US20160317711A1 - Reinforced biologic material - Google Patents

Abstract

The present disclosure provides an implantable medical device comprising a composite graft material including a first biologic component, such as an acellular tissue matrix, and a second non-biologic component.

Description

• This application is a continuation of application Ser. No. 13/616,556, filed Sep. 14, 2012 (allowed), which is a continuation of application Ser. No. 12/621,890, filed Nov. 19, 2009 and issued as U.S. Pat. No. 8,333,803, and claims priority under 35 U.S.C. §119 to U.S. Provisional Patent Application No. 61/117,068, which was filed on Nov. 21, 2008, each of which are hereby incorporated by reference.
• This invention was made with government support under U.S. Army Contract Number W81XWH-06-1-0136. Accordingly, the government has certain rights in the invention.
• The present disclosure generally relates to implantable medical devices and methods for making the same.
• Surgeons performing ligament and tendon replacement in mammals have long sought a material that approximates the load transmission and performance of the native ligament and tendon structures. Synthetic ligaments and tendons have been made from steel, polyester, polyurethane, polyethylene, Nylons, polytetrafluoroethylene, carbon fiber and other man-made materials. Combinations of anyone or more of the aforementioned materials have also been used to manufacture synthetic ligaments. However, synthetics typically experience decreasing functional capability over time and can wear out, fray, and/or particulate in relatively short time periods after implantation.
• As an alternative to synthetic materials, natural ligament or tendon tissue harvested from autografts and/or allograft sources may also be used in ligament or tendon replacement procedures. As with synthetic materials, for both autografts and allografts, long-term recovery of functional parameters (e.g., failure load, linear and tangential stiffness, failure stress, and strain at failure) remains significantly reduced compared to native ligament, tendon or other soft tissue structures.
• There is a need for a material for ligament, tendon, and other soft tissue repair and replacement that is free of donor site morbidity associated with autografts, has improved failure rates over traditional allografts and synthetic tissues, and better approximates native tissue biomechanical performance.
• This discussion of the background disclosure is included to place the present disclosure in context. It is not an admission that any of the background material previously described was published, known, or part of the common general knowledge as at the priority date of the present disclosure and claims.
• As used herein, the term, “comprise” and variations thereof, such as “comprising” and “comprises,” is not intended to exclude other additives, components, integers or steps.
SUMMARY
• In some embodiments, an implantable medical device is provided. The device comprises a plurality of first elongate non-biologic elements, at least a portion of which are under a tensile or compressive stress prior to implantation; at least one biologic component surrounding at least a portion of the plurality of first elongate elements; and at least one second elongate non-biologic element, wherein the at least one second element secures at least one end portion of the plurality of first elongate non-biologic elements.
• In some embodiments, a method of making a composite prosthesis is provided. The method comprises providing a plurality of first elongate non-biologic elements; applying a load to the plurality of first elongate non-biologic elements; covering at least a portion of the plurality of first elongate non-biologic elements with at least one biologic component; and securing the plurality of first elongate non-biologic elements with at least one second elongate non-biologic element.
• In some embodiments, an implantable medical device is provided. The device comprises at least one non-biologic core material under tensile stress; and at least one biologic element disposed about the at least one non-biologic core, the at least one biologic element comprising a biomatrix; wherein the at least one non-biologic core bears a greater tensile load at a time of implantation than the at least one biologic element, while transmitting stress to the at least one biologic element; and after implantation, the at least one non-biologic core gradually weakens, thereby dynamically transferring additional tensile load to the at least one biologic element.
• In some embodiments, a method of making a composite prosthesis is provided. The method comprises providing at least one non-biologic core; applying a tensile load to the non-biologic core; and disposing at least one biologic element about the at least one non-biologic core, the at least one biologic element comprising a biomatrix; wherein the at least one non-biologic core bears a greater tensile load at a time of implantation than the at least one biologic element, while transmitting stress to the at least one biologic element; and after implantation, the at least one non-biologic core gradually weakens, thereby dynamically transferring additional tensile load to the at least one biologic element.
BRIEF DESCRIPTION OF THE DRAWINGS
• FIG. 1 is an exemplary stress-strain curve for various graft materials.
• FIG. 2 is a graph illustrating the concept of functional target loading of a composite graft material.
• FIGS. 3 and 3A show an exemplary embodiment of a composite graft material.
• FIG. 4A shows an exemplary embodiment of a composite graft material employing a non-biologic component in the form of a flat sheet.
• FIG. 48 shows an exemplary embodiment of a rolled composite graft material.
• FIG. 5 shows an exemplary embodiment of an interference screw for anchoring a composite graft material.
• FIG. 6 is a graph depicting the load capacity over time of certain components of a composite graft material, according to certain embodiments.
• FIG. 7 is a graph illustrating the effect of pre-tensioning on the stress-strain curve of various graft materials, according to certain embodiments.
• FIG. 8A illustrates a plurality of elongate non-biologic components, according to certain embodiments.
• FIG. 8B illustrates a sheath of bioabsorbable material, according to certain embodiments.
• FIG. 9 illustrates a plurality of elongate non-biologic components, according to certain embodiments.
• FIGS. 10A-10G illustrate exemplary embodiments of composite grafts, according to certain embodiments.
DETAILED DESCRIPTION
• The present disclosure relates to implantable medical devices and methods of producing and using such devices. In certain embodiments, the medical devices include composite materials/tissues. In some embodiments, the composite materials comprise both biologic and non-biologic components suitable for use as a tissue implant or replacement for a ligament, tendon, or soft tissue structures. In some embodiments, the composite is constructed with at least two materials, for example, a non-biologic component (e.g., a synthetic polymer) and a biologic component (e.g., a biomatrix). In some embodiments, the non-biologic component is combined with the biologic component to create a composite tissue that utilizes certain properties of the constituent materials.
