US20080206297A1 - Porous composite biomaterials and related methods - Google Patents
Porous composite biomaterials and related methods Download PDFInfo
- Publication number
- US20080206297A1 US20080206297A1 US12/039,666 US3966608A US2008206297A1 US 20080206297 A1 US20080206297 A1 US 20080206297A1 US 3966608 A US3966608 A US 3966608A US 2008206297 A1 US2008206297 A1 US 2008206297A1
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- United States
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- composite material
- porous
- porous composite
- poly
- porosity
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- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/3094—Designing or manufacturing processes
- A61F2/30942—Designing or manufacturing processes for designing or making customized prostheses, e.g. using templates, CT or NMR scans, finite-element analysis or CAD-CAM techniques
- A61F2002/30957—Designing or manufacturing processes for designing or making customized prostheses, e.g. using templates, CT or NMR scans, finite-element analysis or CAD-CAM techniques using a positive or a negative model, e.g. moulds
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2210/00—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2210/0004—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof bioabsorbable
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2210/00—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2210/0071—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof thermoplastic
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2230/0063—Three-dimensional shapes
- A61F2230/0069—Three-dimensional shapes cylindrical
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2250/0014—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis
- A61F2250/0015—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in density or specific weight
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2250/0014—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis
- A61F2250/0018—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in elasticity, stiffness or compressibility
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2250/0014—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis
- A61F2250/0023—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in porosity
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2250/0014—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis
- A61F2250/003—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in adsorbability or resorbability, i.e. in adsorption or resorption time
- A61F2250/0031—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in adsorbability or resorbability, i.e. in adsorption or resorption time made from both resorbable and non-resorbable prosthetic parts, e.g. adjacent parts
Definitions
- the present disclosure relates generally to composite biomaterials and more particularly to porous composite biomaterials and related methods.
- Natural bone grafts such as autogenous bone grafts (autografts) are commonly used in procedures for repairing or replacing bone defects because they provide good structural support and osteoinductivity. Natural bone grafts involve removing or harvesting tissue from another part of a host's body (e.g., typically from the iliac crest, hip, ribs, etc.) and implanting the harvested tissue in the defect site. Not only do these grafts require an added surgical procedure needed to harvest the bone tissue, these grafts have limitations, including for example, transplant site morbidity.
- One alternative to autografts is allografts, which involve removing and transplanting tissue from another human (e.g., from bone banks that harvest bone tissue from cadavers) to the defect site.
- DBM Demineralized bone matrix
- Synthetic bone substitute materials have been researched in the treatment of diseased bone (e.g., osteoporosis), injured bone (e.g., fractures), or other bone defects in lieu of natural bone grafts. Synthetic bone substitutes are viable alternatives to the more traditional methods described above. However, synthetic substitute materials used to repair diseased bones and joints should function or perform biologically and mechanically (i.e., as the structural support role of the bone itself) by, for example, mimicking the density and overall physical structure of natural bone to provide a framework for ingrowth of new tissue.
- One type or application of a synthetic bone substitute is a scaffold, which provides support for bone-producing cells.
- Scaffolds may be biodegradable, which degrade in vivo, or they may be non-biodegradable to provide permanent implant fixation (e.g., spinal fusion cages).
- scaffolds are typically biocompatible, and some may be bioactive, bioresorbable, osteoconductive, and/or osteoinductive. The shapability, deliverability, cost, and ability to match the mechanical properties of the surrounding host tissue are other factors that vary among different types of scaffolds and other bone substitutes.
- FIG. 1A is a perspective view of an example porous composite material described herein.
- FIG. 1B is a cross-sectional view of a portion of the example porous composite material of FIG. 1A .
- FIG. 2A-2C are scanning electron micrographs of a portion of the example porous composite material shown in increasing magnification.
- FIG. 3 is graphical representation of the elastic modulus of example apatite reinforced polymer composites versus the reinforcement volume fraction.
- FIG. 4 shows scanning electron micrograph of a portion of the surface of an example composite material reinforced with calcium phosphate whiskers embedded within and exposed on the surface, and schematically showing the orientation of the whiskers relative to the loading direction of the material or scaffold strut.
- FIG. 5A is a schematic illustration of a known spinal fusion cage inserted between spinal vertebrae.
- FIG. 5B illustrates the example known spinal fusion cage of FIG. 5A .
- FIG. 6 illustrates another example scaffold described herein.
- FIG. 7 illustrates yet another example scaffold described herein.
- FIG. 8 is a flow diagram illustrating an example process of creating an example composite material apparatus described herein.
- the example methods, apparatus, and materials described herein provide a biocompatible, bioactive synthetic porous composite for use as synthetic bone substitute materials.
- the synthetic composite may provide a synthetic porous scaffold for use an orthopedic implant and/or be injectable via percutaneous or surgical injection to cure in vivo. Because the example composite material is used to form a scaffold or matrix that is used in an implantable device, the descriptions of one or more of these structures may also describe one or more of the other structures.
- the synthetic porous composites are tailored to mimic biological and mechanical properties of bone tissue for implant fixation, synthetic bone graft substitutes, tissue engineering scaffolds, interbody spinal fusion, or other orthopedic applications.
- An example porous composite material described herein reduces subsidence and/or bone resorption resulting from mechanical mismatch problems between a synthetic scaffold of an implant device and the peri-implant tissue. Additionally, porosity and/or the pore sizes of the example synthetic composite are tailorable to specific applications to effectively promote the vascularization and growth of bone in the pores and/or void spaces of the example scaffolds, thereby improving bonding between the scaffolds and peri-implant tissue.
- the example composite material or scaffolds are synthesized or made through a process that enables reinforcement particles to be integrally formed with or embedded within polymer matrices.
- the polymer matrices embedded with the reinforcement material provide improved material properties (e.g., stiffness, fatigue strength, and toughness).
- the reinforcement particles are also exposed on a surface of the matrices, which promotes bioactivity and/or bioresorption.
- the process provides flexibility to tailor the level of reinforcement particles and porosity for a desired application.
- a porogen material may be used to vary the porosity, while the pore size is tailored by, for example, sieving the porogen to a desired size.
- the mechanical properties (e.g., stiffness, strength, toughness, etc.) of the example scaffold of the implant device may be tailored to match those of the adjacent peri-implant bone tissue to reduce mechanical mismatch problems. Reducing mechanical mismatch provides a decreased risk of subsidence, stress shielding, bone resorption, and/or subsequent failure of adjacent peri-implant bone tissue. Additionally, the example scaffold of the implant device may include a significantly high porosity to promote bone ingrowth, while exhibiting significantly higher effective mechanical properties such as, for example, the mechanical properties of trabecular bone.
- the example composite material includes a continuous porous biocompatible matrix having a thermoplastic polymer matrix reinforced with anisometric calcium phosphate particles.
- a composite material includes a polyetheretherketone (PEEK) or a polyetherketoneketone (PEKK) matrix reinforced with various volume fractions of hydroxyapatite (HA) whiskers (e.g., 20 or 40 volume percent), wherein the matrix is approximately between 70% and 90% porous.
- PEEK polyetheretherketone
- PEKK polyetherketoneketone
- HA hydroxyapatite
- the porous matrix includes a biocompatible, microporous polymer cage reinforced with anisometric calcium phosphate particles and bone morphogenic protein (BMP) such as, for example, rhBMP-2, which can be dispersed or accommodated by the void spaces and/or pores of the example porous scaffold and/or exposed on the surface of the example porous scaffold. Additionally, the BMP binds to the calcium phosphate further localizing the BMP to the surface of the scaffold or matrix.
- BMP bone morphogenic protein
- the example composite materials described herein may be used for applications such as, for example, synthetic bone graft substitutes, bone ingrowth surfaces applied to existing implants, tissue engineering scaffolds, interbody spinal fusion cages, etc.
- carrier materials e.g., collagen, hydrogels, etc.
- growth factors such as BMP
- a femur includes a cortical bone that has a relative porosity on the order of about 5-15%, and a trabecular bone that has a porosity on the order of about 75-95%. Due to the highly significant porosity differences, the trabecular bone exhibits significantly lower effective mechanical properties compared to the cortical bone. Therefore, depending on the application, synthetic composite materials for use as scaffolds and/or spinal fusion cages or other implant devices should possess the mechanical properties exhibited by the cortical bone or the trabecular bone, but must also have effective porosity to promote bone growth.
- the example scaffold of the implant device described herein may be tailored to substantially match or mimic the mechanical properties (e.g., stiffness, strength, toughness, etc.) of the adjacent and/or substituted bone tissue.
- the mechanical properties e.g., stiffness, strength, toughness, etc.
- Several factors may be varied during the synthesis of the composite material and scaffold of the implant device to tailor the mechanical properties including the calcium phosphate reinforcement volume fraction, aspect ratio, size and orientation; the polymer; and the size, volume fraction, shape and directionality of the void space and/or porosity. Tailoring the mechanical properties of the scaffold reduces the likelihood of mechanical mismatch leading to a decreased risk of subsidence, stress shielding, bone resorption and/or subsequent failure of adjacent vertebrae.
