasion and drilling. These interventions involve exposing a joint containing a defect to mesenchymal stem cells. As a result of such interventions, the mesenchymal stem cells may infiltrate the defect, and differentiate into fibrocartilage over time. However, fibrocartilage has a structure and molecular composition distinct from that of the hyaline cartilage found in joints. Fibrocartilage generally provides only short-term improvement, typically lasting less than two years. Alternative treatments are, therefore, needed.
In one aspect, the present disclosure provides a tissue matrix for supporting repair of biological tissues comprising a high molecular weight caprolactone polymer entangled with a polysaccharide. The high molecular weight caprolactone polymer may be selected from polycaprolactone; a co-polymer of polylactic acid and polycaprolactone; a co-polymer of polyglycolic acid and polycaprolactone; a copolymer of polylactic acid, polyglycolic acid, and polycaprolactone; a co-polymer of polyethylene glycol, polylactic acid and polycaprolactone; a co-polymer of polyethylene glycol, polyglycolic acid and polycaprolactone; and a copolymer of polyethylene glycol, polylactic acid, polyglycolic acid, and polycaprolactone A tissue matrix may further include at least one flexibility agent. The flexibility agent may be selected from triethyl citrate, acetyl tributyl citrate, acetyl triethyl citrate, tributyl citrate, trimethyl citrate, trihexyl citrate, acetyl trihexyl citrate, trioctyl citrate, acetyl trioctyl citrate and any combination thereof. Alternatively, the flexibility agent may be selected from polyethylene glycol, polyethylene glycol monoalkyl ether, propylene glycol, glycerin, triacetin and any combination thereof. In a tissue matrix, the polysaccharide may comprise hyaluronic acid polymers. A tissue matrix may further include at least one growth factor which may be for example a bone morphogenetic protein. A growth factor may be an isolated growth factor previously isolated from allogenic bone. A growth factor may be selected from basic fibroblast growth factor (bFGF), transforming growth factor (TGF-β), BMP-2, ADMP-1, a hedgehog protein, an insulin-like growth factor, a platelet-derived growth factor, an interleukin, a colony-stimulating factor, and an activin. A tissue matrix may further include a type I collagen or a type II collagen. A tissue matrix may be combined at a defect site in a joint with a DBM composition, crushed bone, or allogenic bone. A tissue matrix may be formed as a membrane, such as for example a membrane having a thickness of at least about 0.5 mm up to about 3 mm.
In another aspect, the present disclosure a method for repairing a hyaline cartilage defect in a joint in a mammal, the method comprising: infiltrating the joint with autologous mesenchymal stem cells; and applying to the joint a membrane comprising any tissue matrix as described in the foregoing which comprises a high molecular weight caprolactone polymer entangled with a polysaccharide. Infiltrating the joint with autologous mesenchymal stem cells may involved for example introducing at least one aperture into the bone underlying the joint, wherein the at least one aperture is sufficiently large to allow migration of the autologous bone mesenchymal stem cells from the bone marrow cavity to the joint. Introducing an aperture into bone underlying the joint may involve, for example, abrading, microfracturing or drilling the bone underlying the hyaline cartilage defect. The hyaline cartilage defect may include a full-thickness chondral defect. Applying the membrane to the joint may precede infiltrating the joint with autologous mesenchymal stem cells or alternatively, infiltrating the joint with autologous mesenchymal stem cells may precede applying the membrane to the joint. The method may further include securing the membrane to the joint, for example by attaching at least one fastener to the membrane and the joint. A fastener may be a biocompatible glue such as a fibrin glue, a suture, a tissue weld, a dart, a staple, a screw, or a tack. The method may further include applying to the joint a DBM composition, crushed bone and/or allogenic bone.
In another aspect the present disclosure provides a method for repairing a full-thickness chondral defect in a joint of a patient in need of such repair, the method comprising: microfracturing bone underlying the joint; applying to the joint a membrane comprising a tissue matrix comprising a high molecular weight caprolactone polymer entangled with a polysaccharide, wherein the membrane has a thickness of at least about 0.5 mm up to about 3 mm; and anchoring the membrane to the joint. The joint may be for example a knee joint.
The present disclosure describes a synthetic, flexible tissue matrix for supporting tissue repair, which is composed of certain high molecular weight polymers entangled with a polysaccharide, and optionally includes small molecule flexibility agents.