• The non-biologic component, such as a synthetic polymer, is designed to provide appropriate mechanical properties to the composite structure immediately after implantation and to transmit higher loads over traditional biologic implants when the material is implanted. In some embodiments, the non-biologic component transmits some load and motion to the biologic component. In some embodiments, the biologic component is designed to assist in longer-term healing. In some embodiments, the motion/load distribution between the non-biologic component and the biologic component of the composite material contributes to an environment suited for tissue healing. In some embodiments, the biologic component, via a biomatrix, facilitates a process of becoming or transforming from a basic biologic tissue scaffold to a tissue similar to the native tissue being replaced (e.g., a ligament-like tissue) by encouraging or allowing the in-growth of native cells within the matrix structure of the biologic component.
Composite Material:
• Tissue grafts generally experience some change or deterioration in mechanical characteristics within the first month after implantation. Such mechanical performance characteristics may include, for example, load performance, elasticity and stiffness. Recovery of some or all of the mechanical performance characteristics typically progresses over one to two years after implantation.
• Generally, synthetic materials used in tissue replacement impart an initial load capacity at the time of implantation that can be equal to or higher than natural tissue implants. But, synthetic tissue implants typically experience a continual, and at times, significant loss in load capacity over the first two years after implantation.
• Natural fiber tissue implants, such as autografts and allografts, experience a significant drop in load capacity soon after implantation, with an ultimate recovery of load capacity and other mechanical performance characteristics of between 50-60% of the starting capacity of the natural graft tissue.
• In some embodiments, the composite graft material of the present disclosure combines the benefits of typical synthetic polymer tissue grafts (i.e., relatively high initial mechanical performance characteristics) with the prohealing and better long-term mechanical characteristics of natural tissue grafts. The composite tissue may, for example, perform as a summation of its individual components, or better than a summation of the individual components. For example, a typical synthetic implant experiences degradation with decreasing physical performance over time. The composite tissue of the present disclosure provides a layer of biomatrix around or over the synthetic component, which can result in slower degradation than would be exhibited by a typical, uncoated synthetic implant.
• In some embodiments, the first biologic component and the second non-biologic component of the composite graft material are constructed to produce mechanical performance parameters desired for the specific tissue being replaced. For example, in constructing a composite material for ligament replacement, it may be desirable to have an ultimate load failure of approximately 1800 N. If the constructed first component biomatrix material provides an ultimate failure load of only 400 N, then the synthetic second component can be configured to provide the remaining 1400 N to produce a composite graft material having the desired performance characteristics. Similarly, if the desired stiffness for the ACL replacement graft is 200 N/mm and the biomatrix of the first component provides only 50 N/mm, then the polymeric material of the second component can be configured to provide the remaining stiffness of 150 N/mm.
• FIG. 1 illustrates an exemplary stress-strain curve of various materials.Line2 illustrates a desired curve for an ideal graft.Line4 illustrates an exemplary actual stress-strain curve for either a synthetic or natural tissue graft. As can be seen, the actual grafts are not capable of reaching the desired stress levels for the same amount of strain sought in a desired graft.
• In some embodiments, the composite graft material described herein includes both a biologic and a non-biologic material (e.g., preparation of a weave, or of a braid or of a crimp, or of some other configuration such as a layered or rolled configuration), which raises the stress-strain curve for the composite graft material along the y axis. Consequently,line6 illustrates a modified, composite graft materials having improved performance compared to synthetic or biologic grafts.
• FIG. 2 illustrates the load capacity versus time since implantation of the composite graft material to demonstrate the concept of functional target loading of the composite graft material. The biologic material alone has a relatively low load capacity at the time of implantation, but as the body subsequently heals, the load capacity of the biologic component increases over time. Conversely, a polymer graft's load-bearing capacity is relatively high at implantation, but decreases subsequently. It has been found that a composite graft material consistent with the present disclosure (labeled “Hybrid”), which comprises both a biologic component having a biomatrix and a non-biologic component (such as a polymer), has a relatively stable load-bearing capacity over time (that is, the load bearing capacity starts out, and remains, in the “Target Range”).
• The non-biologic component can be coupled with the biologic component in a variety of ways. For example, the biologic component may be disposed around the non-biologic component (as exemplified inFIG. 3), or vice versa. Alternatively, the biologic component may be embedded within a coating, a knit, weave, braid or other structure of the non-biologic component. To provide load sharing between the non-biologic component and the biologic component, the two components may, for example, be comingled or layered and rolled tightly around one another. In some embodiments, such structures create friction between the components. In some embodiments, compressive force is added to the layered construct, e.g., by including securing straps similar to a belt and hoop design.
• FIG. 3 depicts an exemplary embodiment of the composite graft material of the present disclosure. As shown, tubularnon-biologic component40 is provided havingupper portion42,upper taper region43,lower portion44,lower taper region45, andneck portion46.Biologic component50 is also provided and is illustrated as a sheet with anupper edge51 and alower edge52. In some embodiments,biologic component50 is wrapped aroundneck portion46 ofnon-biologic component40 so thatupper edge51 is in contact proximal to or withupper taper region43 andlower edge52 is in contact proximal to or withlower taper region45.Biologic component50 can wrap or encircleneck portion46 one or more times to form a multi-layer wrap. For example,biologic component50 can wrap aroundneck portion46 ofnon-biologic component40 one time, two times, three times, four times, five times, or more.Biologic component50 can similarly wrap aroundupper portion42 andlower portion43 ofnon-biologic component40 one or more times.
• In some embodiments, after wrappingbiologic component50 aroundnon-biologic component40,upper portion42 ofnon-biologic component40 may be rolled or folded over wrappedbiologic component50 and towardlower portion44 such that at least some ofupper portion42 extends below theupper taper region43 and overlapsneck portion46. In some embodiments,lower portion44 is rolled or folded overbiologic component50 and towardupper portion42 such that at least some oflower portion44 extends abovelower taper region45 and overlapsneck portion46, as depicted inFIG. 3A.
• In some embodiments, securing straps and/ortethers60 are provided to apply compressive force to the rolled composite graft material and provide frictional contact between the biologic component and the non-biologic component. The securing straps may, for example, be constructed of the same material asnon-biologic component40.Tethers60 may also be made from the same material as the non-biologic component of the composite material or from other materials such as stainless steel or non-bioabsorbable polymers.