- FIG. 1A illustrates the example synthetic porous composite material 100 described herein.
- FIG. 1B is a cross-sectional view of a portion of the example porous composite material 100 of FIG. 1A .
- the example synthetic composite material 100 provides a synthetic porous scaffold 101 for use or in as an orthopedic implant.
- the example synthetic porous composite material 100 includes a porous thermoplastic polymer (e.g., a PEEK polymer) matrix 102 having anisometric calcium phosphate reinforcement particles 104 integrally formed or embedded with the matrix 102 and/or exposed on a surface of the matrix.
- a porous thermoplastic polymer e.g., a PEEK polymer
- the porous polymer matrix 102 includes a substantially continuous porosity and a plurality of pores 106 to enable bone ingrowth into the porous matrix 102 .
- the matrix 102 is substantially continuously interconnected via a plurality of struts 108 .
- at least one of the plurality of struts 108 may be a load-bearing strut.
- FIGS. 2A-2C are scanning electron micrographs showing increasing magnification of a portion of an example scaffold 200 with struts 202 .
- the example scaffold 200 is a PEEK scaffold reinforced with 40% by volume HA whiskers 204 .
- FIG. 2A illustrates the architecture or matrix 206 of the scaffold 200 and FIG. 2B illustrates an enlarged portion of the struts 202 .
- the HA whiskers 204 are integrally formed and/or embedded within the matrix 206 of the scaffold 200 for reinforcement.
- the HA whiskers 204 are also exposed on a surface 208 of the matrix of the scaffold 200 for bioactivity and/or bioresorption, as noted above.
- the HA whiskers 204 are aligned in a sheet texture and are exposed on the surface 208 of the struts 202 .
- thermoplastic polymer of the example scaffolds described herein may be a biodegradable polymer for synthetic bone graft substitute applications, or nonbiodegradable for implant fixation applications.
- the thermoplastic polymer includes a continuous matrix of a composite material and is biocompatible and/or bioresorbable as described above. Additionally or alternatively, the polymer may be a radiolucent polymer, bioresorbable (i.e., a material capable of being resorbed by a patient under normal physiological conditions) and/or non-bioresorbable, as desired.
- the thermoplastic polymer matrix may include a polymer suitable for injection via percutaneous or surgical injection so that the composite material 100 cures in vivo.
- Suitable non-resorbable polymers include, without limitation, polyaryletherketone (PAEK), polyetheretherketone (PEEK), polyetherketonekteone (PEKK), polyetherketone (PEK), polyethylene, high density polyethylene (HDPE), ultra high molecular weight polyethylene (UHMWPE), low density polyethylene (LDPE), polyethylene oxide (PEO), polyurethane, polypropylene, polypropylene oxide (PPO), polysulfone, polypropylene, copolymers thereof, and blends thereof.
- PAEK polyaryletherketone
- PEEK polyetheretherketone
- PEKK polyetherketonekteone
- PEK polyetherketone
- PEK polyethylene, high density polyethylene (HDPE), ultra high molecular weight polyethylene (UHMWPE), low density polyethylene (LDPE), polyethylene oxide (PEO), polyurethane, polypropylene, polypropylene oxide (PPO), polysulfone, polypropylene, copolymers thereof, and
- Suitable bioresorbable polymers include, without limitation, poly(DL-lactide) (PDLA), poly(L-lactide) (PLLA), poly(glycolide) (PGA), poly( ⁇ -caprolactone) (PCL), poly(dioxanone) (PDO), poly(glyconate), poly(hydroxybutyrate) (PHB), poly(hydroxyvalerate (PHV), poly(orthoesters), poly(carboxylates), poly(propylene fumarate), poly(phosphates), poly(carbonates), poly(anhydrides), poly(iminocarbonates), poly(phosphazenes), copolymers thereof, and blends thereof.
- PDLA poly(DL-lactide)
- PLLA poly(L-lactide)
- PGA poly(glycolide)
- PCL poly( ⁇ -caprolactone)
- PDO poly(dioxanone)
- PDO poly(glyconate), poly(hydroxybutyrate) (PH
- Suitable polymers that are injectible via percutaneous or surgical injection that cure in vivo include, without limitation, polymethylmethacrylate (PMMA), and other polyacrylics from monomers such as bisphenol a hydroxypropylmethacrylate (bis-GMA) and/or tri(ethylene glycol) dimethacrylate (TEG-DMA).
- PMMA polymethylmethacrylate
- bis-GMA bisphenol a hydroxypropylmethacrylate
- TEG-DMA tri(ethylene glycol) dimethacrylate
- synthetic substitute composite materials made of polymers satisfy the functional criteria of an implantable device because they are, for example, formable and inexpensive, polymers alone lack biological efficacy to promote bone growth and/or may lack requisite mechanical properties to support load levels.
- the polymers are reinforced with calcium phosphates.
- the aspect ratio, size, volume fraction and degree of preferred orientation of the calcium phosphate particles 104 may be tailored for the desired material properties and implant performance. For example, consider the information presented in FIG. 3 , which is a graphical illustration of the elastic modulus of HA whisker and powder reinforced polymer composite materials versus the volume fraction percentage of the apatite calcium phosphates that is mixed with the polymer matrix.
- the shaded areas of FIG. 3 show approximate regions for the given mechanical property of the human cortical bone tissue.
- the elastic modulus of the composite materials increases with increasing HA content.
- increasing the level of HA reinforcement in polymer composites increases cellular activity during osteointegration.
- the calcium phosphate reinforcement particles 104 may be in the form of single crystals or dense polycrystals, but are at least in some portion anisometric.
- “Anisometric” refers to any particle morphology (shape) that is not equiaxed (e.g., spherical), such as whiskers, plates, fibers, etc.
- Anisometric particles are usually characterized by an aspect ratio.
- HA single crystals are characterized by the ratio of dimensions in the c- and a-axes of the hexagonal crystal structure.
- the anisometric particles in the present disclosure have an aspect ratio greater than 1.
- the mean aspect ratio of the reinforcement particles is from about 1 to about 100.
- the reinforcement particles can be provided in an amount of from about 1% by volume of the composite biomaterial to about 60% by volume, and for example, from about 20% by volume of the composite to about 50% by volume.
- the calcium phosphate reinforcements particles 104 may be oriented in bulk or near the surface of the polymer matrix 102 to provide directional properties, if desired. For example, if the reinforcement particles 104 are predominately aligned within the matrix 102 the morphological alignment of the particles 104 provides anisotropy for the overall composite 100 , which can be tailored to be similar to the anisotropic mechanical properties of bone tissues.
- FIG. 4 shows a micrograph of anisometric calcium phosphate reinforcement 400 on the surface of a dense composite polymer matrix 402 . Also shown in FIG. 4 is a schematic illustration of a portion of matrix 402 and illustratively showing the orientation of the reinforcement particles 400 relative to the loading direction of the material and/or a scaffold strut, which is, for example, at an angle ⁇ .
- the reinforcement particles 104 may have a maximum dimension from about 20 nm to about 2 mm, and for example, between 20 nm to about 100 ⁇ m. While both nano- and micro-scale calcium phosphate particles improve the mechanical properties of the example synthetic composite material 100 described herein, nano-scale calcium phosphate particles are particularly effective for enhancing bioresorbability and cell attachment, and micro-scale particles are particularly effective for obtaining a uniform dispersion within the matrix 102 .
- Suitable calcium phosphates may include, without limitation, calcium HA, HA whiskers, HA, carbonated calcium HA, beta-tricalcium phosphate (beta-TCP), alpha-tricalcium phosphate (alpha-TCP), amorphous calcium phosphate (ACP), octacalcium phosphate (OCP), tetracalcium phosphate, biphasic calcium phosphate (BCP), anhydrous dicalcium phosphate (DCPA), dicalcium phosphate dihydrate (DCPD), anhydrous monocalcium phosphate (MCPA), monocalcium phosphate monohydrate (MCPM), and combinations thereof.
- DCPA dicalcium phosphate
- DCPD dicalcium phosphate dihydrate
- MCPA monocalcium phosphate monohydrate
- MCPM monocalcium phosphate monohydrate
- a synthetic composite material 100 not only bears physiological levels of load, but also promotes oseteointegration—the direct structural and functional connection between the living bone and the surface of the load-bearing implant.
- the bioactive calcium phosphate particles 104 e.g., HA whiskers
- exposed on the surface of the example porous matrix 102 promote a stable bone-implant interface. Osteointegration also requires the vascularization and growth of bone into an implant via interconnected and/or continuous porosity.
- the size, volume fraction, shape, and directionality of the void spaces and/or pores 106 may be tailored to optimize osteoconduction and implant mechanical properties.
- the pores 106 may be any size or shape, while maintaining a continuous network to promote a fusion through the formation of new bone tissue in the void spaces and/or pores 106 .
- the pores 106 may be present throughout the matrix 102 as illustrated in FIG. 1A .