Surprisingly, the high molecular weight polymers, when entangled with a polysaccharide such as hyaluronic acid polymers through a dual solvent emulsion process, form matrices with the following beneficial aspects relative to a tissue matrix which includes only polylactic acid (PLA) polymers, polyglycolic acid (PGA) polymers, or polymers consisting of a co-polymer of polylactic and polyglycolic acid (PLGA) entangled with hyaluronic acid polymers: 1) increased flexibility at temperatures usually encountered in operating theater (e.g., 15 to 20° C.), while retaining the compressive resistant nature of the matrix; 2) increased aqueous absorption at physiological temperatures while maintaining a good dissolution profile relevant to the time scales for tissue regeneration; and 3) reductions in the appearance of a shiny surface on the strips of matrix, which in other matrices which incorporate only PLA, PGA or PLGA polymers result in migration of hyaluronic acid away from one surface during the manufacturing process.
The observed improved flexibility avoids or reduces the need to further treat or manipulate the tissue matrix in the surgical environment. In contrast, a tissue matrix using only PLA, PGA or PLGA polymers is relatively brittle under these surgical conditions, and thus requires some form of additional heating to facilitate its use. Without being bound by theory, it is believed that the increased absorbency of the improved tissue matrices described herein may be related to an improved ability for these matrices to imbibe and attach cellular component and further tissue formation.
The flexible tissue matrix can be used in methods for repairing a full-thickness chondral defect in a joint of a patient in need of treatment. Defects which may be treated may be any form of joint defect involving loss of or damage to hyaline cartilage, such as, but not limited to, a full-thickness defect, a partial-thickness defect, an age-related degenerative disease defect such as osteoarthritis, a congenital defect, or an injury resulting from trauma. In particular, such methods may include contacting the joint with, or introducing into the joint, cells which may differentiate into chondrocytes, such as mesenchymal stem cells, and applying to the joint a membrane comprising a flexible tissue matrix as described herein. Contact between the damaged joint and autologous mesenchymal stem cells from the underlying bone may be achieved for example using a microfracture technique as described in further detail below.
Section headings as used in this section and the entire disclosure herein are not intended to be limiting.
As used herein, the singular forms “a,” “an” and “the” include plural referents unless the context clearly dictates otherwise. For the recitation of numeric ranges herein, each intervening number there between with the same degree of precision is explicitly contemplated. For example, for the range 6-9, the numbers 7 and 8 are contemplated in addition to 6 and 9, and for the range 6.0-7.0, the numbers 6.0, 6.1, 6.2, 6.3, 6.4, 6.5, 6.6, 6.7, 6.8, 6.9 and 7.0 are explicitly contemplated.
As used herein, the term “mesenchymal stem cells” refers to pluripotent cells which originate within juvenile or adult mesenchymal tissue. Autologous mesenchymal stem cells may be autologous bone mesenchymal stem cells, i.e., autologous mesenchymal stem cells which originate within the marrow cavity of a bone.
As used interchangeably herein, the terms “demineralized bone matrix” and “DBM” refer to allograft bone tissue with the inorganic mineral removed, leaving organic collagen including biologically active bone morphogenetic proteins.
The terms “hyaluronic acid”, “hyaluronate” and “HyA” are used interchangeably herein.
The success of a bone graft is determined by its ability to recruit host cells to the site of the graft and modulate their conversion into bone forming cells such as osteoblasts, to repair the defect. This will depend on the osteoconductive, osteoinductive and osteogenic capabilities of the graft. Currently, autograft bone harvested from the iliac crest is considered the ‘gold standard’ due to its superior osteogenic properties. However, associated donor site morbidity, an increased surgery and recovery time, and a limited supply of donor bone are limiting its use. Allograft bone is a logical alternative to autograft. However, it must be rigorously processed and terminally sterilized prior to implantation to remove the risk of disease transmission or an immunological response. This processing removes the osteogenic and osteoinductive properties of the graft, leaving only an osteoconductive scaffold.
DBM has superior biological properties to un-demineralized allograft bone as the removal of the mineral increases the osteoinductivity of the graft. Currently, a range of DBM products are commercially available and approved by the Food and Drug Administration for clinical use.