• Tethers60 may be useful during implantation or construction of the composite graft material. For example, tethers60 may be used to pull the composite graft material into a bone tunnel.Tethers60 may also be used, for example, to anchornon-biologic component40 whilebiologic component50 is wrapped aroundnon-biologic component40.
• Tethers60 can be attached tonon-biologic component40 in various ways. For example, tethers60 may be woven, knitted, or braided intonon-biologic component40.Tethers60 may also be integrated into thenon-biologic component40, and may be configured to detach fromnon-biologic component40. In some embodiments, tethers60 are used as a radiopaque marker.
• In some embodiments, a composite graft material in accordance with the present disclosure is constructed with a non-biologic component in the form of a flat sheet, as illustrated inFIG. 4A.Non-biologic component80 includesupper portion82,lower portion84,neck portion85, and necklateral edge86.Upper portion82 andlower portion84 may be made of same or different non-biologic material asneck portion85. For example,neck portion85 may comprise a high tensile strength textile of a bioabsorbable polymer, whileupper portion82 andlower portion84 comprise a relatively low tensile strength textile of a bioabsorbable polymer.Non-biologic component80 may also, for example, comprise non-textile polymers as previously described.
• Referring still toFIG. 4A,biologic component50 may, for example, be provided as a flat sheet of biologic material comprising an acellular tissue matrix having anupper edge51, alower edge52, and alateral edge53. In some embodiments,non-biologic component80 is placed on top ofbiologic component50 such that necklateral edge86 ofnon-biologic component80 aligns withlateral edge53 ofbiologic component50, and the two layered components are then rolled such that necklateral edge86 andlateral edge53 remain aligned and form the innermost portion of the roll.
• FIG. 4B shows a non-limiting embodiment of a rolled composite graft material in accordance with the present disclosure. This rolled composite graft material is constructed as described above, with thebiologic component50 forming the outside surface of the rolled structure and necklateral edge86 forming the inner most portion of the rolled structure.Upper portion82 andlower portion84 form a multi-layered non-biologic material within the rolled structure and can provide added strength and material to secure the composite graft material to surrounding native tissue, for example, by interference screws.
• In some embodiments, the composite graft material is designed to match the size (length, width, thickness) of the natural structure (i.e., ligament or tendon) it will replace. For example, for an ACL, the composite graft material may be designed to be about 6 to 12 mm in diameter for a unibody device or 3 to 6 mm in diameter if separated into two bundles. It is known that within the body, specific ligament sizes slide and fit between bony structures. A ligament that is too small may not distribute stress evenly, and a ligament that is too large may interfere with or rub against one or both bony structures. Thus, matching the size of the implant material with the native tissue to be removed can reduce complications.
• In some embodiments, the size of the composite graft material is customized to the patient and the tissue being replaced. For example, one or more rolls of biologic and non-biologic components can be added or removed by varying the size or length of the individual components. The longer the pre-rolled composite construct, the more rolls are possible, thereby producing a finished composite graft material having a greater diameter. Alternatively the number of layers of individual components can be altered to adjust the final size of the graft material. For example, a composite construct comprising a tissue layer, a polymer layer, and another tissue layer would provide a larger diameter graft than a composite construct of only two layers.
• Various techniques may be employed to anchor or fix the composite graft material to an implantation site. For example, in an ACL replacement, interference screws are used for anchoring cadaver or autograft materials. In some embodiments, an interference screw is provided that anchors the composite graft material. This is shown inFIG. 5, whereininterference screw90 is inserted into the core ofgraft94 such that as interference screw90 advances, screw90 expands the diameter ofgraft94 to exert outwardly radial pressure against the surround bone tunnel. Other common fixation devices may be used, including cross-pins, endobuttons, sutures, or staples.
• In some embodiments, screws or other anchoring devices can be made of titanium, stainless steel, biodegradable metals, biodegradable or bioabsorbable polymers such as polylactic acid (PIA), polyglycolic acid (PGA), polylactideglycolide acid (PLGA), polydioxanone (PDO), or polycaprolactone (PCL). As a non-limiting example of a typical interference screw, non-limiting mention is made of the RCI screw manufactured by Smith and Nephew, Andover Mass., 01810.
• The biologic component comprising the biomatrix material of the disclosed composite graft material may benefit from the stress of ordinary movement following implantation. For example, the stresses and strains caused by ordinary activity may cause the biologic tissue to be stronger and recover to a greater ultimate strength due to normal remodeling facilitated by mechanical forces.
• In some embodiments, the non-biologic component of the composite tissue graft material described herein is preloaded with a tensile load ranging from greater than 0 N to about 1800 N (e.g., from about 0.1 to about 1700 N; about 10 to about 1600 N, about 100 to about 1500 N, about 150 to 1400 N, about 200 to 1300 N, etc.). The initial stress on strain on the non-biologic material is partially transferred to the biologic component, with the non-biologic component assuming more of the applied stress after reaching a preloaded limit.
• As previously discussed,FIG. 1 illustrates an exemplary stress-strain curve of various tissue grafts.Line2 illustrates a desired curve for an ideal graft.Line4 illustrates an exemplary actual stress-strain curve for either a synthetic or natural tissue graft. As can be seen, natural grafts are not capable of reaching the desired stress levels for the same amount of strain sought in a desired graft. In contrast, because it incorporates both biologic and non-biologic materials, some embodiments of the composite graft materials described herein may exhibit a stress-strain curve that is shifted along the y axis. Consequently,line6 ofFIG. 1 illustrates a composite graft material having improved load capacity performance over actual synthetic or biologic grafts.
• In some embodiments, the non-biologic component, the biologic component, or both the non-biologic and biologic components can be placed under tensile stress prior to implantation. This has the effect of moving the stress-strain curve of the material along the x-axis as depicted inFIG. 7.Line2 illustrates a desired curve for an ideal graft material.Line5 illustrates an actual curve for synthetic or natural tissue graft, and line7 illustrates a curve of a composite graft material that has been subjected to preloading with a tensile stress.