- the pores 106 may be functionally graded in any material or implant direction, for example, radially, as shown in FIGS. 6 and 7 , from a highly porous region to a relatively dense region, or may include a void space.
- the change in porosity from one region to another may be very distinct, for example as shown in FIGS.
- the graded change may be uniform or variant.
- the central void may be any shape or size, and may receive (e.g., be filled) a material, a structure, or the composite material 100 (i.e., the composite material graded from the porous outer surface to a dense center), thereby forming a porous outer perimeter and a dense central region. Examples are further described in connection with FIGS. 6 and 7 below.
- the porosity and/or pore sizes 106 may be selectively formed by the inclusion of, for example, a porogen material during synthesis of the composite material 100 .
- Pores spaces may range from about 100 Mm to about 500 Mm, and, for example, from about 250 Mm to about 500 Mm.
- the example composite biomaterial 100 may additionally contain some fraction of microporosity within scaffold struts that is less than about 10 Mm in size.
- the total amount of porosity within porous regions may range from about 1% to about 90% by volume, and, for example, between about 70% and 90% by volume.
- the porosity may also be tailored via other processes such as, for example, microsphere sintering, fiber weaving, solvent casting, electrospinning, freeze drying (lyophilization), thermally induced phase separation, gas foaming, and rapid prototyping processes such as, for example, solid freeform fabrication, robotic deposition (aka, robocasting), selective laser sintering, fused deposition modeling, three-dimensional printing, laminated object manufacturing, stereolithography, etc., or any other suitable process(es) or combination(s) thereof.
- processes such as, for example, microsphere sintering, fiber weaving, solvent casting, electrospinning, freeze drying (lyophilization), thermally induced phase separation, gas foaming, and rapid prototyping processes such as, for example, solid freeform fabrication, robotic deposition (aka, robocasting), selective laser sintering, fused deposition modeling, three-dimensional printing, laminated object manufacturing, stereolithography, etc., or any other suitable process(es) or combination(s) thereof.
- the example composite material 100 may optionally include additives, if desired.
- the composite material 100 may include one or more surface-active agents to enhance interfacial bonding between the reinforcement particles 104 and the polymer matrix 102 .
- the void spaces and/or pores 106 may accommodate and deliver one or more growth factors such as, for example, BMP, to enhance osteoinductivity and/or bone regeneration.
- the void spaces and/or pores 106 may also accommodate and deliver one or more transcription factors, matrix metalloproteinases, peptides, proteins, bone cells, progenitor cells, blood plasma, bone marrow aspirate, or combinations thereof, to improve or speed bone regeneration, or resorption and replacement of the biomaterial.
- the void spaces and/or pores 106 may further accommodate a carrier material that may be incorporated into the void spaces and/or pores 106 .
- the carrier material may include, for example, a collagen sponge, membrane, or a hydrogel material to deliver the growth factor material such as, for example, the BMP.
- FIG. 5A is an illustration showing a known interbody spinal fusion cage 500 .
- the example spinal fusion cage 500 is implanted in the inter-vertebral space 502 between two adjacent vertebrae 506 and 508 .
- a disc 510 due to degeneration, herniation, etc., is typically removed and replaced by the spinal fusion cage 500 .
- the spinal fusion cage 500 is used to support or restore vertebral height, and, thus, stabilize or retain adjacent vertebrae 506 and 508 in a desired position. Additionally, the spinal fusion cage 500 is to promote fusion between the vertebrae 506 and 508 .
- FIG. 5B is an enlarged illustration of the known spinal fusion cage 500 of FIG. 5A .
- a typical spinal fusion cage 500 includes a body 510 having a dense outer region 512 and a void 514 at its center.
- the dense outer surface 512 may be made of PEEK, titanium, or other material that can be used to support the vertebrae 506 and 508 .
- the spinal fusion cage 500 made of a PEEK, titanium, etc. cannot attach to the bone.
- the center void 514 is typically provided with a packing material (not shown) such as, a natural bone graft, a collagen sponge that retains bone growth factors, or the spinal fusion cage 500 is coated with the bone growth factors or other agents that promote osteoinduction.
- the example porous scaffold 101 having the composite material 100 described herein, and with respect to FIG. 1A can be implemented with the spinal fusion cage 500 of FIGS. 5A and 5B to replace the packing materials, such as natural bone graft.
- the porous scaffold 101 promotes bone ingrowth and the pores 106 may accommodate or deliver for example, a BMP, to further improve rate of growth (fusion rate).
- the calcium phosphate e.g., HA whisker
- FIG. 6 illustrates another example scaffold or matrix 600 implemented with the example composite material 100 described herein.
- the example scaffold 600 may be implemented as an interbody spinal fusion cage.
- the scaffold 600 includes a body 602 having a porous polymer matrix 604 integrally formed or embedded with anisometric calcium phosphate particles 606 .
- the matrix 604 of the example scaffold 600 includes a radiolucent polymer (e.g., PEEK) integrally formed or embedded with anisometric calcium phosphate reinforcements 606 such as, for example, HA whiskers.
- the radiolucent polymer provides improved radiographic analysis of fusion following implantation.
- the example scaffold 600 may also include a BMP such as, for example, rhBMP-2.
- the example scaffold 600 is a biocompatible, microporous polymer scaffold or matrix supplemented with anisometric calcium phosphate reinforcements and BMP.
- the example scaffold 600 may formed so that the pores are functionally graded in any material or implant direction such as, for example, radially, as shown in FIG. 6 , from a highly porous center or central region 608 to relatively dense outer region or surface 610 .
- the change in porosity from one region to another may be distinct or gradual from the central region 608 to the outer region 610 . Further, the graded change may be uniform or variant.
- the dense outer region 610 provides structural integrity along with the advantages of the composite material 100 described herein.
- the porous structure 604 has pore sizes that range between about 100 Mm and about 500 Mm, and preferably, between about 250 Mm and about 500 Mm, and a porosity that ranges between about 1% to about 90%.
- the spinal fusion cage material 600 may include microporosity having pore sizes less than about 10 ⁇ m.
- FIG. 7 illustrates another example scaffold 700 .
- the porous scaffold 700 includes a porous matrix 702 having the composite material 100 described herein.
- the porous scaffold 700 includes a center or central void 704 that may be any shape or size. Additionally or alternatively, the central void 704 may receive a material 706 , a stem, or any other substance or structure, illustratively depicted by dashed lines.
- the central void 704 may receive a stem 706 (e.g., an implant) such as, for example, a titanium stem, a dense composite stem (e.g, a PEEK composite stem), or any other suitable material or structure.
- a stem 706 e.g., an implant
- a dense composite stem e.g, a PEEK composite stem
- the scaffold 700 is formed so that the pores are functionally graded in any material or implant direction, for example, radially as shown in FIG. 7 , from a the high porous outer region or surface 702 to a relatively dense center or central region 708 .
- the change in porosity from one region to another may be distinct or gradual from the central region 708 to the highly porous outer region 702 .
- the graded change may be uniform or variant.
- the example scaffold 700 forms a porous perimeter having a dense core, where the material is continuous from the porous perimeter to the dense core.
- the dense central region 708 provides structural integrity along with the advantages of the composite material 100 described herein.
- the porous matrix 702 and the dense central region 708 may have pore sizes that range between about 100 ⁇ m and about 500 ⁇ m, and preferably, between about 250 ⁇ m and about 500 ⁇ m, and a porosity that ranges between about 1% to about 90%.
- the spinal fusion cage 700 may include a microporosity having pore sizes less than about 10 ⁇ m.
- the composite material 100 and/or the scaffolds 101 , 600 , 700 may also include a roughened surface such as, for example, serrated teeth, that come into direct contact with the adjacent peri-implant tissue to prevent movement relative to the peri-implant tissue after implantation.
- the scaffolds 101 , 600 , 700 may include holes, notches, pins, radiographic markers, or other features that may be gripped or otherwise used for positioning of the scaffolds 101 , 600 , 700 by minimally invasive surgical tools and procedures.
- the example composite material 100 and/or the scaffolds 101 , 600 , 700 may be manufactured by methods common to reinforced thermoplastic and thermosetting polymers, including but not limited to injection molding, reaction injection molding, compression molding, transfer molding, extrusion, blow molding, pultrusion, casting/potting, solvent casting, microsphere sintering, fiber weaving, solvent casting, electrospinning, freeze drying (lyophilization), thermally induced phase separation, gas foaming, and rapid prototyping processes such as solid freeform fabrication, robotic deposition (aka, robocasting), selective laser sintering, fused deposition modeling, three-dimensional printing, laminated object manufacturing, stereolithography, etc., or any other suitable process(es) or combination(s) thereof.
