WO2008012828A2 - Composite implants for promoting bone regeneration and augmentation and methods for their preparation and use - Google Patents
Composite implants for promoting bone regeneration and augmentation and methods for their preparation and use Download PDFInfo
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- WO2008012828A2 WO2008012828A2 PCT/IL2007/000946 IL2007000946W WO2008012828A2 WO 2008012828 A2 WO2008012828 A2 WO 2008012828A2 IL 2007000946 W IL2007000946 W IL 2007000946W WO 2008012828 A2 WO2008012828 A2 WO 2008012828A2
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- 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
- A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
- A61L27/56—Porous materials, e.g. foams or sponges
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- 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
- A61L27/40—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material
- 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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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61P—SPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
- A61P19/00—Drugs for skeletal disorders
Definitions
- the present invention relates generally to implantable, devices for promoting regeneration and augmentation of bone and more specifically of composite reducing sugar cross-linked collagen based matrices, methods for their use and methods for their preparation.
- Alveolar bone loss is secondary to early tooth loss and periodontal disease, leading to severe functional and esthetic problems.
- the replacement of missing or hopeless teeth is possible via the use of dental implants.
- These, however require sufficient bony housing to accommodate an implant of appropriate length and diameter to be able to withstand the oclussal load on the future prosthetic device, and to provide optimal esthetic results.
- alveolar bone augmentation is mandatory for functional and esthetic long term success of dental implants.
- bone grafts under a barrier that prevents soft tissue invasion, and allows a selective cell line with osteogenic capabilities to populate the defect. These are used to facilitate migration and differentiation of mesenchymal cells to form osteoblasts and lay down bone within the defect.
- such devices may serve as a scaffold that supports cell migration.
- the grafts may be derived from natural sources (human and other animals), or from various synthetic materials, as is known in the art. Bone grafts are normally used as a powder with particle size ranging from 0.25-2 mm mixed with patient's blood as a coagulum or mixed with sterile saline. In some cases, gel or putty like consistency of the implant provide improved handling of the material.
- the graft material should be biocompatible with minimal allergic or immunogenic reactions. 3.
- the graft should be safe from risk of disease transmission.
- the graft material should preferably serve as a scaffold that encourages cells to migrate and populate the secluded space of the bone defect.
- the graft should preferably undergo complete degradation within 6-12 months. 6.
- the graft should preferably mimic bone matrix proteins and should be capable of undergoing ossification.
- the graft should serve as a carrier for suitable growth factors.
- the graft should be easy to handle even by inexperienced clinicians requiring minimal skills for its preparation and implantation to save time and reduce possible complications.
- a method for preparing a composite multi-density cross-linked collagen implantable device includes the steps of, compressing a suspension including fibrillated collagen particles in a first suspending solution to form a first matrix having a first density, applying to the first matrix a suspension including fibrillated collagen particles in a second suspending solution to form a second matrix attached to the first matrix the second matrix having a second density lower than the first density, drying the first matrix and the second matrix to form a dry multi-density composite matrix, and reacting the multi-density composite matrix with a reducing sugar to form the composite multi-density cross-linked collagen implantable device.
- the step of reacting includes incubating the composite multi-density implantable device with a reducing sugar in an incubation solution including ethanol.
- the incubation solution includes 70% ethanol.
- the reducing sugar is selected from D(-) ribose and DL glyceraldehyde.
- At least one additional substance is added to at least one of the first suspending solution, said second suspension solution, said first matrix, and said second matrix.
- the method also includes the step of adding living cells to the composite implantable device.
- the cells are selected from cultured cells, stem cells, human cells, animal cells, fibroblasts, pluripotent bone marrow cells, pluripotent stem cells, bone building cells, osteoblasts, mesenchymal cells, mammalian cells, primary cells, genetically modified cells, nerve cells and any combinations thereof.
- a composite multi-density cross-linked collagen implantable device prepared by any of the above methods.
- a composite multi-density cross-linked collagen based implant includes a first reducing sugar cross-linked collagen based matrix having a first density and at least a second reducing sugar cross-linked collagen based matrix attached to the first reducing sugar cross-linked collagen based matrix.
- the second collagen based matrix has a second density lower than the first density.
- the first and the second reducing sugar cross-linked collagen based matrices are obtained by cross-linking collagen with a reducing sugar in an incubation solution including ethanol.
- the incubation solution comprises 70% ethanol.
- the reducing sugar is selected from D(-) ribose and DL glyceraldehyde.
- the composite implant includes at least one additional substance.
- the implant includes living cells selected from cultured cells, stem cells, human cells, animal cells, fibroblasts, pluripotent bone marrow cells, pluripotent stem cells, bone building cells, osteoblasts, mesenchymal cells, mammalian cells, primary cells, genetically modified cells, nerve cells and any combinations thereof.
- a method for using a composite multi-density cross-linked collagen implantable device for treating a bone defect includes the step of applying to the bone defect a composite multi-density glycated cross-linked collagen based implantable device including a first reducing sugar cross-linked collagen based matrix having a first density and at least a second reducing sugar cross-linked collagen based matrix attached to the first collagen based matrix.