• In some embodiments, a portion of the tensile load applied to the non-biologic component is transferred to the biologic component. The initial strain applied is selected to be high enough to prevent or retard resorption of the biologic component upon implantation, but low enough to avoid physically damaging the biologic tissue. For example, the strain applied to the biologic component may range from less than or equal to 40%, less than or equal to 35%, less than or equal to 30%, less than or equal to 25%, less than or equal to 20%, less than or equal to 15%, less than or equal to 10%, less than or equal to 5%, and less than or equal to 1% of the initial strain applied to the non-biologic material by an initial tensile load. The initial strain applied to the biologic component may also fall within any range specified by a combination of the above recited endpoints, e.g., from greater than or equal to 1% to less than or equal to 40%, from greater than or equal to 5% to less than or equal to 35%, from greater than or equal to 10% to less than or equal to 30%, and from greater than or equal to 15% to less than or equal to 25% of the initial strain imparted to the non-biologic component by an initial tensile load.
• In some embodiments, a composite graft material can be made using a plurality of elongate non-biologic components wrapped with at least one layer of a biologic component. The elongate non-biologic components can be placed under a tensile stress ranging from greater than 0 N to 1800 N (e.g., from about 100 to about 1700 N; about 200 to about 1600 N, about 300 to about 1500 N, etc.), prior to wrapping with the biologic component. The plurality of elongate non-biologic components may also be pre-wrapped in a sheath comprising non-biologic components. At least one end of the non-biologic components can be secured (e.g., by whipping, wrapping, and/or winding) with an additional elongate component to form multiple layers with a raised surface at the end. The biologic component may, for example, be wrapped around the secured plurality of elongate non-biologic components and secured with a smaller fastening or whipping adjacent to the raised surface formed by the secured biologic component.
• In some embodiments, all of the plurality of elongate non-biologic components can be placed under a tensile stress prior to forming the composite graft material. In other embodiments, a percentage of the elongate non-biologic components can be placed under tensile stress prior to forming the composite graft material, while a percentage of the elongate biologic components can be free of tensile stress prior to forming the composite graft material. Further, in some embodiments, the plurality of elongate non-biologic components and the biologic component can be placed under a tensile stress prior to final assembly of the graft.
• FIG. 8A illustrates a plurality of elongatenon-biologic components810. The plurality of elongate components can be bundled as a group having between 200 and 1200 individual elongate components, depending on the size and mechanical requirements of the composite graft material. In some embodiments, the number of individual components can be between 400 and 1000, 600 and 800, or approximately 700 individual components. The elongate non-biologic components may also be bioabsorbable. The plurality ofelongate components810 can have aproximal end812 and adistal end814. Securing elements816 (e.g., whipping elements) can be wrapped around the plurality of components to secure thecomponents810 as abundle818. The plurality ofelongate components810 can be placed under a tensile load prior to securing. Securingelements816 are attached to the plurality ofcomponents810 in such a manner as to retain the preloaded tensile stress in the plurality of elongate components.
• FIG. 8B illustrates a non-limiting embodiment of the present disclosure, whereinsheath815 of bioabsorbable non-biologic material is wrapped around the plurality ofelongate components810. The plurality of elongate components may be loaded with a tensile stress independently of the sheath, or the sheath and plurality of elongate components can be loaded together. Securingelements816 can be wrapped around and over thesheath815 of non-biologic material.
• In some embodiments, a biologic component containing a biomatrix is used to cover or coat at least a portion of the plurality of elongate non-biologic components. In some embodiments, the biologic component may be in the form of a sheet wrapped around a secured plurality of elongate non-biologic components. As a non-limiting example,FIG. 9 illustrates a plurality of elongatenon-biologic components910 having aproximal end912 anddistal end914. Securingelements916 are wrapped around the plurality of elongate components to secure the elongate components as abundle918 and maintain a preloaded tensile stress in theelongate bundle918. Securingelements916 can be wrapped in multiple layers to form a raisedsurface917.
• In some embodiments,biologic component920 may be wrapped in one or more layers around theelongate bundle918 and secured by second securingelements922 proximate the raisedsurface917 formed by securingelements916. Second securingelements922 can be secured about thebiologic component920 and theelongate bundle918 such that the biologic component is free from tensile stress. In some embodiments, thebiologic component920 can be placed under tensile stress and secured by second securingelements922 to maintain the tensile load in thebiologic component920. In some embodiments, the tensile load in the biologic component can range from greater than 0 N to about 1800 N, from greater than 0 to about 600 N, from about 50 to about 300 N, or from about 100 to about 200 N. In some embodiments, thebiologic component920 may, be pre-loaded to the same tensile stress as the plurality ofelongate components910. In some embodiments, thebiologic component920 may also be pre-loaded to tensile stress less than that of the plurality ofelongate components910. In some embodiments, thebiologic component920 can be pre-loaded to a tensile stress more than that of the plurality ofelongate components910.
• In some embodiments, the biologic component can be paired with the plurality of elongate elements in a variety of ways, including: as a single layer sheet wrapped about the elongate non-biologic components; in a jellyroll manner wherein the biologic component is wrapped in multiple layers; as a non-uniform sheet such that multiple layers of biologic component are not concentric about the plurality of elongate elements; as a top sheath wrapped or coated over an inner sheath of non-biologic material; as a coating about the outer surface of the bundle of elongate non-biologic elements; and/or as a coating interspersed throughout the bundle of elongate non-biologic components.
• FIG. 10A showscomposite graft material1000 comprising a plurality of elongatenon-biologic elements1010 andbiologic component1020, whereinbiologic component1020 is wrapped as a sheet in a single layer over the plurality ofelongate elements1010.FIG. 10B shows acomposite graft material1001 comprising a plurality of elongatenon-biologic elements1011 and biologic component1021, wherein biologic component1021 is wrapped as a sheet in a jellyroll fashion with multiple layers over the plurality ofelongate elements1011.FIG. 10C shows a composite graft material1002 comprising a plurality of elongatenon-biologic elements1012 andbiologic component1022, whereinbiologic component1022 is wrapped as a non-uniform sheet in a jellyroll fashion with multiple non-concentric layers over the plurality ofelongate elements1012.FIG. 10D shows acomposite graft material1003 comprising a plurality of elongatenon-biologic elements1013 andbiologic component1023, whereinbiologic component1023 is wrapped as a single layer sheet forming an outer sheath overinner sheath1035 of non-biologic material.Inner sheath1035 is wrapped about the plurality of elongate non-biologic components.