- methods common to reinforced thermoplastic and thermosetting polymers including but not limited to injection molding, reaction injection molding, compression molding, transfer molding, extrusion, blow molding, pultrusion, casting/potting, solvent casting, microsphere sintering, fiber weaving, solvent casting, electrospinning, freeze drying (lyophilization), thermally
- FIG. 8 is a flowchart of an example method 800 that may be used to synthesize the example composite material 100 and/or scaffolds 101 , 600 , 700 described herein. While an example manner of synthesizing the example composite material 100 and/or scaffolds 101 , 600 , 700 has been illustrated in FIG. 8 , one or more of the steps and/or processes illustrated in FIG. 8 may be combined, divided, re-arranged, omitted, eliminated and/or implemented in any other way. Further still, the example method of FIG. 8 may include one or more processes and/or steps in addition to, or instead of, those illustrated in FIG. 8 , and/or may include more than one of any or all of the illustrated processes and/or steps. Further, although the example method is described with reference to the flow chart illustrated in FIG. 8 , persons of ordinary skill in the art will readily appreciate that many other methods of synthesizing the example composite material 100 and/or scaffolds 101 , 600 , 700 may alternatively be used.
- the composite material 100 and/or the scaffolds 101 , 600 , 700 are processed using a powder processing approach in conjunction with compression molding and particle leaching techniques and is particularly suited for achieving a high concentration (e.g., >40 vol %) of well-dispersed (and aligned, if desired) anisometric calcium phosphate reinforcements (e.g., HA whiskers) in a thermoplastic matrix (e.g., PEEK) with minimal degradation of the calcium phosphate size/shape during processing.
- a high concentration e.g., >40 vol %
- anisometric calcium phosphate reinforcements e.g., HA whiskers
- a thermoplastic matrix e.g., PEEK
- the calcium phosphate reinforcement volume fraction, aspect ratio, size and orientation; the polymer; and the size, volume fraction, shape and directionality of the void space and/or porosity may be tailored to vary the mechanical properties of the composite material 100 and/or scaffolds 101 , 600 , 700 .
- a polymer such as, for example, PEEK, and anisometic calcium phosphate particles, such as HA whiskers, are provide in powder form (block 802 ).
- the PEEK polymer powder may have, for example, a mean particle size of about 26 ⁇ m.
- the HA whiskers may be synthesized (block 801 ) using, for example, the chelate decomposition method.
- the PEEK powder and the synthesized HA whiskers are co-dispersed in a fluid (block 804 ) such as, for example ethanol, and mixed (block 804 ) using, for example, ultrasonication under constant stirring—forming a viscous suspension.
- a fluid such as, for example ethanol
- the porosity of the mixture is selectively varied and/or tailored (block 806 ).
- the porosity may be formed and tailored by the addition of a suitable porogen material such as, for example, NaCl, wax, polysaccharides (sugars), cellulose, etc.
- the extent of the porosity can be controlled by varying the amount of porogen used (block 805 ), while the pore size could be tailored by sieving the porogen (block 807 ) to a desired size prior to mixing the porogen with the polymer mixture.
- the porosity and/or the pore size of the polymer matrix may be selectively varied using any other suitable methods and/or process(es) such as, for example, microsphere sintering, fiber weaving, solvent casting, electrospinning, freeze drying (lyophilization), thermally induced phase separation, gas foaming, or rapid prototyping processes such as, for example, solid freeform fabrication, robotic deposition (aka, robocasting), selective laser sintering, fused deposition modeling, three-dimensional printing, laminated object manufacturing, stereolithography, etc., or any other suitable process(es) or combination(s) thereof.
- suitable methods and/or process(es) such as, for example, microsphere sintering, fiber weaving, solvent casting, electrospinning, freeze drying (lyophilization), thermally induced phase separation, gas foaming, or rapid prototyping processes such as, for example, solid freeform fabrication, robotic deposition (aka, robocasting), selective laser sintering, fused deposition modeling, three-dimensional printing, laminated object manufacturing
- the viscous suspension is wet-consolidated (block 808 ) by, for example, vacuum filtration and drying to remove any residual fluid (i.e., ethanol).
- the composite mixture is densified (block 810 ) by, for example, uniaxial compression, to form a composite preform.
- the preform is compression molded (block 812 ) and/or sintered at elevated temperatures (e.g., approximately 20° C. to 400° C.) sufficient to fuse the polymer particles with minimal damage to the calcium phosphate reinforcements.
- elevated temperatures e.g., approximately 20° C. to 400° C.
- the process or composite material may be heated to a desired processing temperature and the implant may be shaped or formed (block 814 ). Densifying and molding the composite material includes aligning the calcium phosphate reinforcement particles (e.g., HA whiskers) morphologically and/or crystallographically within the scaffold struts.
- the scaffold may have any shape and/or size (e.g., any polygonal shape) and can be formed by methods common to reinforced thermoplastic and thermosetting polymers, including but not limited to injection molding, reaction injection molding, compression molding, transfer molding, extrusion, blow molding, pultrusion, casting/potting, solvent casting, and rapid prototyping processes such as, for example, solid freeform fabrication, robotic deposition (aka, robocasting), selective laser sintering, fused deposition modeling, three-dimensional printing, laminated object manufacturing, stereolithography, etc., or any other suitable process(es).
- the composite material 100 and/or the scaffolds 101 , 600 , 700 are formed by the mold walls and/or machining after molding.
- the composite material undergoes a leaching process (block 816 ) to remove, for example, the porogen used during synthesis of the composite material.
- the leaching may occur, for example, via a dissolution method, heating method, and/or any other suitable methods and/or process(es). More specifically, dissolution may include immersing the scaffold in a fluid, such as, for example, deionized water.
- viscous flow of the polymer/reinforcement mixture during molding can be designed to tailor the preferred orientation of the anisometric reinforcements in the implant.
- surface-active agents may be added during the mixing process and/or to the surface of the composite material to enhance interfacial bonding between reinforcement particles and the matrix.
- HA whiskers were synthesized using the chelate decomposition method. The as-synthesized HA whiskers were measured by optical microscopy to have a mean length of 21.6 ⁇ m, width of 2.8 ⁇ m and aspect ratio of 7.6.
- composite scaffolds with 75, 82.5 and 90% porosity were processed with 0-40 vol % HA whisker reinforcement.
- Appropriate amounts of polymer powder and HA whiskers were co-dispersed in ethanol via a sonic dismembrator and mechanical stirring at 1200 rpm.
- the appropriate amount of the NaCl i.e, porogen
- the total scaffold volume consisted of the material volume plus the pore volume.
- the reinforcement level was calculated based the desired material volume, while the porosity level was calculated based on the total scaffold volume.
- the viscous suspension was wet-consolidated using vacuum filtration.
- the powder mixture was dried overnight in a forced convection oven at 90° C. and densified at 125 MPa in a cylindrical pellet die using a hydraulic platen press.
- the die and densified powder mixture was heated in a vacuum oven to the desired processing temperature and transferred to a hydraulic platen press for compression molding. Scaffolds with 82.5 and 90% porosity were molded at 350° C., while scaffolds with 75% porosity were molded at 350, 365 and 375° C.
- a pressure of 250 MPa was applied to the die as the polymer solidified.
- the sintered composite pellet was ejected from the die and placed approximately 300 mL deionized water for at least 72 h to dissolve the NaCl crystals. The deionized water was changed daily.
- the as-molded composite scaffolds had a diameter of 1 cm and were machined to a height of 1 cm.
- the table below provides mechanical properties of the example PEKK scaffold reinforced with HA whiskers that was processed using a compression molding/particle leaching method such as, for example, the method 800 of FIG. 8 as implemented in the description above.
- the mechanical properties of HA whisker reinforced PEKK were evaluated in uniaxial compression.
- Tensile properties of the HA whisker reinforced PEKK scaffolds were evaluated prior to scaffold fabrication.
- Scaffolds with 40 vol % HA whisker reinforcement and 75%, 82% and 90% porosity exhibited yield strengths of 0.52 MPa, 0.13 MPa and 0.04 MPa, respectively.
- the HA content also affected the modulus and failure strain of the scaffolds.
- a scaffold having 75% porosity and 20 vol % reinforcement HA whisker exhibited modulus of 106.3 MPa, compared to a modulus of 69.5 MPa for scaffolds with 0 vol % HA whisker reinforcement.
- the example methods and apparatus described herein offer synthetic porous composite material that may be used for synthetic bone substitutes for implant fixation, fraction fixation, synthetic bone graft substitutes, interbody spinal fusion, tissue engineering scaffolds, or other applications.
- Many aspects of the of the porous composite material may be tailored to provide specific mechanical, biological, and surgical functions, such as, the polymer composition and molecular orientation, porosity and pore size of the porous matrix, or the HA reinforcement content, morphology, preferred orientation, and size.
Abstract
Description
- This application claims the benefit of U.S. Provisional Patent Application Ser. No. 60/904,098, filed on Feb. 28, 2007, entitled “Reinforced Porous Polymer Scaffolds” and U.S. Provisional Patent Application Ser. No. 60/939,256, filed on May 21, 2007, entitled “Interbody Spinal Fusion Cages Containing Anisometric Calcium Phosphate Reinforcements and Related Methods,” both of which are incorporated herein in their entireties.
- The present disclosure relates generally to composite biomaterials and more particularly to porous composite biomaterials and related methods.