- the second collagen based matrix has a second density lower than the first density.
- the at least second collagen based matrix is disposed within the bone defect to promote bone formation within the bone defect.
- the first collagen based matrix at least partially prevents the formation of tissue other then bone tissue within the bone defect.
- the implantable device is obtained by incubating a collagen based composite multi-density implantable device with a reducing sugar in an incubation solution including ethanol.
- the incubation solution includes 70% ethanol.
- the reducing sugar is selected from D(-) ribose and DL glyceraldehyde.
- the composite implantable device includes least one additional substance.
- a method for using a reducing sugar cross-linked collagen matrix as an improved scaffold for cell proliferation and cell differentiation includes the steps of providing a scaffold comprising a collagen matrix cross-linked with a reducing sugar, and incubating the scaffold with living cells to induce improved growth and/or proliferation and/or differentiation of the cells.
- the cells are selected from cultured cells, stem cells, human cells, animal cells, fibroblasts, pluripotent bone marrow cells, pluripotent stem cells, bone building cells, osteoblasts, mesenchymal cells, mammalian cells, primary cells, genetically modified cells, nerve cells and any combinations thereof.
- the scaffold is obtained by incubating a collagen based matrix with a reducing sugar in an incubation solution including ethanol.
- the incubation solution includes 70% ethanol.
- the reducing sugar is selected from D(-) ribose and DL glyceraldehyde.
- the scaffold comprises at least one additional substance.
- the at least one additional substance is selected from an antimicrobial agent, an anti-inflammatory agent, an anti-bacterial agent, an anti-fungal agent, one or more factors having tissue inductive properties, growth factors, growth promoting and/or growth inhibiting proteins or factors, extracellular matrix components, an anesthetic material, an analgesic material, an osteoblast attracting factor, a drug, a pharmaceutical agent , a pharmaceutical composition, a protein, a glycoprotein, a mucoprotein, a mucopolysaccharide, a glycosaminoglycan, hyaluronic acid, chondroitin 4-sulfate, chondroitin 6-sulfate, keratan sulfate, dermatan sulfate, heparin, heparan sulfate, a proteoglycan, a lecitin rich interstitial proteoglycan, decorin
- Fig. 1 is a composite photomicrograph representing several regions of tissue excised from an implant of a rat calvarial experimental bone defect twelve weeks after the implantation of a composite matrix comprising a scaffold including a reducing sugar cross-linked collagen based sponge and a reducing sugar cross-linked collagen barrier membrane;
- Fig. 2 is a schematic cross-sectional view representing a composite implantable cross- linked collagen matrix having parts with different densities in accordance with an embodiment of the method of the present invention;
- Fig. 3 is a photograph representing a composite implantable cross-linked collagen matrix having parts with different densities prepared from porcine collagen for treating bone defects, in accordance with an embodiment of a method of the present invention
- Fig. 4 is a schematic graph representing a schematic cross sectional view of a bone defect treated with an implantable composite cross-linked collagen matrix having parts with different densities for treating bone defects, in accordance with an embodiment of a method of the present invention
- Fig. 5 is a schematic graph representing the results of an in-vitro experiment quantitatively comparing the fibroblast population of a collagen sponge based on ribose cross-linked porcine collagen with the fibroblast population of another commercially available collagen sponge based on collagen stabilized with formaldehyde.
- reducing sugar is defined as any natural and/or artificial reducing sugar and any derivatives of such reducing sugars, including but not limited to, glycerose (glyceraldehyde), threose, erythrose, lyxose, xylose, arabinose, allose, altose, glucose, manose, gulose, idose, galactose, fructose, talose, a diose, a triose, a tetrose, a pentose, a hexose, a septose, an octose, a nanose, a decose, a reducing disaccharide, maltose, lactose, cellobiose, gentiobiose, melibiose, turanose, trehalose and a reducing trisaccharide and a reducing sugars, including but not limited to, glycerose
- collagen is defined for the purposes of the present application as any form of natural collage and/or purified collagen and/or chemically modified collagen, and/or proteolitically treated collagen, and/or genetically engineered collagen, and/or artificially produced collagen, including but not limited to, native collagen, fibrillar collagen, fibrillar atelopeptide collagen, lyophylized collagen, freeze dried collagen, collagen obtained from animal sources, a collagen produced by a genetically modified plant and/or microorganism and/or mammal and/or multicellular organism, porcine collagen, bovine collagen, human collagen, recombinant collagen, pepsinized collagen, reconstituted collagen, reconstituted purified collagen, reconstituted attelopeptyde purified collagen, and any combinations thereof.
- EXPERIMENT 1 EXPERIMENT 1
- This experiment describes histological evidence of new bone formation in vivo within collagen matrices cross-linked with a reducing sugar.