• Biologic component1020 may also be applied as a coating. The coating can, for example, be in the form of a liquid, a powder, or a spray, and may be applied using any suitable technique.
• FIG. 10E shows acomposite graft material1004 comprising a plurality of elongatenon-biologic elements1014 andbiologic component1024, whereinbiologic component1024 coats the outer surface of the plurality ofelongate elements1015.FIG. 10F shows acomposite graft material1005 comprising a plurality of elongate non-biologic elements andbiologic component1025, whereinbiologic component1025 is interspersed between and coats the outer surfaces of the individual elongate elements in the plurality ofelongate elements1015, as shown inFIG. 10G.
• In some embodiments, the plurality of elongate non-biologic elements are secured by a securing material (e.g., a whipping material) such that the securing material is wound about the plurality of elongate non-biologic elements in a manner that is engageable with an anchor screw. The securing material may, for example, be wound to create a screw-thread pattern having a pitch compatible with an anchoring screw to better engage and lock the composite graft material to the anchoring screw upon implantation in the patient. The material used to secure the tissue or biologic component to the plurality of elongate non-biologic elements can also be wound so as to have a screw-screw thread pattern engageable with an anchoring screw. The securing material can form the male or female thread to the threads of the anchoring screw.
• In some embodiments, the composite graft material may be used for ACL replacement. In some embodiments, the composite graft material is designed to have the properties of a typical ACL, e.g., failure load (1200-2400 N); stiffness (150-300 N/mm); failure stress (18-28 MPa); strain at failure (20-35%); and modulus of elasticity (75-180 MPa).
• In some embodiments, the natural mechanical and biologic properties of native ACL tissue may be matched, for example, by selecting and constructing each component of a device to meet specific design requirements. For example, a device meeting the general characteristics of an ACL may be made with a non-biologic component having a modulus of elasticity of about 140 MPa, a maximum rupture load or ultimate load failure of about 1200 N, and degradation resistance through 9 to 16 months before construction of the composite graft material. In some embodiments, the biologic component exhibits a modulus of elasticity of about 55 MPa at the time of implantation and a maximum load at rupture of approximately 600 N before construction of the composite graft material.
• In some embodiments, a composite graft material suitable for ACL repair may, for example, exhibit a maximum rupture load of approximately 1400 N before implantation. In some embodiments, the ultimate failure load of the non-biologic component of such an implant may decrease after implantation, while the failure load of the biologic component will increase over time as native cells proliferate through the biomatrix. In some embodiments, the implant may have an ultimate failure load of approximately 600 N within four months of implantation, approximately 400 N within eight months of implantation, and approximately 1000 N within 12 months of implantation. In some embodiments, the composite graft material for ACL replacement may have a stiffness of approximately 85 N/mm before implantation, approximately 106 N/mm within four months of implantation, approximately 78 N/mm within eight months of fixation, and approximately 176 N/mm within twelve months of fixation.
• FIG. 6 depicts the load capacity over time of the first component, the second component and the composite graft material of a non-limiting example of a composite ACL graft according to various embodiments. As shown, the first component,line8, exhibited a drop in load capacity immediately following implantation with an increase in load capacity thereafter as native cells proliferated throughout the biomatrix.Line10 illustrates the initially high load capacity of the second component after implantation with a steady decrease in load capacity as the second component degraded over time.Line12 shows the load capacity of the composite graft containing both the first component and the second component.
Biologic Component:
• Biologic components that may be suitably used to produce composite graft materials can include any biologic material (e.g., whole tissue or tissue-derived material) with the properties described herein. Non-limiting examples of such biologic materials include biomatrices, such as acellular tissue matrices.
• As used herein, the term “acellular tissue matrix” (“ATM”) refers to a tissue-derived biomatrix structure that is made from any of a wide range of collagen-containing tissues by removing all or substantially all viable cells and all detectable subcellular components and/or debris generated by killing cells. As used herein, an ATM lacking “substantially all viable cells” is an ATM in which the concentration of viable cells is less than 1% of that in the tissue or organ from which the ATM was made.
• Accordingly, in some non-limiting embodiments, the ATMs of the present disclosure contain epithelial basement membrane. In other non-limiting embodiments, the composite grafts disclosed herein lack or substantially lack epithelial basement membrane. In some embodiments, the ATMs include a vascular basement membrane that may facilitate ingrowth of vascular endothelial cells.
• ATM's suitable for use in the present disclosure may, for example, retain certain biologic functions, such as cell recognition, cell binding, the ability to support cell spreading, cell proliferation, cellular in-growth and cell differentiation. Such functions may be provided, for example, by undenatured collagenous proteins (e.g., type I collagen) and a variety of non-collagenous molecules (e.g., proteins that serve as ligands for either molecules such as integrin receptors, molecules with high charge density such as glycosaminoglycans (e.g., hyaluronan) or proteoglycans, or other adhesins). In some embodiments, the ATM's may retain certain structural functions, including maintenance of histological architecture and maintenance of the three-dimensional array of the tissue's components. The ATM's described herein may also, for example, exhibit desirable physical characteristics such as strength, elasticity, and durability, defined porosity, and retention of macromolecules.
• ATMs suitable for use in the present disclosure may be crosslinked or uncrosslinked. In some non-limiting embodiments, the composite graft includes an uncrosslinked ATM. The efficiency of the biologic functions of an ATM can be measured, for example, by the ability of the ATM to support cell proliferation. In some embodiments of the present disclosure, the ATM exhibits at least 50% (e.g., at least: 50%; 60%; 70%; 80%; 90%; 95%; 98%; 99%; 99.5%; 100%; or more than 100%, or any ranges between 50%-100%) of that of the native tissue or organ from which the ATM is made.