- Natural bone grafts such as autogenous bone grafts (autografts) are commonly used in procedures for repairing or replacing bone defects because they provide good structural support and osteoinductivity. Natural bone grafts involve removing or harvesting tissue from another part of a host's body (e.g., typically from the iliac crest, hip, ribs, etc.) and implanting the harvested tissue in the defect site. Not only do these grafts require an added surgical procedure needed to harvest the bone tissue, these grafts have limitations, including for example, transplant site morbidity. One alternative to autografts is allografts, which involve removing and transplanting tissue from another human (e.g., from bone banks that harvest bone tissue from cadavers) to the defect site. However, allografts are known to induce infection and immunotoxicity, suffer from limited supply and variability, and have a lessened effectiveness because the cells and proteins that promote bone growth are lost during the harvesting process (e.g., during cleansing and disinfecting process). Demineralized bone matrix (DBM) is typically used to induce bone growth at defect sites, but DBM lacks the mechanical properties (e.g., stiffness, strength, toughness, etc.) necessary to be considered a viable option for load-bearing applications.
- Synthetic bone substitute materials have been researched in the treatment of diseased bone (e.g., osteoporosis), injured bone (e.g., fractures), or other bone defects in lieu of natural bone grafts. Synthetic bone substitutes are viable alternatives to the more traditional methods described above. However, synthetic substitute materials used to repair diseased bones and joints should function or perform biologically and mechanically (i.e., as the structural support role of the bone itself) by, for example, mimicking the density and overall physical structure of natural bone to provide a framework for ingrowth of new tissue. One type or application of a synthetic bone substitute is a scaffold, which provides support for bone-producing cells. Scaffolds may be biodegradable, which degrade in vivo, or they may be non-biodegradable to provide permanent implant fixation (e.g., spinal fusion cages). In addition, scaffolds are typically biocompatible, and some may be bioactive, bioresorbable, osteoconductive, and/or osteoinductive. The shapability, deliverability, cost, and ability to match the mechanical properties of the surrounding host tissue are other factors that vary among different types of scaffolds and other bone substitutes.
- Problems may arise when there is a mechanical mismatch between the bone substitute and the surrounding tissue. For example, metallic implants and dense ceramics have mechanical properties that are typically an order of magnitude greater than the bone tissue. As a result, a stiff metal bone substitute implant acts to “shield” the adjacent bone tissue from mechanical stresses, resulting in a weakened bone at the bone-implant interface. Furthermore, efforts to utilize porous ceramics or polymer bone cement in place of stiffer materials have been limited. For example, ceramics possess low fracture toughness, thereby making the orthopedic implant brittle (i.e., susceptible to fracture). Polymers are limited by higher compliance and lower strength, thereby limiting their ability to support physiological load levels. Additionally, conventional orthopedic implant biomaterials are not osteoconductive and bioactive, resulting in a lack of bonding between the implant and the peri-implant tissue.
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FIG. 1A is a perspective view of an example porous composite material described herein. -
FIG. 1B is a cross-sectional view of a portion of the example porous composite material ofFIG. 1A . -
FIG. 2A-2C are scanning electron micrographs of a portion of the example porous composite material shown in increasing magnification. -
FIG. 3 is graphical representation of the elastic modulus of example apatite reinforced polymer composites versus the reinforcement volume fraction. -
FIG. 4 shows scanning electron micrograph of a portion of the surface of an example composite material reinforced with calcium phosphate whiskers embedded within and exposed on the surface, and schematically showing the orientation of the whiskers relative to the loading direction of the material or scaffold strut. -
FIG. 5A is a schematic illustration of a known spinal fusion cage inserted between spinal vertebrae. -
FIG. 5B illustrates the example known spinal fusion cage ofFIG. 5A . -
FIG. 6 illustrates another example scaffold described herein. -
FIG. 7 illustrates yet another example scaffold described herein. -
FIG. 8 is a flow diagram illustrating an example process of creating an example composite material apparatus described herein. - In general, the example methods, apparatus, and materials described herein provide a biocompatible, bioactive synthetic porous composite for use as synthetic bone substitute materials. The synthetic composite may provide a synthetic porous scaffold for use an orthopedic implant and/or be injectable via percutaneous or surgical injection to cure in vivo. Because the example composite material is used to form a scaffold or matrix that is used in an implantable device, the descriptions of one or more of these structures may also describe one or more of the other structures. The synthetic porous composites are tailored to mimic biological and mechanical properties of bone tissue for implant fixation, synthetic bone graft substitutes, tissue engineering scaffolds, interbody spinal fusion, or other orthopedic applications. An example porous composite material described herein reduces subsidence and/or bone resorption resulting from mechanical mismatch problems between a synthetic scaffold of an implant device and the peri-implant tissue. Additionally, porosity and/or the pore sizes of the example synthetic composite are tailorable to specific applications to effectively promote the vascularization and growth of bone in the pores and/or void spaces of the example scaffolds, thereby improving bonding between the scaffolds and peri-implant tissue.
- The example composite material or scaffolds are synthesized or made through a process that enables reinforcement particles to be integrally formed with or embedded within polymer matrices. In this manner, the polymer matrices embedded with the reinforcement material provide improved material properties (e.g., stiffness, fatigue strength, and toughness). The reinforcement particles are also exposed on a surface of the matrices, which promotes bioactivity and/or bioresorption. Additionally, the process provides flexibility to tailor the level of reinforcement particles and porosity for a desired application. For example, a porogen material may be used to vary the porosity, while the pore size is tailored by, for example, sieving the porogen to a desired size.
- By varying the volume of the reinforcement particles and the porosity of the example scaffold, the mechanical properties (e.g., stiffness, strength, toughness, etc.) of the example scaffold of the implant device may be tailored to match those of the adjacent peri-implant bone tissue to reduce mechanical mismatch problems. Reducing mechanical mismatch provides a decreased risk of subsidence, stress shielding, bone resorption, and/or subsequent failure of adjacent peri-implant bone tissue. Additionally, the example scaffold of the implant device may include a significantly high porosity to promote bone ingrowth, while exhibiting significantly higher effective mechanical properties such as, for example, the mechanical properties of trabecular bone.
- In particular, the example composite material includes a continuous porous biocompatible matrix having a thermoplastic polymer matrix reinforced with anisometric calcium phosphate particles. More specifically, in one example, a composite material includes a polyetheretherketone (PEEK) or a polyetherketoneketone (PEKK) matrix reinforced with various volume fractions of hydroxyapatite (HA) whiskers (e.g., 20 or 40 volume percent), wherein the matrix is approximately between 70% and 90% porous. In another example, the porous matrix includes a biocompatible, microporous polymer cage reinforced with anisometric calcium phosphate particles and bone morphogenic protein (BMP) such as, for example, rhBMP-2, which can be dispersed or accommodated by the void spaces and/or pores of the example porous scaffold and/or exposed on the surface of the example porous scaffold. Additionally, the BMP binds to the calcium phosphate further localizing the BMP to the surface of the scaffold or matrix.
- The example composite materials described herein may be used for applications such as, for example, synthetic bone graft substitutes, bone ingrowth surfaces applied to existing implants, tissue engineering scaffolds, interbody spinal fusion cages, etc. In each of the applications, carrier materials (e.g., collagen, hydrogels, etc.) containing growth factors, such as BMP, may be incorporated into the pore space of the scaffold of the implant device to further enhance osteoinduction and/or osteoconduction to promote osteointegration.
- Human bone tissues exhibit substantial variation in mechanical properties depending on the tissue density and microstructure. The properties are highly dependent on anatomic location and apparent density of the measured specimen. For example, a femur includes a cortical bone that has a relative porosity on the order of about 5-15%, and a trabecular bone that has a porosity on the order of about 75-95%. Due to the highly significant porosity differences, the trabecular bone exhibits significantly lower effective mechanical properties compared to the cortical bone. Therefore, depending on the application, synthetic composite materials for use as scaffolds and/or spinal fusion cages or other implant devices should possess the mechanical properties exhibited by the cortical bone or the trabecular bone, but must also have effective porosity to promote bone growth.
- To avoid the mechanical mismatch problems, such as stress shielding, the example scaffold of the implant device described herein may be tailored to substantially match or mimic the mechanical properties (e.g., stiffness, strength, toughness, etc.) of the adjacent and/or substituted bone tissue. Several factors may be varied during the synthesis of the composite material and scaffold of the implant device to tailor the mechanical properties including the calcium phosphate reinforcement volume fraction, aspect ratio, size and orientation; the polymer; and the size, volume fraction, shape and directionality of the void space and/or porosity. Tailoring the mechanical properties of the scaffold reduces the likelihood of mechanical mismatch leading to a decreased risk of subsidence, stress shielding, bone resorption and/or subsequent failure of adjacent vertebrae.