Membranes comprising a tissue matrix comprising a polyester entangled with a polysaccharide, and methods of entangling a polyester and a polymer using a dual solvent emulsion process, are described in U.S. Pat. No. 8,192,759, “Tissue Matrix System,” the entire disclosure of which is incorporated herein by reference. “Entanglement” and related terms, as used herein, refers to a state of polymers in melts or concentrated solutions above the overlap concentration, in which polymers interpenetrate one another and motion of the molecules is restricted to movement along a virtual tube which surrounds each molecule. (See, e.g., Glossary of Colloid and Polymer Science (available at world wide web.studsvik.uu.se/pwwwp/Rennie/gloss.htm#E).
The present disclosure however provides an improved, flexible tissue matrix for supporting tissue repair, which is composed of certain high molecular weight polymers entangled with a polysaccharide and optionally further entangled with a polyester polymer. As used herein, the term “entangled” refers to the spatial relationship between high molecular weight caprolactone polymers and a polysaccharide such as hyaluronic acid which is achieved using the dual solvent emulsion process described herein, and optionally further with respect to a polyester polymer optionally included in the flexible tissue matrix. The flexible tissue matrix optionally further includes small molecule flexibility agents. The flexible tissue matrix optionally further includes one or more growth factors, osteostimulative agents, and/or bone morphogenetic proteins, which may be obtained by prior isolation from allogenic bone. Additionally, in use, the flexible tissue matrix may be combined with any such growth factors, osteostimulative agents, and/or bone morphogenetic proteins, or with other materials such as allogenic bone, crushed cancellous bone, crushed cortical bone, or a DBM composition.
For the flexible tissue matrix, a high molecular weight polymer may be a caprolactone polymer such as polycaprolactone (PCL); a co-polymer of polylactic acid (PLA) and polycaprolactone (poly(lactide-co-caprolactone) (PLCL); a co-polymer of polyglycolic acid (PGA) and caprolactone (poly(glycolide-co-caprolactone) (PGCL); a copolymer of polycaprolactone and both polylactic acid and polyglycolic acid (e.g., PGA-PLCL, PLA-PGCL); a co-polymer of polyethylene glycol (PEG), polylactic acid and polycaprolactone (e.g., PEG-PLCL, PLA-PEG-PCL and PLA-PEG-PLCL); a co-polymer of polyethylene glycol, polyglycolic acid and polycaprolactone (e.g., PEG-PGCL, PGA-PEG-PCL and PGA-PEG-PGCL); or a copolymer of polyethylene glycol, polylactic acid, polyglycolic acid, and polycaprolactone (e.g., PLA-PEG-PGCL, PGA-PEG-PLCL, PLA-PEG-PGA-PCL; PGA-PEG-PLA-PCL). Any of these high molecular weight polymers may further be combined in a polymer blend with a second polymer selected from polylactic acid (PLA), polyglycolic acid (PGA), or a copolymer of polylactic acid and polyglycolic acid (PLGA). The polymers in the matrix do not however consist solely of PLA, PGA or PLGA, although any of these polymers can be used in combination with any of high molecular weight caprolactone polymer.
The polysaccharide may be hyaluronic acid, chondroitin sulfate, dermatan sulfate, keratan sulfate, heparan, heparan sulfate, dextran, dextran sulfate, alginate, or any combination thereof, including any of these existing as multiple polymers, for example in solution. In non-limiting example, a tissue matrix comprises a high molecular caprolactone weight polymer such as, but not limited to a co-polymer of polylactic acid and polycaprolactone (poly(lactide-co-caprolactone), and hyaluronic acid polymers. For example, both types of polymers (high molecular caprolactone weight polymers and hyaluronic acid polymers) are entangled with another via the dual solvent emulsion process described herein. As used herein, the term “hyaluronic acid” may refer to the free acid form of hyaluronic acid, a salt of hyaluronic acid such as sodium hyaluronate, or a combination thereof. Hyaluronic acid polymers may be obtained from a commercial source, such as a hyaluronic acid distributed by Lifecore Biomedical, Inc, Chaska, Minn. and having an average molecular weight of from about 100,000 to about 2,000,000 Daltons. In non-limiting example, the hyaluronic acid may be sodium hyaluronate having an average molecular weight of about 1,700,000.