• In some embodiments, the biologic component, when implanted, is amenable to being remodeled by infiltrating cells such as differentiated cells of the relevant host tissue, stem cells such as mesenchymal stem cells, or progenitor cells. Remodeling may be directed by the above-described ATM components and signals from the surrounding host tissue (such as cytokines, extracellular matrix components, biomechanical stimuli, and bioelectrical stimuli). For example, the presence of mesenchymal stem cells in the bone marrow and the peripheral circulation has been documented in the literature and shown to regenerate a variety of musculoskeletal tissues [Caplan (1991) J. Orthop. Res. 9:641-650; Caplan (1994) Clin. Plast. Surg. 21:429-435; and Caplan et al. (1997) Clin. Orthop. 342:254-269]. Additionally, in some embodiments, the graft will provide some degree (greater than threshold) of tensile and biomechanical strength during the remodeling process.
• An ATM in accordance with the present disclosure may be manufactured from a variety of source tissues. For example, the ATM may be produced from any collagen-containing soft tissue and musculo-skeletonal tissue (e.g., dermis, fascia, pericardium, dura, umbilical cords, placentae, cardiac valves, ligaments, tendons, vascular tissue (arteries and veins such as saphenous veins), neural connective tissue, urinary bladder tissue, ureter tissue, or intestinal tissue), as long as the above-described properties are retained by the matrix. Moreover, the tissues in which the matrices containing the ATM are placed may include any tissue that can be remodeled by invading or infiltrating cells. Non-limiting examples of such tissues include skeletal tissues such as bone, cartilage, ligaments, fascia, and tendon. Other tissues in which any of the above grafts can be placed include, for example, skin, gingiva, dura, myocardium, vascular tissue, neural tissue, striated muscle, smooth muscle, bladder wall, ureter tissue, intestine, and urethra tissue.
• While an acellular tissue matrix may be made from one or more individuals of the same species as the recipient of the acellular tissue matrix graft, this is not necessarily the case. Thus, for example, an acellular tissue matrix may be made from porcine tissue and implanted in a human patient. Species that can serve as recipients of acellular tissue matrix and donors of tissues or organs for the production of the acellular tissue matrix include, without limitation, mammals, such as humans, nonhuman primates (e.g., monkeys, baboons, or chimpanzees), pigs, cows, horses, goats, sheep, dogs, cats, rabbits, guinea pigs, gerbils, hamsters, rats, or mice.
• As an example of suitable porcine-derived tissue, non-limiting mention is Strattice™, which is a porcine dermal tissue produced by Lifecell Corp, Branchburg, N.J. The tissue matrix may be derived from porcine skin by removing the epidermis while leaving the dermal matrix substantially intact. In some embodiments, the porcine-derived tissue matrix may facilitate tissue ingrowth and remodeling with the patient's own cells. In other embodiments, the material can include a collagenous matrix derived from human cadaver skin (e.g. AlloDerm™, Lifecell Corp, Branchburg, N.J.) that has been processed to remove both the epidermis and cells.
• In general, the steps involved in the production of an acellular tissue matrix include harvesting the tissue from a donor (e.g., a human cadaver or animal source) and cell removal under conditions that preserve biologic and structural function. In certain embodiments, the process includes chemical treatment to stabilize the tissue and avoid biochemical and structural degradation together with or before cell removal. In various embodiments, the stabilizing solution arrests and prevents osmotic, hypoxic, autolytic, and proteolytic degradation, protects against microbial contamination, and reduces mechanical damage that can occur with tissues that contain, for example, smooth muscle components (e.g., blood vessels). The stabilizing solution may contain an appropriate buffer, one or more antioxidants, one or more oncotic agents, one or more antibiotics, one or more protease inhibitors, and/or one or more a smooth muscle relaxant.
• The tissue is then placed in a decellularization solution to remove viable cells (e.g., epithelial cells, endothelial cells, smooth muscle cells, and fibroblasts) from the structural matrix without damaging the biologic and structural integrity of the collagen matrix. The decellularization solution may contain an appropriate buffer, salt, an antibiotic, one or more detergents (e.g., TRITON X-100™, sodium deoxycholate, polyoxyethylene (20) sorbitan mono-oleate), one or more agents to prevent cross-linking, one or more protease inhibitors, and/or one or more enzymes. In some embodiments, the decellularization solution comprises 1% TRITON X-100™ in RPMI media with Gentamicin and 25 mM EDTA (ethylenediaminetetraacetic acid). In some embodiments, the tissue is incubated in the decellularization solution overnight at 37 DC with gentle shaking at 90 rpm. In certain embodiments, additional detergents may be used to remove fat from the tissue sample. For example, in some embodiments, 2% sodium deoxycholate is added to the decellularization solution.
• After the decellularization process, the tissue sample is washed thoroughly with saline. In some exemplary embodiments, e.g., when xenogenic material is used, the decellularized tissue is then treated overnight at room temperature with a deoxyribonuclease (DNase) solution. In some embodiments, the tissue sample is treated with a DNase solution prepared in DNase buffer (20 mM HEPES (4-(2-hydroxyethyl)-1-piperazineethanesulfonic acid), 20 mM CaCl2 and 20 mM MgCl2). Optionally, an antibiotic solution (e.g., Gentamicin) may be added to the DNase solution. Any suitable buffer can be used as long as the buffer provides suitable DNase activity.
• Elimination of the α-gal epitopes from the collagen-containing material may diminish the immune response against the collagen-containing material. The α-gal epitope is expressed in non-primate mammals and in New World monkeys (monkeys of South America) as well as on macromolecules such as proteoglycans of the extracellular components. U. Galili et al., J. Biol. Chem. 263: 17755 (1988). This epitope is absent in Old World primates (monkeys of Asia and Africa and apes) and humans, however. Id. Anti-gal antibodies are produced in humans and primates as a result of an immune response to α-gal epitope carbohydrate structures on gastrointestinal bacteria. U. Galili et al., Infect. Immun. 56: 1730 (1988); R. M. Hamadeh et al., J. Clin. Invest. 89: 1223 (1992).
• Since non-primate mammals (e.g., pigs) produce α-gal epitopes, xenotransplantation of collagen-containing material from these mammals into primates often results in rejection because of primate anti-Gal binding to these epitopes on the collagen-containing material. The binding results in the destruction of the collagen-containing material by complement fixation and by antibody dependent cell cytotoxicity. U. Galili et al., Immunology Today 14:480 (1993); M. Sandrin et al., Proc. Natl. Acad. Sci. USA 90: 11391 (1993); H. Good et al., Transplant. Proc. 24: 559 (1992); B. H. Collins et al., J. Immunol. 154: 5500 (1995). Furthermore, xenotransplantation results in major activation of the immune system to produce increased amounts of high affinity anti-gal antibodies. Accordingly, in some embodiments, when animals that produce α-gal epitopes are used as the tissue source, the substantial elimination of α-gal epitopes from cells and from extracellular components of the collagen-containing material, and the prevention of re-expression of cellular α-gal epitopes can diminish the immune response against the collagen-containing material associated with anti-gal antibody binding to α-gal epitopes.