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FIG. 1A illustrates the example synthetic porouscomposite material 100 described herein.FIG. 1B is a cross-sectional view of a portion of the example porouscomposite material 100 ofFIG. 1A . The example syntheticcomposite material 100 provides a syntheticporous scaffold 101 for use or in as an orthopedic implant. - The example synthetic porous
composite material 100 includes a porous thermoplastic polymer (e.g., a PEEK polymer)matrix 102 having anisometric calciumphosphate reinforcement particles 104 integrally formed or embedded with thematrix 102 and/or exposed on a surface of the matrix. In this manner, thepolymer matrix 102 embedded with thereinforcement particles 104 provides high material strength, and thereinforcement particles 104 exposed on the surface of thematrix 102 promote bioactivity and/or bioresorption. Theporous polymer matrix 102 includes a substantially continuous porosity and a plurality ofpores 106 to enable bone ingrowth into theporous matrix 102. In addition, thematrix 102 is substantially continuously interconnected via a plurality ofstruts 108. Furthermore, at least one of the plurality ofstruts 108 may be a load-bearing strut. -
FIGS. 2A-2C are scanning electron micrographs showing increasing magnification of a portion of anexample scaffold 200 withstruts 202. Theexample scaffold 200 is a PEEK scaffold reinforced with 40% by volume HA whiskers 204.FIG. 2A illustrates the architecture ormatrix 206 of thescaffold 200 andFIG. 2B illustrates an enlarged portion of thestruts 202. In the illustrated example, theHA whiskers 204 are integrally formed and/or embedded within thematrix 206 of thescaffold 200 for reinforcement. The HA whiskers 204 are also exposed on asurface 208 of the matrix of thescaffold 200 for bioactivity and/or bioresorption, as noted above. As shown inFIG. 2C , theHA whiskers 204 are aligned in a sheet texture and are exposed on thesurface 208 of thestruts 202. - The thermoplastic polymer of the example scaffolds described herein may be a biodegradable polymer for synthetic bone graft substitute applications, or nonbiodegradable for implant fixation applications. The thermoplastic polymer includes a continuous matrix of a composite material and is biocompatible and/or bioresorbable as described above. Additionally or alternatively, the polymer may be a radiolucent polymer, bioresorbable (i.e., a material capable of being resorbed by a patient under normal physiological conditions) and/or non-bioresorbable, as desired. Further, the thermoplastic polymer matrix may include a polymer suitable for injection via percutaneous or surgical injection so that the
composite material 100 cures in vivo. - Suitable non-resorbable polymers include, without limitation, polyaryletherketone (PAEK), polyetheretherketone (PEEK), polyetherketonekteone (PEKK), polyetherketone (PEK), polyethylene, high density polyethylene (HDPE), ultra high molecular weight polyethylene (UHMWPE), low density polyethylene (LDPE), polyethylene oxide (PEO), polyurethane, polypropylene, polypropylene oxide (PPO), polysulfone, polypropylene, copolymers thereof, and blends thereof. Suitable bioresorbable polymers include, without limitation, poly(DL-lactide) (PDLA), poly(L-lactide) (PLLA), poly(glycolide) (PGA), poly(ε-caprolactone) (PCL), poly(dioxanone) (PDO), poly(glyconate), poly(hydroxybutyrate) (PHB), poly(hydroxyvalerate (PHV), poly(orthoesters), poly(carboxylates), poly(propylene fumarate), poly(phosphates), poly(carbonates), poly(anhydrides), poly(iminocarbonates), poly(phosphazenes), copolymers thereof, and blends thereof. Suitable polymers that are injectible via percutaneous or surgical injection that cure in vivo include, without limitation, polymethylmethacrylate (PMMA), and other polyacrylics from monomers such as bisphenol a hydroxypropylmethacrylate (bis-GMA) and/or tri(ethylene glycol) dimethacrylate (TEG-DMA).
- Although synthetic substitute composite materials made of polymers satisfy the functional criteria of an implantable device because they are, for example, formable and inexpensive, polymers alone lack biological efficacy to promote bone growth and/or may lack requisite mechanical properties to support load levels. To increase the mechanical properties of the polymers, the polymers are reinforced with calcium phosphates. The aspect ratio, size, volume fraction and degree of preferred orientation of the calcium phosphate particles 104 (e.g., HA whisker particles) may be tailored for the desired material properties and implant performance. For example, consider the information presented in
FIG. 3 , which is a graphical illustration of the elastic modulus of HA whisker and powder reinforced polymer composite materials versus the volume fraction percentage of the apatite calcium phosphates that is mixed with the polymer matrix. The shaded areas ofFIG. 3 show approximate regions for the given mechanical property of the human cortical bone tissue. As depicted in the graph, the elastic modulus of the composite materials increases with increasing HA content. In addition, increasing the level of HA reinforcement in polymer composites increases cellular activity during osteointegration. - The calcium
phosphate reinforcement particles 104 may be in the form of single crystals or dense polycrystals, but are at least in some portion anisometric. “Anisometric” refers to any particle morphology (shape) that is not equiaxed (e.g., spherical), such as whiskers, plates, fibers, etc. Anisometric particles are usually characterized by an aspect ratio. For example, HA single crystals are characterized by the ratio of dimensions in the c- and a-axes of the hexagonal crystal structure. Thus, the anisometric particles in the present disclosure have an aspect ratio greater than 1. In one example, the mean aspect ratio of the reinforcement particles is from about 1 to about 100. By further example, the reinforcement particles can be provided in an amount of from about 1% by volume of the composite biomaterial to about 60% by volume, and for example, from about 20% by volume of the composite to about 50% by volume. - Due to their morphology, the calcium
phosphate reinforcements particles 104 may be oriented in bulk or near the surface of thepolymer matrix 102 to provide directional properties, if desired. For example, if thereinforcement particles 104 are predominately aligned within thematrix 102 the morphological alignment of theparticles 104 provides anisotropy for theoverall composite 100, which can be tailored to be similar to the anisotropic mechanical properties of bone tissues. For example,FIG. 4 shows a micrograph of anisometriccalcium phosphate reinforcement 400 on the surface of a densecomposite polymer matrix 402. Also shown inFIG. 4 is a schematic illustration of a portion ofmatrix 402 and illustratively showing the orientation of thereinforcement particles 400 relative to the loading direction of the material and/or a scaffold strut, which is, for example, at an angle θ. - Furthermore, there are no limits on the size or amount of the
calcium phosphate particles 104 inmatrix 102, provided that thecalcium phosphate particles 104 are dispersed within and/or exposed at the surface of thepolymer matrix 102. For example, thereinforcement particles 104 may have a maximum dimension from about 20 nm to about 2 mm, and for example, between 20 nm to about 100 μm. While both nano- and micro-scale calcium phosphate particles improve the mechanical properties of the example syntheticcomposite material 100 described herein, nano-scale calcium phosphate particles are particularly effective for enhancing bioresorbability and cell attachment, and micro-scale particles are particularly effective for obtaining a uniform dispersion within thematrix 102. - Suitable calcium phosphates may include, without limitation, calcium HA, HA whiskers, HA, carbonated calcium HA, beta-tricalcium phosphate (beta-TCP), alpha-tricalcium phosphate (alpha-TCP), amorphous calcium phosphate (ACP), octacalcium phosphate (OCP), tetracalcium phosphate, biphasic calcium phosphate (BCP), anhydrous dicalcium phosphate (DCPA), dicalcium phosphate dihydrate (DCPD), anhydrous monocalcium phosphate (MCPA), monocalcium phosphate monohydrate (MCPM), and combinations thereof.