- a rat calvarial model was used to study the performance of a collagen based sponge-like matrix material cross- linked with a reducing sugar as an ossification promoting bone defect filler material useable in association with a collagen based membrane barrier.
- Fig. 1 is a composite photomicrograph, representing cross-sections of tissue excised from rat calvarial bone defect experimental model at 12 weeks after treatment with a combination of a collagen sponge and barrier membrane as described hereinabove (stained with Mallory Trichrome stain).
- micrograph labeled B of Fig. 1 represents a higher magnification of defect area (original magnification xlO). Note areas in which new bone is formed within the sponge above the original envelope of bone.
- the micrograph labeled C of Fig. 1 represents a different magnified area (original magnification x40) from the photomicrograph of the part labeled A of Fig. 1. New bone is formed within the sponge's cavities and the walls of the sponge may be observed (arrows).
- results of these experiments further support the novel and unexpected superior properties of the porcine ribose cross-linked collagen matrices in promoting bone regeneration and bone augmentation in comparison with other commercially available collagen membranes which were cross-linked with other different cross-linkers, as described in detail in the article.
- the dual, time dependent, effect of the denser barrier membrane was also clearly demonstrated in the above mentioned article by Zubery et al. which clearly shows that while initially the denser barrier membrane functions as an effective barrier preventing the penetration of fibroblasts into the bone defect region occupied by the less dense collagen sponge layer, at a later stage of the defect healing process, bone forming cells successfully invade the denser collage barrier membrane resulting in substantially complete ossification of the barrier membrane and participating in improving the bone regeneration and augmentation process.
- a composite bone graft implant that includes a part with a relatively low density of collagen based material serving as a scaffold for bone regeneration and augmentation and another part having higher density of collagen for initially serving as a barrier for preventing invasion of other non-bone forming cells and tissue into the bone defect.
- the composite matrix 1 includes a first portion 2 which includes reducing sugar cross-linked collagen having a relatively low density (sponge-like structure) conducive to bone forming cells or tissues and serving as a scaffold for bone tissue formation therein.
- the composite matrix 1 also includes a second portion 4 which includes reducing sugar cross-linked collagen having a relatively high density which may act (at least initially) as a barrier for preventing or reducing the penetration of unwanted cells or tissues into the first portion 2 of the matrix 1 to reduce or prevent the formation of connective tissue in the first portion 2 of the matrix.
- An advantage of the composite matrix is that the portion 4 in addition to serving as a barrier as explained hereinabove may also enhance bone augmentation by supporting (at least in the more advanced stages of the augmentation) bone formation by being ossified.
- Porcine fibrillar collagen was prepared as described in detail in the US. Patent 6,682,760, incorporated herein by reference in its entirety. The fibrillated collagen was concentrated by centrifugation at 4500 rpm. AU centrifugations (unless specifically stated otherwise) were done using a model RC5C centrifuge with a SORVALL SS-34 rotor commercially available from SORV ALL® Instruments DUPONT, USA.
- the fibrillated collagen concentration after centrifugation was 75 mg/mL (as determined by Lowry standard method).
- fibrillated collagen 50 milliliters (50 mL) fibrillated collagen were poured into a 140 mm x 120 mm stainless steel tray.
- the fibrillated collagen was equally dispersed and covered with a mesh (Propyltex 05-1 25/30, commercially available from SEFAR AG, Heiden, Switzerland), A perforated polystyrene plate was placed on top of the mesh and a 5 kilogram weight was placed on top of the plate in order to compress the fibrillated collagen. The compression lasted for 18 hours at 4 0 C.
- the shelf temperature during lyophilization was +30 0 C and the vacuum during lyophilization was approximately 0.01 bar.
- FIG. 3 is a photograph representing a composite implantable cross-linked collagen matrix having parts with different densities prepared from porcine collagen for treating bone defects, in accordance with an embodiment of a method of the present invention as described hereinabove in EXAMPLE 1.
- the region labeled 6 represents the lower density portion of the composite matrix and the region labeled 8 represents the denser portion which functions as a barrier layer.
- Porcine fibrillar collagen was prepared as described in detail in the US. Patent 6,682,760, incorporated herein by reference in its entirety.
- the fibrillated collagen was concentrated by centrifugation at 4500 rpm. All centrifugations (unless specifically stated otherwise) were done using a model RC5C centrifuge with a SORVALL SS-34 rotor commercially available from SORV ALL® Instruments DUPONT, USA.
- 450 mL of purified collagen (concentration: 2.73 mg/mL) were mixed with 50 mL fibrillation buffer (as described in detail in the US. Patent 6,682,760) and poured into a tray. The mixture was incubated for 18 hour at 37 0 C to form a gel.
- the fibrillated collagen was covered with a mesh (Propyltex 05-1 25/30, commercially available from SEFAR AG, Heiden, Switzerland), A perforated stainless steel plate was placed on top of the mesh and a 1.9 kg weight was placed on the gel for 18 hours at 37 0 C to compress the gel to form a membrane.