• To remove α-gal epitopes, after washing the tissue thoroughly with saline to remove the DNase solution, the tissue sample may be subjected to one or more enzymatic treatments to remove certain immunogenic antigens, if present in the sample. In some embodiments, the tissue sample may be treated with an α-galactosidase enzyme to eliminate α-gal epitopes if present in the tissue. In some embodiments, the tissue sample is treated with α-galactosidase at a concentration of 300 U/L prepared in 100 mM phosphate buffer at pH 6.0 In other embodiments, the concentration of α-galactosidase is increased to 400 u/L for adequate removal of the α-gal epitopes from the harvested tissue. Any suitable enzyme concentration and buffer can be used as long as sufficient removal of antigens is achieved.
• Alternatively, rather than treating the tissue with enzymes, animals that have been genetically modified to lack one or more antigenic epitopes may be selected as the tissue source. For example, animals (e.g., pigs) that have been genetically engineered to lack the terminal α-galactose moiety can be selected as the tissue source. For descriptions of appropriate animals see co-pending U.S. application Ser. No. 10/896,594 and U.S. Pat. No. 6,166,288, the disclosures of which are incorporated herein by reference in their entirety.
• After the acellular tissue matrix is formed, histocompatible, viable cells may optionally be seeded in the acellular tissue matrix to produce a graft that may be further remodeled by the host. In some embodiments, histocompatible viable cells may be added to the matrices by standard in vitro cell co-culturing techniques prior to transplantation, or by in vivo repopulation following transplantation. In vivo repopulation can be by the recipient's own cells migrating into the acellular tissue matrix or by infusing or injecting cells obtained from the recipient or histocompatible cells from another donor into the acellular tissue matrix in situ. Various cell types can be used, including embryonic stem cells, adult stem cells (e.g. mesenchymal stem cells), and/or neuronal cells. In various embodiments, the cells can be directly applied to the inner portion of the acellular tissue matrix just before or after implantation. In certain embodiments, the cells can be placed within the acellular tissue matrix to be implanted, and cultured prior to implantation.
• Particulate ATM can be made from any of the above described non-particulate ATMs by any process that results in the preservation of the biologic and structural functions described above. As used herein, particulate ATMs are those particulate or pulverized (powdered) matrices having a longest dimension of 1.0 mm or less.
• In some embodiments, particulate ATM used in the present disclosure is manufactured so as to minimize damage to collagen fibers, including sheared fiber ends. As a non-limiting example of a suitable method for making particulate ATM is described in U.S. Pat. No. 6,933,326. The particle size for Cymetra is in the range of about 60 microns to about 150 microns as determined by mass spectrophotometry.
Non-Biologic Component:
• The at least one non-biologic component of the present disclosure may, for example, comprise biocompatible natural and/or synthetic materials. Biocompatible natural materials may include, for example, collagen, fibrin, and silk. Biocompatible synthetic materials may include, for example, bioabsorbable polymers, non-bioabsorbable polymers, and metallic alloys or compositions. In some embodiments of the present disclosure, a non-biologic component that is biocompatible and bioabsorbable is used. Utilizing bioabsorbable polymers may allow for a transfer of loads from the non-biologic component (e.g., the polymer) to the biologic component as native tissue regenerates throughout the matrix structure of the biologic component.
• As used herein, a “biocompatible” composition is one that has the ability to support cellular activity necessary for complete or partial tissue regeneration, but does not stimulate an unacceptable inflammatory or immunological response in the host. The term, “unacceptable local inflammatory or immunological response in the host” means a local or systemic inflammatory or immunologic response that prevents tissue regeneration.
• As used herein, the term “bioabsorbable” means that a material can be absorbed by a mammalian body via biologically mediated degradation processes, such as enzymatic and cellular processes and/or chemically mediated degradation processes. Such processes include, for example, degradation processes wherein the degradation products are excreted through one of the body's organ systems or in which the degradation products are incorporated into normal metabolic pathways.
• In some embodiments, a suitable bioabsorbable material for use in the present disclosure, is made of a poly-hydroxybutyrate (a polyhydroxyalkanoate), such as the TephaFlex polymer produced by Tepha, Inc. of Cambridge, Mass. In some embodiments, useful bioabsorbable materials include, for example, polylactic acid (PLA), polyglycolic acid (PGA), polylactideglycolide acid (PLGA), polydioxanone (PDO), or polycaprolactone (PCL). In some embodiments, bioabsorbable materials suitable for use in the present disclosure include polyanhydrides, polyorthoesters, poly(amino acids), polypeptides, polydepsipeptides, nylon-2/nylon-6coplyamides, poly(alkylene succinates), poly(hydroxyl butyrate) (PHB), poly (butylene diglocolate), poly (ε-caprolactone), polydihydropyrans, polyphosphazenes, poly (ortho ester), poly (cyano acrylates), modified polysaccharides, cellulose, starch, chitin, modified proteins, collagen, fibrin, and combinations and copolymers thereof. Non-limiting examples of non-bioabsorbable materials include noble metals such as gold, as well as the near noble metals.
• In some embodiments, synthetic polymers that may be used in accordance with the present disclosure include those listed in U.S. Pat. No. 5,885,829, the disclosure of which is incorporated herein by reference in its entirety.
• The non-biologic components used herein may be provided in any form. In some embodiments, the non-biologic components are in the form of a molded shape (e.g., as a single contiguous polymeric piece). Further, in some embodiments, the non-biologic components are in the form of a textile comprised of multiple yarns, the yarn being either a monofilament or a multifilament structure (such as a braid). Textile manufacturing methods can then make final structures that are knitted, woven, braided, nonwoven, or combinations thereof.
• Although the present disclosure has been described with reference to certain non-limiting embodiments, other implementations are possible. For example, the composite material may be used for many applications where soft tissues need to be replaced and yet provide specific load-carrying or biomechanical characteristics, including ligament, tendon or soft tissue replacement about the knees, ankles, shoulders, neck, and spine. Other hybrid systems can be developed utilizing the same basic ideas as described above. Examples include: artificial meniscus replacement or repair; abdominal wall (e.g., hernia) repair; cartilage repair in, for example, knees, shoulders and hips; joint resurfacing (instead of removing joints, the joint articulating surface can simply be covered with a composite material reinforced with fabric using appropriately designed anchors or sutures); and pace maker pouches (a simple bag/pouch used to contain pacers or pain manager systems would make periodic replacement much simpler and would create a more stable anchor pacer implant).
• Accordingly, other embodiments will be apparent to those skilled in the art from consideration of the specification disclosed herein. It is intended that the specification and embodiments disclosed herein be considered as exemplary only, with a true scope being indicated by the following claims.