- As described above, a synthetic
composite material 100 not only bears physiological levels of load, but also promotes oseteointegration—the direct structural and functional connection between the living bone and the surface of the load-bearing implant. The bioactive calcium phosphate particles 104 (e.g., HA whiskers) exposed on the surface of the exampleporous matrix 102 promote a stable bone-implant interface. Osteointegration also requires the vascularization and growth of bone into an implant via interconnected and/or continuous porosity. - Thus, the size, volume fraction, shape, and directionality of the void spaces and/or
pores 106 may be tailored to optimize osteoconduction and implant mechanical properties. Thepores 106 may be any size or shape, while maintaining a continuous network to promote a fusion through the formation of new bone tissue in the void spaces and/or pores 106. For example, thepores 106 may be present throughout thematrix 102 as illustrated inFIG. 1A . Also, thepores 106 may be functionally graded in any material or implant direction, for example, radially, as shown inFIGS. 6 and 7 , from a highly porous region to a relatively dense region, or may include a void space. The change in porosity from one region to another may be very distinct, for example as shown inFIGS. 6 and 7 , or gradual. Furthermore, the graded change may be uniform or variant. In addition, instead of a graded change there may be a combination of materials having two or more densities of pores. The central void may be any shape or size, and may receive (e.g., be filled) a material, a structure, or the composite material 100 (i.e., the composite material graded from the porous outer surface to a dense center), thereby forming a porous outer perimeter and a dense central region. Examples are further described in connection withFIGS. 6 and 7 below. - As discussed in greater detail below, the porosity and/or pore
sizes 106 may be selectively formed by the inclusion of, for example, a porogen material during synthesis of thecomposite material 100. Pores spaces may range from about 100 Mm to about 500 Mm, and, for example, from about 250 Mm to about 500 Mm. The examplecomposite biomaterial 100 may additionally contain some fraction of microporosity within scaffold struts that is less than about 10 Mm in size. The total amount of porosity within porous regions may range from about 1% to about 90% by volume, and, for example, between about 70% and 90% by volume. However, the porosity may also be tailored via other processes such as, for example, microsphere sintering, fiber weaving, solvent casting, electrospinning, freeze drying (lyophilization), thermally induced phase separation, gas foaming, and rapid prototyping processes such as, for example, solid freeform fabrication, robotic deposition (aka, robocasting), selective laser sintering, fused deposition modeling, three-dimensional printing, laminated object manufacturing, stereolithography, etc., or any other suitable process(es) or combination(s) thereof. - Additionally, the example
composite material 100 may optionally include additives, if desired. For example, thecomposite material 100 may include one or more surface-active agents to enhance interfacial bonding between thereinforcement particles 104 and thepolymer matrix 102. The void spaces and/orpores 106 may accommodate and deliver one or more growth factors such as, for example, BMP, to enhance osteoinductivity and/or bone regeneration. Furthermore, the void spaces and/orpores 106 may also accommodate and deliver one or more transcription factors, matrix metalloproteinases, peptides, proteins, bone cells, progenitor cells, blood plasma, bone marrow aspirate, or combinations thereof, to improve or speed bone regeneration, or resorption and replacement of the biomaterial. In some examples, the void spaces and/orpores 106 may further accommodate a carrier material that may be incorporated into the void spaces and/or pores 106. The carrier material may include, for example, a collagen sponge, membrane, or a hydrogel material to deliver the growth factor material such as, for example, the BMP. Thecalcium phosphate reinforcements 104 exposed on the surface of theporous matrix 102, along with the porosity, improves the retention of the BMP within thematrix 102 and at the peri-implant interface. -
FIG. 5A is an illustration showing a known interbodyspinal fusion cage 500. The examplespinal fusion cage 500 is implanted in theinter-vertebral space 502 between twoadjacent vertebrae disc 510, due to degeneration, herniation, etc., is typically removed and replaced by thespinal fusion cage 500. Thespinal fusion cage 500 is used to support or restore vertebral height, and, thus, stabilize or retainadjacent vertebrae spinal fusion cage 500 is to promote fusion between thevertebrae -
FIG. 5B is an enlarged illustration of the knownspinal fusion cage 500 ofFIG. 5A . A typicalspinal fusion cage 500 includes abody 510 having a denseouter region 512 and a void 514 at its center. The denseouter surface 512 may be made of PEEK, titanium, or other material that can be used to support thevertebrae spinal fusion cage 500 made of a PEEK, titanium, etc., cannot attach to the bone. Thus, to promote bone ingrowth, thecenter void 514 is typically provided with a packing material (not shown) such as, a natural bone graft, a collagen sponge that retains bone growth factors, or thespinal fusion cage 500 is coated with the bone growth factors or other agents that promote osteoinduction. - The example
porous scaffold 101 having thecomposite material 100 described herein, and with respect toFIG. 1A , can be implemented with thespinal fusion cage 500 ofFIGS. 5A and 5B to replace the packing materials, such as natural bone graft. As noted above, theporous scaffold 101 promotes bone ingrowth and thepores 106 may accommodate or deliver for example, a BMP, to further improve rate of growth (fusion rate). Furthermore, the calcium phosphate (e.g., HA whisker) binds to thebody 510 and localizes the BMP within thecentral void 514, which further promotes osteointegration. -
FIG. 6 illustrates another example scaffold ormatrix 600 implemented with the examplecomposite material 100 described herein. Theexample scaffold 600 may be implemented as an interbody spinal fusion cage. Thescaffold 600 includes abody 602 having aporous polymer matrix 604 integrally formed or embedded with anisometriccalcium phosphate particles 606. Furthermore, thematrix 604 of theexample scaffold 600 includes a radiolucent polymer (e.g., PEEK) integrally formed or embedded with anisometriccalcium phosphate reinforcements 606 such as, for example, HA whiskers. The radiolucent polymer provides improved radiographic analysis of fusion following implantation. Theexample scaffold 600 may also include a BMP such as, for example, rhBMP-2. In another example, theexample scaffold 600 is a biocompatible, microporous polymer scaffold or matrix supplemented with anisometric calcium phosphate reinforcements and BMP. - Additionally, the
example scaffold 600 may formed so that the pores are functionally graded in any material or implant direction such as, for example, radially, as shown inFIG. 6 , from a highly porous center orcentral region 608 to relatively dense outer region orsurface 610. The change in porosity from one region to another may be distinct or gradual from thecentral region 608 to theouter region 610. Further, the graded change may be uniform or variant. The denseouter region 610 provides structural integrity along with the advantages of thecomposite material 100 described herein. In the illustrated example, theporous structure 604 has pore sizes that range between about 100 Mm and about 500 Mm, and preferably, between about 250 Mm and about 500 Mm, and a porosity that ranges between about 1% to about 90%. Furthermore, the spinalfusion cage material 600 may include microporosity having pore sizes less than about 10 μm. -
FIG. 7 illustrates anotherexample scaffold 700. Theporous scaffold 700 includes aporous matrix 702 having thecomposite material 100 described herein. Theporous scaffold 700 includes a center orcentral void 704 that may be any shape or size. Additionally or alternatively, thecentral void 704 may receive amaterial 706, a stem, or any other substance or structure, illustratively depicted by dashed lines. For example, thecentral void 704 may receive a stem 706 (e.g., an implant) such as, for example, a titanium stem, a dense composite stem (e.g, a PEEK composite stem), or any other suitable material or structure. - Additionally, in other examples, the
scaffold 700 is formed so that the pores are functionally graded in any material or implant direction, for example, radially as shown inFIG. 7 , from a the high porous outer region orsurface 702 to a relatively dense center orcentral region 708. The change in porosity from one region to another may be distinct or gradual from thecentral region 708 to the highly porousouter region 702. Further, the graded change may be uniform or variant. In this manner, theexample scaffold 700 forms a porous perimeter having a dense core, where the material is continuous from the porous perimeter to the dense core. The densecentral region 708 provides structural integrity along with the advantages of thecomposite material 100 described herein. In the illustrated example, theporous matrix 702 and the densecentral region 708 may have pore sizes that range between about 100 μm and about 500 μm, and preferably, between about 250 μm and about 500 μm, and a porosity that ranges between about 1% to about 90%. Furthermore, thespinal fusion cage 700 may include a microporosity having pore sizes less than about 10 μm. - In other examples, the
composite material 100 and/or thescaffolds scaffolds scaffolds - The example
composite material 100 and/or thescaffolds -
FIG. 8 is a flowchart of anexample method 800 that may be used to synthesize the examplecomposite material 100 and/orscaffolds composite material 100 and/orscaffolds FIG. 8 , one or more of the steps and/or processes illustrated inFIG. 8 may be combined, divided, re-arranged, omitted, eliminated and/or implemented in any other way. Further still, the example method ofFIG. 8 may include one or more processes and/or steps in addition to, or instead of, those illustrated inFIG. 8 , and/or may include more than one of any or all of the illustrated processes and/or steps. Further, although the example method is described with reference to the flow chart illustrated inFIG. 8 , persons of ordinary skill in the art will readily appreciate that many other methods of synthesizing the examplecomposite material 100 and/orscaffolds - The
composite material 100 and/or thescaffolds composite material 100 and/orscaffolds - A polymer such as, for example, PEEK, and anisometic calcium phosphate particles, such as HA whiskers, are provide in powder form (block 802). The PEEK polymer powder may have, for example, a mean particle size of about 26 μm. The HA whiskers may be synthesized (block 801) using, for example, the chelate decomposition method.
- The PEEK powder and the synthesized HA whiskers are co-dispersed in a fluid (block 804) such as, for example ethanol, and mixed (block 804) using, for example, ultrasonication under constant stirring—forming a viscous suspension.
- After the polymer powder and the HA whiskers are mixed, the porosity of the mixture is selectively varied and/or tailored (block 806). In one example, the porosity may be formed and tailored by the addition of a suitable porogen material such as, for example, NaCl, wax, polysaccharides (sugars), cellulose, etc. The extent of the porosity can be controlled by varying the amount of porogen used (block 805), while the pore size could be tailored by sieving the porogen (block 807) to a desired size prior to mixing the porogen with the polymer mixture. In another examples, the porosity and/or the pore size of the polymer matrix may be selectively varied using any other suitable methods and/or process(es) such as, for example, microsphere sintering, fiber weaving, solvent casting, electrospinning, freeze drying (lyophilization), thermally induced phase separation, gas foaming, or rapid prototyping processes such as, for example, solid freeform fabrication, robotic deposition (aka, robocasting), selective laser sintering, fused deposition modeling, three-dimensional printing, laminated object manufacturing, stereolithography, etc., or any other suitable process(es) or combination(s) thereof.
- The viscous suspension is wet-consolidated (block 808) by, for example, vacuum filtration and drying to remove any residual fluid (i.e., ethanol). The composite mixture is densified (block 810) by, for example, uniaxial compression, to form a composite preform.