- a mesh Propyltex 05-1 25/30, commercially available from SEFAR AG, Heiden, Switzerland
- the compressed membrane was placed in a 140mm xl20 mm stainless steel tray and 100 mL of a suspension of porcine fibrillated collagen (37.5 mg/mL) in 10 millimolar phosphate buffer solution (PBS pH 7.36) prepared as described in detail in the US. Patent 6,682,760, were poured and evenly distributed on top of the compressed, fibrillated collagen layer.
- the tray was transferred into the lyophilizer (Freeze dryer model FD 8 commercially available from Heto Lab Equipment DK-3450 Aller ⁇ d, Denmark), pre-frozen for eight hours and lyophilized for 24 hours.
- the condenser temperature was -80 0 C.
- the shelf temperature during pre- freezing was -40 °C.
- the shelf temperature during lyophilization was +3O 0 C and the vacuum during lyophilization was approximately 0.01 bar.
- 200 mL of a solution containing 120 mL absolute ethanol (commercially available from Merck, Germany), 80 mL PBS buffer solution (10 mM, pH 7.36) and 2 gram of DL-glyceraldehyde (commercially available as Catalogue No. G5001 from Sigma, USA) were added to the dried (lyophilized) fibrillated collagen and incubated at 37 0 C for 24 hours to perform the cross-linking of the composite collagen structure.
- the combined collagen product was washed exhaustively with DI water and lyophilized, using the same conditions as described above.
- Porcine fibrillar collagen was prepared as described in detail in the US. Patent
- the compressed membrane was placed in a 140mm xl20 mm stainless steel tray and 100 mL of a suspension of porcine fibrillated collagen (37.5 mg/mL) in 10 millimolar phosphate buffer solution (PBS pH 7.36) prepared as described in detail in the US. Patent 6,682,760 were poured and evenly distributed on top of the compressed, fibrillated collagen layer.
- the tray was transferred into the lyophilizer (Freeze dryer model FD 8 commercially available from Heto Lab Equipment DK-3450 Aller ⁇ d, Denmark), pre-frozen for eight hours and lyophilized for 24 hours.
- the condenser temperature was -80°C.
- the shelf temperature during pre- freezing was -40°C.
- the shelf Ijemperature during lyophilization was +3O 0 C and the vacuum during lyophilization was approximately O.Olbar.
- Porcine fibrillar collagen was prepared as described in detail in the US. Patent
- the fibrillated collagen concentration after centrifugation was 15 mg/mL (as determined by Lo wry standard method).
- FIG. 4 which is a cross-sectional diagram illustrating a cross section of a bone defect treated with a implantable composite cross-linked collagen matrix 16 having parts with different densities for treating bone defects, in accordance with an embodiment of a method of the present invention.
- the bone 10 has a bone defect 12 therein.
- the shaped composite matrix 14 is inserted into the defect 12 so that the portion 18 having the lower density faces the walls of the defect 12 and the denser barrier portion 16 is positioned adjacent the surface of the bone 10, preferably entirely covering the opening of the defect 12 to prevent penetration of unwanted cells (such as, for example, fibroblasts) populating the space of the defect 12 and/or the lower density portion 18 of the composite matrix 14.
- the portion 18 may thus function as a suitable ossification substrate (scaffold) for bone tissue growth while being protected by the portion 16 of the composite matrix 14 which functions as a barrier preventing or reducing the penetration of fibroblasts and/or other undesirable cells or tissues into the defect 12 and/or into the portion 18.
- the portion 16 may gradually ossify as well, enhancing bone augmentation and the integrity of the augmented bone tissue.
- Ribose cross-linked collagen porcine sponge was prepared as disclosed hereinabove in EXAMPLE 4). The glycation (and cross-linking) incubation was performed at 37 0 C for seven days to perform the ribose cross-linking of the collagen structure. The ribose cross-linked collagen products were washed exhaustively with DI water and lyophilized, using the same conditions as described above. The ability of the resulting ribose cross- linked collagen sponge to serve as a scaffold for support proliferation and/or differentiation of human foreskin fibroblasts was compared to bovine collagen sponge product (CollaCot ® ) commercially available from Sulzer Medica (Sulzer Dental Inc. USA). It is noted that as Sulzer Dental Inc. was recently bought by Zimmer Dental Inc., CA, U. S. A the same sponge product under the same name CollaCot ® continues to be commercially available from Zimmer Dental Inc., CA, U.S.A.
- CollaCot ® bovine collagen sponge product
- the Sulzer CollaCot ® sponge includes bovine collagen extracted from bovine deep flexor (Achilles) tendon and GAG, and stabilized with formaldehyde.
- DMEM Dulbeco Modified Eagle's Medium
- HEPES Hydrophilese
- FBS Fetal bovine serum
- Gentamycin 20 mg/mL Gentamycin was used throughout the entire experiment.
- the sponges were incubated in a tissue culture incubator at 37 °C, with medium changes performed approximately every two days.
- the cell populated sponges were harvested at twenty (20) days after seeding and histology and quantitative analysis was performed.