Claims (27)

What is claimed is:

1. A method of making a composite prosthesis, comprising:

providing a plurality of first elongate non-biologic elements;

applying a load to the plurality of first elongate non-biologic elements;

covering at least a portion of the plurality of first elongate non-biologic elements with at least one biologic component; and

securing the plurality of first elongate non-biologic elements with at least one second elongate non-biologic element.

2. The method ofclaim 1, wherein the plurality of first elongate non-biologic elements comprise at least one material chosen from bioabsorbable polymer, bioabsorbable metal, or a combination of bioabsorbable polymer and bioabsorbable metal.

3. The method ofclaim 1, wherein the plurality of first elongate non-biologic elements comprise at least one material chosen from polyhydroxyalkanoate, polyhydroxybutyrate, polylactic acid (PLA), polyglycolic acid (PGA), polylactideglycolide acid (PLGA), polydioxanone (PDO), polycaprolactone (PCL), a polyanhydride, a polyorthoester, a poly(amino acid), a polypeptide, a polydepsipeptide, a nylon-2/nylon-6 copolyamide, a poly(alkylene succinate), poly(hydroxyl butyrate) (PHB), poly (butylene diglocolate), poly (ε-caprolactone), a polydihydropyran, a polyphosphazene, a poly (cyano acrylates), modified polysaccharides, cellulose, starch, chitin, modified proteins, collagen, fibrin, and copolymers thereof.

4. The method ofclaim 1, wherein the plurality of first elongate non-biologic elements comprise at least one of a noble metal, near noble metal, iron, or magnesium.

5. The method ofclaim 1, wherein the plurality of first elongate non-biologic elements comprises a plurality of threads, cords, cables, ribbons, or braids.

6. The method ofclaim 1, further comprising:

covering the plurality of first elongate non-biologic elements with a bioabsorbable sheath; and

applying a tensile load to the sheath and the plurality of first elongate non-biologic elements.

7. The method ofclaim 1, wherein all or a portion of the plurality of first elongate non-biologic elements are tensile loaded with a force ranging from greater than 0 N to about 1800 N.

8. The method ofclaim 7, wherein only a portion of the plurality of first elongate non-biologic elements are tensile loaded.

9. The method ofclaim 1, wherein all or a portion of the plurality of first elongate non-biologic elements are compressively loaded.

10. The method ofclaim 9, wherein only a portion of the first elongate non-biologic elements are compressively loaded.

11. The method ofclaim 1, wherein the at least one biologic components comprises a biomatrix.

12. The method ofclaim 11, wherein the biomatrix comprises an acellular tissue matrix or a particulate acellular tissue matrix.

13. The method ofclaim 1, wherein the at least one biologic component forms a sheath about the plurality of first elongate non-biologic elements.

14. The method ofclaim 1, wherein the at least one biologic component at least partially separates at least one of the elongate non-biologic elements comprised within the plurality of first elongate non-biologic elements.

15. The method ofclaim 1, wherein the at least one biologic component at least partially coats each elongate member comprised within the plurality of elongate non-biologic elements.

16. The method ofclaim 1, further comprising applying the at least one biologic component to the plurality of first elongate non-biologic elements in the form of a coating, a paste, a powder, a liquid, or a spray.

17. The method ofclaim 1, wherein securing the plurality of first elongate non-biologic elements comprises at least one of whipping, wrapping, and winding an end portion of the plurality of first elongate non-biologic elements with the at least one second elongate non-biologic element.

18. The method ofclaim 17, wherein securing the plurality of first elongate non-biologic elements includes formation of at least one layer of the at least one second elongate non-biologic element about the plurality of first elongate non-biologic elements.

19. The method ofclaim 18, wherein securing the plurality of first elongate non-biologic elements includes formation of a pitched portion for engaging an anchoring screw.

20. The method ofclaim 1, wherein the at least one second elongate non-biologic element is bioabsorbable.

21. The method ofclaim 1, wherein the at least one second elongate non-biologic element is comprised of the same material as the plurality of first elongate non-biologic elements.

22. The method ofclaim 1, wherein the at least one second elongate non-biologic element comprises a thread, cord, cable, ribbon, or braid.

23. The method ofclaim 1, wherein the second elongate non-biologic element secures the plurality of first elongate non-biologic elements while maintaining the load applied to the plurality of first elongate non-biologic elements.

24. The method ofclaim 1, wherein the plurality of first elongate non-biologic elements have a higher load capacity than the at least one biologic component at a time of implantation.

25. The method ofclaim 1, wherein the at least one biologic component has a higher load capacity than the plurality of first elongate non-biologic elements after implantation and following ingrowth of native cells within the at least one biologic component.

26. An method of making a composite prosthesis, comprising:

providing at least one non-biologic core;

applying a tensile load to the non-biologic core; and

disposing at least one biologic element about the at least one non-biologic core, the at least one biologic element comprising a biomatrix,

wherein:

the at least one non-biologic core bears a greater tensile load at a time of implantation than the at least one biologic element, while transmitting strain to the at least one biologic element; and

after implantation, the at least one non-biologic core gradually weakens, thereby transferring additional tensile load to the at least one biologic element.

27. The method ofclaim 26, wherein the strain applied to the at least one biologic element by the at least one non-biologic core is less than 50% of the strain applied to the at least one non-biologic care by the at least one tensile load.

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