Surprisingly, high molecular weight caprolactone polymers may be successfully entangled with polysaccharide polymers such as hyaluronic acid polymers using a dual solvent emulsion process, and moreover, the resulting matrix exhibits the following unexpected, beneficial aspects relative to a tissue matrix which is composed solely of PLA, PGA or PLGA entangled with hyaluronic acid polymers: 1) increased flexibility at temperatures usually encountered in the operating theater (e.g., 15 to 20° C.), while retaining the compressive resistant nature of the matrix; 2) increased aqueous absorption at physiological temperatures while maintaining a good dissolution profile relevant to the time scales for tissue regeneration; and 3) reductions in the appearance of a shiny surface on the strips of matrix, which in other polymer matrices which incorporate only PLA, PGA or PLGA results in migration of hyaluronic acid away from one surface during the manufacturing process.
The observed characteristics of the resulting synthetic tissue matrix, including in particular the improved flexibility thereof, avoids or reduces the need to further treat or manipulate the tissue matrix in a surgical environment. In contrast, a tissue matrix using only PLA, PGA or PLGA is comparatively brittle under surgical conditions, and thus requires some form of additional treatment as heating to facilitate its use. Without being bound by theory, it is believed that the increased absorbency of the improved synthetic tissue matrices described herein may be related to an improved ability for these matrices to imbibe and attach cellular component and further tissue formation.
Once implanted in vivo, the flexible tissue matrix serves as scaffold that provides a microenvironment that is both biocompatible with and conducive to new bone formation. The high molecular weight polymer and optional additional polyester polymer provide(s) a three-dimensional structure, and a reliable resorption rate at the site of implantation which is consistent the rate of endochondral bone remodeling. Additionally, hyaluronic acid is believed to play an important role in tissue regeneration and repair, and to assist important early events in bone formation by promoting the migration, proliferation, and differentiation of osteogenic cells. A combination of a high molecular weight caprolactone polymer with a polysaccharide such as hyaluronic acid, and optionally further with a polyester polymer such as PLA, PGA or PLGA, when entangled according to the process described herein, provides a scaffold with improved cohesiveness, molding properties and handling characteristics relative to other known synthetic scaffolds and matrices.
A tissue matrix is prepared using a dual solvent emulsion process as described herein below and in the Examples. Briefly, a high molecular weight caprolactone polymer as described herein above, is dissolved in an organic solvent such as ethyl acetate, a halogenated solvent such as methylene dichloride, chloroform, or tetrahydrofuran, or any combination thereof as known to those of routine skill in the art. Once the high molecular weight caprolactone polymer is dissolved, optionally a polyester polymer such as PLA, PGA or PLGA may be added to the solution and also dissolved. When a high molecular weight polycaprolactone polymer is combined with another (second) polymer such as PGA, PLA or PLGA, they may be combined in a volume ratio of about 10:1 to about 1:1 (second polymer:high molecular weight polycaprolactone polymer). For example, PLGA may be combined with PLCL at a volume ratio of about 10:1 to about 1:1 (PLGA:PLCL). A polysaccharide such as but not limited to hyaluronate (HyA) is dissolved in water. The two solutions (total polymer including high molecular weight polycaprolactone in organic solvent, and polysaccharide in water) are combined at a volume ratio of at least about 1.5:1 (3:2), about 2:1, about 3:1, or any volume ratio from about 4:1 to about 15:1 (total polymer including high molecular weight polycaprolactone in organic solvent:polysaccharide in water) and mixed using any agitation method as known in the art to form an emulsified mixture, or emulsion. For example, a homogenizer as known in the art can be used for agitation. The emulsion is then frozen. After freezing, the frozen emulsion is lyophilized to remove the two solvents, thereby yielding a matrix comprising the high molecular weight caprolactone polymer, and optionally a polyester polymer such as PLA, PGA or PLGA, entangled with the polysaccharide. As described in further detail herein below, prior to freezing, a certain volume of the emulsion can be poured into a flat mould of predetermined volume such that the certain volume of emulsion results in a layer of emulsion of a desired thickness. After freezing and lyophilizing, the resulting matrix is formed as a thin film or membrane of the desired thickness, which is then removed from the mould for use in repairing tissue, or for further processing to achieve a desired membrane thickness, for example using rollers.