- the sponge was then removed, fixed and embedded in paraffin for crio-sectioning using standard techniques. 5 ⁇ m thick paraffin sections of the sponge were stained with Hematoxylin & Eosine stain.
- the stained sections were microscopically observed at magnifications of X10-X40 active primary human fibroblasts were observed to produce a loose network of new collagen within the sponge cavities. These newly formed collagen networks were in contact with other fibroblasts as well as with the sponge collagen walls.
- Visual examination of the photomicrographs revealed that primary cultured human fibroblasts proliferate in the ribose-cross-linked porcine collagen sponge homogenously. In contrast, the same fibroblasts grow (to a much lesser extent) primarily at the edges of Sulzer Medica's bovine collagen sponge and not in the middle section of the sponge possibly indicating greater difficulty of cell penetration of and migration into the Sulzer Medica's sponge.
- the COLBAR ribose cross-linked collagen sponge (also referred to as the COLBAR sponge hereinafter) may be a favorable scaffold for the proliferation and differentiation of tissue.
- the growth of human fibroblasts within the glycated and cross- linked collagen sponge was also compared with a commercially available bovine collagen sponge (CollaCote ® ) and was unexpectedly found to be superior in the COLBAR sponge.
- Pluripotent stem cells also flourished within the sponge suggesting the possibility of inducing differentiation while using the COLB AR reducing sugar cross-linked collagen sponge as a biological scaffold.
- the automatic cell counting was performed using a Nikon Eclipse 5Oi microscope with a Maerzhauser Scan 100x80 Motorized microscope stage. The microscope was coupled to a Nikon Digital Sight DS-5M Camera. The Lens magnification was 1OX.
- a stitched image composed of multiple images spanning the whole length of the sponge was formed by using the NIS Elements AR 2.30 SP4 Build 384 software commercially available from Nikon Instruments Inc., NY, U.S.A.
- the cells were counted in each (1x1 mm) field automatically by the software.
- the stitched image size for the porcine ribose cross-linked collagen sponge was 15190 xl976 pixels representing a section size of 10.5x1.1 millimeters.
- the stitched image size for the Sulzer sponge was 9091x1921 pixels representing a section size of 6.1x1.1 millimeters (note that the Sulzer sponge was shorter than the COLBAR porcine ribose cross-linked collagen sponge). For both sponges the area per count was 1 x 1 millimeters.
- the results of the automatic cell counting are illustrated in Fig. 5 below.
- Fig 5 is a schematic graph representing the results of an in- vitro experiment quantitatively comparing the fibroblast population of a collagen sponge based on ribose cross-linked porcine collagen with the fibroblast population of another commercially available collagen sponge based on collagen stabilized with formaldehyde.
- the vertical axis represents the number of cells counted and the horizontal axis represents the length of the sponge in millimeters.
- the hollow symbols represent the four different results of sections 1, 4, 7 and 10 taken at 1 microns 20 microns, 40 microns and 60 microns along the width of the sponge (in a direction perpendicular to the length and to the height of the sponge), respectively of the COLBAR reducing sugar cross-linked sponge.
- the dashed line associated with the hollow symbols represents a curve passing through the averaged value of the four cell counts (obtained from respective 1X1 millimeter fields of the first, fourth, seventh and tenth sections taken at each particular value of sponge length).
- the error bars represent the standard deviation of the mean for each averaged value of a group of four measurements at the specified sponge length.
- the filled symbols represent the four different results of sections I 5 4, 7 and 10 taken at 1 microns 20 microns, 40 microns and 60 microns along the width of the sponge (in a direction perpendicular to the length and to the height of the sponge), respectively of the Sulzer formaldehyde stabilized CollaCote ® bovine collagen sponge.
- the continuous line associated with the filled symbols represents a curve passing through the averaged value of the four cell counts (obtained from respective 1x1 millimeter fields of the first, fourth, seventh and tenth sections taken at each particular value of Sulzer sponge length).
- the error bars represent the standard deviation of the mean for each averaged value of a group of four measurements at the specified sponge length.
- the averaged cell counts are consistently significantly higher in the COLBAR sponge than in the Sulzer sponge. In both sponges, the cell count is higher towards the end of the sponge than in the middle portion of the sponge which may possible (but not necessarily ) be due to effects associated with the rate of migration of fibroblasts from the sponge's edge to the inner part of the sponge.
- the cell count near one edge along the length of the sponge (represented by the value of 0.5 millimeters on the horizontal axis) is significantly higher than the cell count at the opposite edge of the same sponge
- the cell counts of the COLBAR sponge are always higher than the cell counts of the Sulzer sponge at the corresponding length.
- the increase in cell count ranges from a cell count increase of about 358% in the cell count of the COLBAR sponge relative to the Sulzer sponge at 0.5 millimeter sponge length, to a cell count increase of about 565% in the cell count at the center of the COLBAR sponge (at 4.5 millimeters sponge length) relative to the center of the Sulzer sponge (at 2.5 millimeter sponge length).
- the cell count increase of the COLBAR sponge relative to the Sulzer sponge is about 389%.
- the COLBAR ribose cross-linked porcine collagen sponge produced as disclosed hereinabove is substantially and unexpectedly more conducive to penetration, growth and proliferation of primary human fibroblast cultured under the same conditions. It is noted that while the reasons for this advantage of the COLBAR sponge are not clear at the present, it may possibly be due to the fact that small amounts of the cross- linker may be slowly released from the cross-linked collagen of both sponges.
- the actual structure and moieties presented to cells by the glycated and/or reducing sugar cross-linked collagen matrix itself is more favorable to or supportive of cell migration and/or penetration, and/or viability and/or proliferation than the structure or moieties presented by the Sulzer collagen sponge and/or other non-glycated, cross-linked collagen matrices.
- the portions 16 and/or 18 of the composite matrix 14, and the portions 2 and/or 4 of the matrix 1 of Fig. 2 may also include, in addition to the reducing sugar cross-linked collagen, other types of biocompatible materials or any suitable mixtures of biocompatible materials for modifying the properties of the matrices or of a selected portion of the device.
- Such materials may include but are not limited to, hyaluronic acid (HA) and/or hyaluronan and/or suitable derivatives, and/or salts and/or esters thereof, chitosan and/or hyaluronan and/or suitable derivatives and/or salts and/or esters thereof, various oligosaccharides and/or polysaccharides and/or suitable derivatives and/or salts and/or esters thereof, various biocompatible synthetic polymers as is known in the art, cross-linked and/or non-cross-linked proteins (such as, but not limited to, alkaline phosphatase and/or pyrophosphatase which play a role in mineralization of new bone), cross-linked and/or non-cross-linked glycoproteins and the like, calcium phosphate nanoparticles and/or hydroxy-apatite crystals (which may be used to accelerate bone augmentation), growth factors such as, but not limited to BMP's, PDGF and the like, including any growth factors
- the materials or substances that may be added to the composite membranes of the present invention are not limited to structural materials such as natural and/or synthetic polymers and the like but may also include other types of additives, including but not limited to, small molecules, drugs, anesthetic material(s), analgesic material(s) or any other desired material or substance. Any combinations of the above materials with any other materials disclosed in the present application may also be used.
- the additional materials added to the reducing sugar cross-linked collagen forming the implanted matrices of the present invention may be cross linked or non-cross-linked, biocompatible, natural or synthetic polymers.
- Such polymers or other substances which » may be added to the collagen-based matrices of the implants of the invention may be trapped within and/or cross-linked to the collagen during the glycation and/or cross- linking process used to form the composite matrix as described in Examples 1-3 above.
- chitosan is used as an additive to one or more of the portions 2 and 4 of the matrices of the device 4, the glycation process and subsequent cross-linking crosslinks not only the molecules of collagen to each other but also forms cross-links attaching the chitosan backbone to collagen molecules through the glycation of free amino groups in chitosan and the lysine amino groups in collagen.
- the resulting composite matrix may have different, biological and physico-chemical characteristics.
- Co-pending US provisional application serial number 60/713,390 to Bayer et al, filed September 2, 2005 discloses, inter alia, such cross-linked matrices including collagen and amino-grbup containing polysaccharides or amino derivatized polysaccharides and methods for their preparation.
- any other cross-linking reducing sugar or reducing sugar derivatives known in the art may be used for cross-linking of the collagen matrices forming the composite matrices of the present invention.
- cross-linking in aqueous solutions is described in US patents 5,955,438 and 6,346,515 to Pitaru et al., which are both incorporated herein by reference in their entirety.
- cross-linking methods used in the cross-linking of the embodiments of the composite multi-density membranes of the present invention may be applied using either D or L forms or mixtures of D and L forms of reducing sugars or reducing sugar derivatives, as is known in the art.
- a composite matrix having three portions may be made and used for bone induction or conduction. This may be accomplished by adding an additional layer of fibrillated collagen having a low density of collagen particles on top of the portion 2 of the implant 1 before drying to for a three layer composite matrix having three portions each having a different density of collagen.
- the three layered composite matrix may then be dried and cross-linked using a reducing sugar in a reaction mixture with or without a polar solvent as described hereinabove.
- the resulting three layered composite matrix may then be washed and dried or lyophilized as described hereinabove.
- the size and shape of the composite matrix having two or more layers of glycated reducing sugar cross-linked collagen may vary according to need and type of bone defect in need of treatment.
- the thickness of the various layers or portions of the implanted matrix may be varied at will by controlling the amount and/or the concentration of material used when forming each layer or portion of the matrix. Any type of shape, size, number of layers or portions and the thickness of each layer or portion may be used in the matrices of the present invention, depending, inter alia, on the specific application.
- matrices having a density gradient along one or more dimensions of the portion of the matrix or along the entire span of the matrix may be made.