A tissue matrix optionally further includes one or more flexibility agents to promote or further enhance the flexibility of the tissue matrix. One or more flexibility agents may be selected from triethyl citrate, acetyl tributyl citrate, acetyl triethyl citrate, tributyl citrate, trimethyl citrate, trihexyl citrate, acetyl trihexyl citrate, trioctyl citrate, acetyl trioctyl citrate or any combination thereof. Alternatively, one or more flexibility agents may be selected from polyethylene glycol, polyethylene glycol monoalkyl ether, propylene glycol, glycerin, triacetin or any combination thereof. The flexibility agent may be added to either the total polymer including high molecular weight polycaprolactone in organic solvent, or to the aqueous polysaccharide solution, depending on the solubility characteristics of the flexibility agent as will be readily known or determined by one of routine skill in the art.
A flexible tissue matrix as described herein may further comprise one or more growth factors, osteostimulative agents, and/or bone morphogenetic proteins (BMPs), which may be synthetic, for example obtained by prior synthesis or by recombinant protein production as known in the art, or by isolation from a natural source such as allogenic bone. For example, and without being limited by theory, certain growth factors are believed to promote formation of hyaline cartilage by promoting differentiation of mesenchymal stem cells into hyaline cartilage-forming chondrocytes, thereby speeding the healing process. Non-limiting examples of such growth factors which may be incorporated into a membrane of the present teachings include a member of the TGF-β superfamily, such as TGF-β1, TGF-β2, TGF-β3, or a bone morphogenetic protein (BMP); a growth differentiation factor; ADMP-1; a fibroblast growth factor (FGF) such as acidic FGF or basic FGF; a member of the hedgehog family of proteins, such as indian hedgehog, sonic hedgehog, or desert hedgehog; a platelet-derived growth factor, an interleukin; a colony-stimulating factor; an activin; a member of the insulin-like growth factor (IGF) family, such as IGF-I or IGF-II; a member of the platelet-derived growth factor (PDGF) family, such as PDGF-AP, PDGF-BB and PDGF-AA; a member of the interleukin (IL) family, such as IL-1, IL-2, IL-3, IL-4, IL-5 or IL-6; or a member of the colony-stimulating factor (CSF) family, such as CSF-1, G-CSF, and GM-CSF. A growth factor may be a growth factor obtained from a tissue source, or can be a recombinant growth factor produced in vitro, in a cell culture, or in a microorganism using standard molecular biology techniques. In some aspects, a growth factor may be a bone morphogenetic protein, such as, in non-limiting example, BMP-1, BMP-2, BMP-3, BMP-4, BMP-5, BMP-6 or BMP-7. Any such growth factors may for example be obtained by prior isolation from bone tissue including allogenic bone tissue. For example, one or more growth factors such as one or more BMPs may be isolated from allogenic bone and incorporated in the flexible tissue matrix. A flexible tissue matrix as described herein may comprise, in addition to or instead of a growth factor, a collagen such as type I collagen, type II collagen, type IX collagen, type X collagen, or type XI collagen. A growth factor or a collagen may be incorporated in the matrix by first preparing an aqueous solution or suspension of the growth factor or collagen (e.g., a collagen suspension), and adding the solution or suspension to the combination of the total polymer in organic solvent and the polysaccharide in water, before or during the emulsification process.
Additionally, in use the flexible tissue matrix may be combined with any such growth factors, osteostimulative agents, and/or bone morphogenetic proteins, and/or with other materials such as allogenic bone, crushed cancellous bone, crushed cortical bone, or a DBM composition.
A flexible tissue matrix as described herein may be formed as a membrane for convenient implantation at the site of a defect. For example, a flexible tissue matrix may be formed as a membrane having a thickness of at least about 0.5 mm up to about 3 mm. A membrane may be formed using methods known to those of routine skill in the art for preparing thin films from liquid or fluid materials. For example, a membrane may be formed by preparing the dual solvent emulsion as described elsewhere herein, pouring a certain volume of the emulsion into a mould of predetermined size, and then lyophilizing the emulsion in the mould. Thickness of the membrane can be further controlled by regulating the rate of pour into the mould and stopping the pour when a layer of emulsion of desired thickness within the mould is obtained. After the lyophilized emulsion has been removed from the mould, the thickness of the resulting membrane can still further be modified by rolling the material through rollers to obtain a membrane of the desired thickness. Alternatively, a membrane may be formed using an extrusion process in which the emulsion is extruded at a predetermined thickness.
The present teachings encompass methods for repairing a full-thickness chondral defect in a joint of a patient in need of treatment. The present methods of joint repair may be applied to any body joint comprising hyaline cartilage, such as, but not limited to, a joint of a knee, an elbow, an ankle, a shoulder, a jaw or a wrist. A joint of may be any joint comprising articular cartilage, such as a joint of a long bone, for example a knee joint comprising articular cartilage of a femur. Furthermore, the methods may be used with both humans and animals having joint defects, including, without limitation, a mammal such as a companion animal or farm animal (e.g., a cat, a dog, a sheep, a cow, a goat, a pig, or a horse). Defects which may be treated may be any form of joint defect involving loss of or damage to hyaline cartilage, such as, but not limited to, a full-thickness defect, a partial-thickness defect, an age-related degenerative disease defect such as osteoarthritis, a congenital defect, or an injury resulting from trauma.
Treatment of a joint defect using the methods disclosed herein is believed to promote deposition of hyaline cartilage in the defect rather than fibrocartilage. Briefly, the methods comprise contacting the joint with, or introducing into the joint, cells which may differentiate into chondrocytes, such as mesenchymal stem cells, and applying to the joint a membrane comprising a flexible tissue matrix as described herein. Such methods using a tissue matrix comprising only a polyester polymer and hyaluronate are described for example in U.S. 2007-0128155 A1 (U.S. patent application Ser. No. 11/635,265) the entire disclosure of which is herein incorporated by reference. Most conveniently, such mesenchymal stem cells may be autologous mesenchymal stem cells originating in the bone underlying the damaged joint, although mesenchymal stem cells from other bones may be used as well. Contact between the damaged joint and autologous mesenchymal stem cells from the underlying bone may be achieved most readily by a microfracture technique, i.e. by introducing one or more apertures into the subchondral bone underlying the defective joint. Such apertures need be at least large enough to allow passage of the mesenchymal stem cells from the bone mesenchyme to the joint. Several well-established procedures may be used to form such passages, such as, without limitation, abrasion (such as abrasion arthroplasty), perforation (e.g., with a surgical awl) and drilling of the bone. These and other treatment procedures are well known to skilled artisans, and described in detail in the literature, for example in references such as Steadman, J. R. et al., Clinical Orthopaedics and Related Research 391S: S362-S369, 2001; and Steadman et al., J. Knee Surg. 15(3):170-176 (2002).
Without being limited by theory, it is believed that following introduction of passages or perforations into the bone, mesenchymal stem cells may migrate out from the bone marrow cavity through the passages, and populate the joint. Exposure of the mesenchymal stem cells to the local environment of the joint leads to differentiation of the stem cells into cartilage-forming chondrocytes. In the further presence of a membrane comprising a tissue matrix as described herein, the chondrocytes produce hyaline cartilage rather than fibrocartilage. The introduction of the cells under these conditions may thereby restore the cartilage of a defective joint to a state more closely resembling that of the joint pre-injury.
Accordingly, the methods of the present disclosure may include microfracturing bone underlying the joint, and applying to the joint a membrane comprising a flexible tissue matrix as described herein. Microfracturing may precede the application to the joint of a membrane comprising a flexible tissue matrix, or vice versa. Additionally, the membrane can be manually shaped according to the contours of a joint. The method may further comprise securing the membrane to the joint, for example anchoring or fastening the membrane to the joint, or immobilizing the membrane at the joint. Securing the membrane may be part of the surgical intervention in the treatment of a patient. Accordingly, in various aspects, a skilled artisan such as an orthopaedic surgeon may secure a membrane at the site of defect in a patient, using at least one fastener, to thereby retain the membrane at the site. Such retention of the membrane may promote the formation of hyaline cartilage by chondrocytes differentiated from mesenchymal stem cells. Examples of a fastener that may be used in the present methods include, without limitation, a biocompatible glue, a suture, a tissue weld, a dart, a staple, a screw, a tack, and a combination thereof. A biocompatible glue may be a fibrin glue, such as a fibrin sealant. A non-limiting example of a biocompatible glue that may be used with the present teachings is a fibrin sealant manufactured by Oesterreichisches Institut Fuer Haemoderivate G.M.B.H. in Vienna, Austria and distributed by Baxter Healthcare Corporation, Glendale, Calif. under the brand name TISSEEL® VH. Non-limiting examples of other fasteners which may be used instead of, or in addition to a biocompatible glue include sutures, tissue welds such as described in Helmsworth, T. F., et aI., Laser Surgery Medicine 10: 576-583, 1990, staples, darts, pins and tacks. In some aspects, a fastener may comprise a biocompatible or bioabsorbable material such as, without limitation, a PLA/PLG polymer, or a non-absorbable material such as a biocompatible metal. A fastener may be an absorbable suture which passes through both the membrane and a joint, and thereby secures apposition of the membrane to the joint. Furthermore, in non-limiting example, the attaching may comprise gluing the membrane to the joint.