- Various different methods for forming density gradients within one or more of the portions of a matrix may be used. For example one may use centrifugation techniques to form a density gradient along a dimension of one or more of the portions 2 and 4 of the matrix 1 of Fig. 2.
- Other methods for forming continuous or discontinuous density gradients may include, but are not limited to, mixing of two different suspensions each having a different density of collagen based material therein and overlaying of the resulting mixture on top of the layer 4.
- any other method for gradient forming known in the art such as but not limited to spinning method, may be used in forming composite matrices having density gradients.
- additives may include, but are not limited to, relatively small or intermediate size molecules materials or substances such as, but not limited to, antimicrobial agent(s), an anti-inflammatory agent(s), anti-bacterial agent(s), anti-fungal agent(s), one or more factors having tissue inductive properties, growth factors, growth promoting and/or growth inhibiting proteins or factors, extracellular matrix components, anesthetic material(s), analgesic material(s), BMPs, osteoblast attracting factors or substances, and any other desired drugs or pharmaceutical agent(s) or compositions.
- glycosaminoglycans such as but not limited to chondroitin 4-sulfate, chondroitin 6-sulfate, keratan sulfate, dermatan sulfate, heparin, heparan sulfate, hyaluronan, proteoglycans such as the lecitin rich interstitial proteoglycans decorin, biglycan, fibromodulin, lumican, aggrecan, syndecans, beta- glycan, versican, centroglycan, serglycin, fibronectins, fibroglycan, chondroadherins, fibulins, thrombospondin-5, calcium phosphate, hydroxyapatite, alkaline phosphatase and pyrophosphatase
- glycosaminoglycans such as but not limited to chondroitin 4-sulfate, chondroitin 6-sulfate, keratan sulfate,
- any material(s) related to gene therapy may also be included in the composite matrices of the present invention, such as, but not limited to, DNA, RNA, fragments of DNA or RNA, nucleic acids, oligonucleotides, polynucleotides, anti-sense DNA or RNA, plasmids, vectors or the like, allogeneic material(s) a nucleic acid, an oligonucleotide, a chimeric DNA/RNA construct, DNA or RNA probes, anti-sense DNA, anti-sense RNA 5 a gene, a part of a gene, a composition including naturally or artificially produced oligonucleotides, a plasmid DNA, a cosmid DNA, modified viral genetic constructs or any other substance or compound containing nucleic acids or chemically modified nucleic acids, or various combinations or mixtures of the above disclosed substances, compounds and genetic constructs, and may also include the vectors required for promoting cellular uptake and transcription, such as
- any combinations of any of the substances, materials, additives, genetic constructs, gene therapy materials, drugs, and any other additives disclosed hereinabove and/or hereinafter may be added to the composite matrices of the present application.
- All the above disclosed materials or substances and any combinations of such materials or substances which may be used as additives to the composite membranes of the present invention may be added either before or after the performing of the cross- linking reaction (using the reducing sugar cross-linker). However, it may also be possible to add one or more additives, perform the cross-linking of the collagen and then add additional substance(s) by soaking the cross-linked collagen in a solution including one or more additional substances and/or additives.
- the implantable devices and/or composite membranes of the present invention may also be modified by the inclusion of living cells.
- living cells may be autologous cells derived from the patient in which the implant is going to be implanted but may also be cells from a genetically compatible donor.
- the cells may be any type of living cells which may have a supporting role or assisting role in bone formation, such as but not limited to osteoblasts, progenitor cells, stem cells, precursor cells, embryonic stem cells, adult derived stem cells, cells derived from cell cultures or cell lines, non-differentiated cells, or the like.
- Such cells may be added to the devices of the present invention by soaking the devices or implants or parts thereof in suspensions of such cells or in culture medium in which such cells are present.
- the implant, device or composite membranes may be incubated together with any of the above disclosed cells for a sufficient period of time to ensure penetration or migration of such cells into the scaffold part of the device or composite membranes.
- the devices, implants or composite membranes charged with cells may be implanted in or inserted into the bone defect as described hereinabove.
- Such additives or materials may be simply mixed with the collagen based material used for preparation of the composite matrices before the cross-linking step. After the collagen and/or compositions containing collagen mixed with other polymers are cross- linked some or all of the added substances or additives may be trapped in the cross- linked matrix (or matrices) and may be released from the matrix to exert their biological influence within or in the vicinity of the defect.
- some molecules containing amino groups may be covalently linked to the collagen or polysaccharide backbones through collagen (lysine) amino groups or through amino groups of the polysaccharide used in mixed membranes by the glycation reactions and further rearrangement and/or cross-linking steps.
- Such covalently linked molecules or agents may modify the structure and physiological properties of the resulting matrices and may confer various useful biological properties thereon, as is known in the art, such as, for example, serving as molecular cues for cells which penetrate the scaffold, etc.
- composite matrices of the invention as described hereinabove may also be seeded prior to implantation thereof with any suitable type of living cells which may be useful for assisting or improving bone tissue formation within the matrix or the bone defect, such cells may include but are not limited to, osteoblasts, stem cells, or any other bone building cells known in the art.