As indicated in the foregoing, introduction of at least one aperture in the subchondral bone may precede application of a membrane to the joint, or application of a membrane to the joint may precede the introduction of at least one aperture.
The present disclosure thus encompasses methods for repair of a full thickness chondral defect in a joint of a patient in need of treatment, the methods involving a) introducing at least one aperture through bone underlying the joint, wherein the at least one aperture allows migration of mesenchymal stem cells from a marrow cavity of the bone to the joint, and b) applying to the joint a membrane comprising a flexible tissue matrix as described herein. The methods may further comprise securing the membrane to the joint, using attachments methods and devices as described herein and as otherwise well known to skilled artisans.
Additionally, in use the flexible tissue matrix may be combined with one or more growth factors, osteostimulative agents, and/or bone morphogenetic proteins, and/or with other materials such as allogenic bone, crushed cancellous bone, crushed cortical bone, or a DBM composition. For example, any of the joint treatment or repair methods optionally further comprises applying to the joint, or implanting at a joint defect site, one or more growth factors, osteostimulative agents, and/or bone morphogenetic proteins, and/or other material such as allogenic bone, crushed cancellous bone, crushed cortical bone, or a composition composed of DBM. For example, a DBM gel, putty or paste, or thin sheets or membranes of DBM may be implanted at the joint defect site and/or placed in direct contact with the joint at the defect site. Several suitable DBM substances are commercially available for use in orthopedic surgeries, such as but not limited to Osteofil® IC allograft paste (RTI Biologics Inc., Alachua, Fla.), Grafton® DBM products including putty, paste, gel and sheets (strips) (Medtronics Biologics, Inc., Memphis Tenn.), Dynagraft D™ (Citagenix, Inc., Laval, Qc, Canada), and demineralized trabecular bone products such as but not limited to MatrixOI™ (Cellright, Inc., Universal City, Tex.) Sheets or strips comprising or made of any of the foregoing materials may for example have approximately the same thickness as a membrane comprising the flexible tissue matrix, e.g. at least about 0.5 mm up to about 3 mm. Any of the foregoing materials in any of their various forms may be used generally according to the manufacturer's instructions and in combination with the flexible tissue matrix as may be determined according to guidelines well known to those of routine skill in the art. Application to the joint, or implantation at the a joint defect site, of one or more growth factors, osteostimulative agents, and/or bone morphogenetic proteins, and/or with other materials such as allogenic bone, crushed cancellous bone, crushed cortical bone, or a DBM composition, or a composition comprising any one or more such elements, may take place at any point relative to application of the flexible membrane to the joint, and introduction of at least one aperture for microfracturing.
The following examples are illustrative, and are not intended to limit the scope of the claims.
This example illustrates a method of constructing an entangled matrix comprising a polyester and a polysaccharide. In this example, poly(lactide-co-glycolide) having molecular weight of 1.5×105 is dissolved in dichloromethane (125 mg/ml) and with Hyaluronate (HyA) of molecular weight of about 1.3×106 Dalton is dissolved in water (15 mg/ml). The two polymer solutions, 2 parts PLGA, and 1 part HyA, are mixed with 1 part Milli Q water by vortexing at high speed for about 5 minutes. The emulsified mixture is immediately poured into a mould pre-cooled at −70° C. in a bath containing dry ice in isopropyl alcohol. After freezing, the mold and its contents are transferred into a second container that is loaded with dry ice and connected to vacuum line. Organic solvent is removed by this process at the temperature between −70° C. to −40° C., leaving HyA in wet-ice phase. Water is then removed by raising the temperature to −10° C. under vacuum.
In this example, poly(lactide-co-caprolactone) (PLCL) having a molecular weight of about 2×105 is dissolved in ethyl acetate (80 mg/ml) containing polyethylene glycol 400 (PEG400) (20 mg/ml). Once the PLCL is dissolved, poly(lactide-co-glycolide) (PLGA) having a molecular weight of about 1.5×105 is added (240 mg/ml) and dissolved. Hyaluronate (HyA) of molecular weight of about 1.5×106 is dissolved in water (20 mg/ml). The two polymer solutions, 3 parts PLGA/PLCL, and 2 parts HyA, are mixed, poured in moulds sized sufficiently to produce a membrane having a thickness of 3 mm, and frozen as described in Example 1. After freezing, the frozen emulsion is lyophilized to remove the two solvents yielding a membrane formed of a flexible tissue matrix comprising PLGA/PLCL entangled with HyA.
In this example, an athletic patient presents with a traumatic knee injury to an orthopedic surgeon. A diagnosis is made of damaged articular cartilage of the femoral condyle. The surgeon performs a microfracture procedure on the patient's femoral condyle, creating channels through the bone underlying the hyaline cartilage using an awl or drill. The surgeon selects a membrane having a thickness of 3 mm formed from a tissue matrix prepared as described in Example 2, and shaped to follow the contours of the condyle. The surgeon coats one side of the membrane with TISSEEL® VH fibrin sealant and then applies the membrane to the damaged femoral condyle using gentle pressure. The patient is instructed to keep pressure off the knee for a period of weeks. The condyle is repaired with new hyaline cartilage by six months after the surgical intervention.
Treatment of a knee injury is carried out substantially as described in Example 3 above. A membrane formed of DBM and having a thickness of no more than 3 mm is also applied to the damaged femoral condyle and secured in position using TISSEEL® VH fibrin sealant.
In this example, a patient with osteoarthritis presents with a full-thickness chondral defect in an elbow joint. A surgeon performs a microfracture procedure on the humerus underlying the joint using a drill or awl. A membrane having a thickness of 1 mm and formed from a tissue matrix prepared substantially as described in Example 2, and shaped to follow the contours of the condyle, is positioned by the surgeon upon the condyle. The surgeon secures the membrane in place with a series of screws made of a resorbable PLA/PLG polymer. Following surgery, new hyaline cartilage deposits along the condyle over a six month period. The new cartilage is anatomically indistinguishable from normal hyaline cartilage.
In this example, a middle age male presents with a traumatic dislocation of the shoulder. A diagnosis is made of disruption of the articular cartilage covering the head of the humerus at its articulation with the glenoid socket of the scapula. The patient is operated upon by a surgeon, who performs a microfracture procedure on the head of the humerus. A membrane having a thickness of 1 mm and formed from a tissue matrix prepared as described in Example 2, and shaped to approximate the contours of the humeral head, is positioned by the surgeon upon the humeral head. The surgeon secures the membrane in place with a series of resorbable pins. Following surgery, new hyaline cartilage deposits along the condyle over a period of six months. The new cartilage is anatomically indistinguishable from normal hyaline cartilage.
One skilled in the art would readily appreciate that the articles and kits described in the present disclosure are well adapted to carry out the objects and obtain the ends and advantages mentioned, as well as those inherent therein. The methods, procedures, treatments and kits described herein are merely representative and exemplary, and are not intended as limitations on the scope of the invention. It will be readily apparent to one skilled in the art that varying substitutions and modifications may be made to the present disclosure disclosed herein without departing from the scope and spirit of the invention.
All patents and publications mentioned in the specification are indicative of the levels of those skilled in the art to which the present disclosure pertains. All patents and publications are herein incorporated by reference to the same extent as if each individual publication was specifically and individually indicated to be incorporated by reference. Any discussion of references cited herein is intended merely to summarize the assertions made by their authors and no admission is made that any reference or portion thereof constitutes relevant prior art. Applicants reserve the right to challenge the accuracy and pertinency of the cited references.
This application claims the benefit of the filing date of U.S. 61/727,454 filed Nov. 16, 2012, the entire disclosure of which is herein incorporated by reference.
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| Number | Date | Country | |
|---|---|---|---|
| 20140142718 A1 | May 2014 | US |
| Number | Date | Country | |
|---|---|---|---|
| 61727454 | Nov 2012 | US |