- any type of collagen may be used in the composite matrices of the present invention including but not limited to, native collagen, fibrillar collagen, fibrillar atelopeptide collagen, lyophylized collagen, collagen obtained from animal sources, human collagen, recombinant collagen, proteolitically digested collagen, pepsinized collagen, reconstituted collagen, collagen types I, II and IX, or any other suitable mixture of any other types of collagen known in the art and any combinations thereof.
- glycated collagen mean any type of collagen which was reacted with a reducing sugar or with a reducing sugar derivative and also include all types of cross-linked collagen which may be formed in subsequent rearrangement and/or cross-linking following the glycation of the collagen.
- the devices and methods described herein are not limited to oral surgical procedures described and may be easily modified and adapted for any type of procedure involving treatment of bone defects, fractures, and the like in any type of bone for orthopedic, plastic, cosmetic and other types of surgery and bone graft implant procedures.
- the composite matrices of the invention may be used to treat any type of bone defect or bone fracture of any type of bones in humans or other species of animals. .
- any of the composite glycated collagen based and/or reducing sugar cross-linked collagen based implants disclosed herein and any of the reducing sugar cross-linked collagen based scaffolds and sponges disclosed in the present application may also include one or more additives such as but not limited to, an antimicrobial agent, an anti-inflammatory agent, an anti-bacterial agent, an anti-fungal agent, one or more factors having tissue inductive properties, growth factors, growth promoting and/or growth inhibiting proteins or factors, extracellular matrix components, an anesthetic material, an analgesic material, an osteoblast attracting factor, a drug, a pharmaceutical agent, a pharmaceutical composition, a protein, a glycoprotein, a mucoprotein, a mucopolysaccharide, a glycosaminoglycan, hyaluronic acid, chondroitin 4-sulfate, chondroitin 6-sulfate, keratan sulfate, dermatan sulfate, heparin, heparan
- any of the composite and/or reducing sugar cross-linked collagen based implants disclosed herein and any of the glycated collagen based and/or reducing sugar cross-linked collagen based scaffolds and sponges disclosed in the present application may also include living cells therein.
- the living cells may include but are not limited to cultured cells, stem cells, human cells, animal cells, fibroblasts, pluripotent bone marrow cells, pluripotent stem cells, bone building cells, osteoblasts, mesenchymal cells, mammalian cells, primary cells, genetically modified cells, nerve cells and any combinations thereof.
- Such cells may be introduced into the composite implants and/or sponges and or scaffolds by suitable seeding and incubation, as disclosed hereinabove or by any other method for cell seeding known in the art.
- the specific examples of the composite sponges, implants and the scaffold materials disclosed herein are made by glycation and/or and cross-linking of a single type of collagen, this is not obligatory and any of the above disclosed collagen types including also any suitable mixture of different collagen types (with or without additives and/or additional polymers, and/or living cells) may be used in making the composite sponges, implants and scaffold materials disclosed hereinabove.
Abstract
Description
Claims
Priority Applications (3)
Application Number | Priority Date | Filing Date | Title |
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EP07790001A EP2051658A4 (en) | 2006-07-27 | 2007-07-29 | Composite implants for promoting bone regeneration and augmentation and methods for their preparation and use |
JP2009521418A JP2009544400A (en) | 2006-07-27 | 2007-07-29 | Complex embedded plants for promoting bone regeneration and growth and methods for their production and use. |
AU2007278024A AU2007278024A1 (en) | 2006-07-27 | 2007-07-29 | Composite implants for promoting bone regeneration and augmentation and methods for their preparation and use |
Applications Claiming Priority (2)
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US83347606P | 2006-07-27 | 2006-07-27 | |
US60/833,476 | 2006-07-27 |
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PCT/IL2007/000946 WO2008012828A2 (en) | 2006-07-27 | 2007-07-29 | Composite implants for promoting bone regeneration and augmentation and methods for their preparation and use |
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EP (1) | EP2051658A4 (en) |
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WO (1) | WO2008012828A2 (en) |
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RU2800928C2 (en) * | 2019-06-20 | 2023-08-01 | Датум Дентал Лтд. | Implant containing collagen membrane |
CN113332497A (en) * | 2021-04-30 | 2021-09-03 | 国家纳米科学中心 | Double-sided bracket and preparation method and application thereof |
CN113332497B (en) * | 2021-04-30 | 2022-04-22 | 国家纳米科学中心 | Double-sided bracket and preparation method and application thereof |
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EP2051658A4 (en) | 2012-05-30 |
US20080026032A1 (en) | 2008-01-31 |
US20090269386A1 (en) | 2009-10-29 |
AU2007278024A1 (en) | 2008-01-31 |
JP2009544400A (en) | 2009-12-17 |
WO2008012828A3 (en) | 2009-05-07 |
EP2051658A2 (en) | 2009-04-29 |
US20090269385A1 (en) | 2009-10-29 |
US20090269387A1 (en) | 2009-10-29 |
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