- Following the initial densification, the preform is compression molded (block 812) and/or sintered at elevated temperatures (e.g., approximately 20° C. to 400° C.) sufficient to fuse the polymer particles with minimal damage to the calcium phosphate reinforcements. The process or composite material may be heated to a desired processing temperature and the implant may be shaped or formed (block 814). Densifying and molding the composite material includes aligning the calcium phosphate reinforcement particles (e.g., HA whiskers) morphologically and/or crystallographically within the scaffold struts.
- The scaffold may have any shape and/or size (e.g., any polygonal shape) and can be formed by methods common to reinforced thermoplastic and thermosetting polymers, including but not limited to injection molding, reaction injection molding, compression molding, transfer molding, extrusion, blow molding, pultrusion, casting/potting, solvent casting, and rapid prototyping processes such as, for example, solid freeform fabrication, robotic deposition (aka, robocasting), selective laser sintering, fused deposition modeling, three-dimensional printing, laminated object manufacturing, stereolithography, etc., or any other suitable process(es). The
composite material 100 and/or thescaffolds - The composite material undergoes a leaching process (block 816) to remove, for example, the porogen used during synthesis of the composite material. The leaching may occur, for example, via a dissolution method, heating method, and/or any other suitable methods and/or process(es). More specifically, dissolution may include immersing the scaffold in a fluid, such as, for example, deionized water.
- Furthermore, viscous flow of the polymer/reinforcement mixture during molding can be designed to tailor the preferred orientation of the anisometric reinforcements in the implant. Additionally surface-active agents may be added during the mixing process and/or to the surface of the composite material to enhance interfacial bonding between reinforcement particles and the matrix.
- The following example is provided to further illustrate the example apparatus and methods described herein and, of course, should not be construed as in any way limiting in scope. It is to be understood by one of ordinary skill in the art that the following examples are neither comprehensive nor exhaustive of the many types of methods and apparatus which may be prepared in accordance with the present disclosure.
- In the example, commercially available PEKK and sodium chloride (NaCl) powders with mean particle sizes of 70 and 250 μm, respectively, were used as-received. HA whiskers were synthesized using the chelate decomposition method. The as-synthesized HA whiskers were measured by optical microscopy to have a mean length of 21.6 μm, width of 2.8 μm and aspect ratio of 7.6.
- In the example, composite scaffolds with 75, 82.5 and 90% porosity were processed with 0-40 vol % HA whisker reinforcement. Appropriate amounts of polymer powder and HA whiskers were co-dispersed in ethanol via a sonic dismembrator and mechanical stirring at 1200 rpm. Following dispersion, the appropriate amount of the NaCl (i.e, porogen) was added to the suspension and mixed by hand using a Teflon coated spatula. The total scaffold volume consisted of the material volume plus the pore volume. Thus, the reinforcement level was calculated based the desired material volume, while the porosity level was calculated based on the total scaffold volume. After mixing, the viscous suspension was wet-consolidated using vacuum filtration. The powder mixture was dried overnight in a forced convection oven at 90° C. and densified at 125 MPa in a cylindrical pellet die using a hydraulic platen press. The die and densified powder mixture was heated in a vacuum oven to the desired processing temperature and transferred to a hydraulic platen press for compression molding. Scaffolds with 82.5 and 90% porosity were molded at 350° C., while scaffolds with 75% porosity were molded at 350, 365 and 375° C. A pressure of 250 MPa was applied to the die as the polymer solidified. After cooling to room temperature, the sintered composite pellet was ejected from the die and placed approximately 300 mL deionized water for at least 72 h to dissolve the NaCl crystals. The deionized water was changed daily. The as-molded composite scaffolds had a diameter of 1 cm and were machined to a height of 1 cm.
- In the example, unconfined compression tests were performed to investigate the mechanical properties of the composite scaffolds. Specimens were tested on an electromagnetic test instrument in phosphate buffered saline (PBS) at 37° C. using a crosshead speed of 1 mm/min. Force-displacement data was used to calculate the elastic modulus, compressive yield stress (CYS), and failure strain of the composite scaffolds. One-way analysis of variance (ANOVA) was used to compare mechanical properties between experimental groups. The compressive properties of HA whisker reinforced PEKK scaffolds were tabulated in table 1.
- The table below provides mechanical properties of the example PEKK scaffold reinforced with HA whiskers that was processed using a compression molding/particle leaching method such as, for example, the
method 800 ofFIG. 8 as implemented in the description above. The mechanical properties of HA whisker reinforced PEKK were evaluated in uniaxial compression. Tensile properties of the HA whisker reinforced PEKK scaffolds were evaluated prior to scaffold fabrication. -
HA Molding Elastic Yield Porosity Content Temperature Modulus Strain (%) (Vol %) (° C.) (MPa) CYS (MPa) (%) 75 0 350 69.5 (12.2) 1.25 (0.16) 5.7 (0.4) 75 0 365 100.7 (10.7) 2.04 (0.26) 4.4 (1.2) 75 0 375 95.6 (10.5) 2.55 (0.34) 4.4 (1.1) 75 20 350 106.3 (15.0) 1.28 (0.13) 3.7 (1.1) 75 20 365 115.4 (13.4) 1.77 (0.30) 2.9 (0.6) 75 20 375 141.1 (39.2) 2.28 (0.35) 2.9 (0.7) 75 40 350 54.0 (18.3) 0.52 (0.17) 2.2 (0.3) 75 40 365 84.3 (41.5) 1.15 (0.38) 2.7 (0.5) 75 40 375 120.2 (29.8) 1.65 (0.34) 2.3 (1.9) 82 40 350 15.7 (6.7) 0.13 (0.03) 2.6 (1.9) 90 0 350 0.75 (0.18) 0.15 (0.04) 30 (0.0) 90 40 350 0.23 (0.13) 0.04 (0.01) 30 (0.0) - As shown in the table, for a given reinforcement level, the compressive modulus decreased with increased porosity, and the yield strength decreased with increased porosity. Scaffolds with 0% vol % HA whisker reinforcement and 75% and 90% porosity exhibited moduli of 69.5 and 0.75 MPa, while scaffolds with 40 vol % HA whisker reinforcement and 75%, 82% and 90% porosity exhibited moduli of 54.0, 15.7 and 0.23 MPa, respectively. Scaffolds with 0 vol % HA whisker reinforcement and 75% and 90% porosity exhibited yield strengths of 1.25 MPa and 0.15 MPa, respectively. Scaffolds with 40 vol % HA whisker reinforcement and 75%, 82% and 90% porosity exhibited yield strengths of 0.52 MPa, 0.13 MPa and 0.04 MPa, respectively. The HA content also affected the modulus and failure strain of the scaffolds. A scaffold having 75% porosity and 20 vol % reinforcement HA whisker exhibited modulus of 106.3 MPa, compared to a modulus of 69.5 MPa for scaffolds with 0 vol % HA whisker reinforcement.
- The example methods and apparatus described herein offer synthetic porous composite material that may be used for synthetic bone substitutes for implant fixation, fraction fixation, synthetic bone graft substitutes, interbody spinal fusion, tissue engineering scaffolds, or other applications. Many aspects of the of the porous composite material may be tailored to provide specific mechanical, biological, and surgical functions, such as, the polymer composition and molecular orientation, porosity and pore size of the porous matrix, or the HA reinforcement content, morphology, preferred orientation, and size.
- Although the teachings of the present disclosure have been illustrated in connection with certain examples, there is no intent to limit the present disclosure to such examples. On the contrary, the intention of this application is to cover all modifications and examples fairly falling within the scope of the appended claims either literally or under the doctrine of equivalents.
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Cited By (104)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2010091223A1 (en) * | 2009-02-06 | 2010-08-12 | David Cheung | Biphasic collagen membrane or capsule for guided tissue regeneration |
US20100256758A1 (en) * | 2009-04-02 | 2010-10-07 | Synvasive Technology, Inc. | Monolithic orthopedic implant with an articular finished surface |
US20100255053A1 (en) * | 2009-04-03 | 2010-10-07 | Warsaw Orthopedic, Inc. | Medical implant with bioactive material and method of making the medical implant |
US20100262224A1 (en) * | 2009-04-13 | 2010-10-14 | Kleiner Lothar W | Stent Made From An Ultra High Molecular Weight Bioabsorbable Polymer With High Fatigue And Fracture Resistance |
US20100262244A1 (en) * | 2009-04-14 | 2010-10-14 | Warsaw Orthopedic, Inc. | Metal Coated Implant |
US20110022180A1 (en) * | 2009-07-24 | 2011-01-27 | Warsaw Orthopedic, Inc. | Implantable medical devices |
US20110029026A1 (en) * | 2009-07-28 | 2011-02-03 | Southwest Research Institute | Micro-Structure Particles For Load Bearing Bone Growth |
US20110035017A1 (en) * | 2007-09-25 | 2011-02-10 | Depuy Products, Inc. | Prosthesis with cut-off pegs and surgical method |
US20110045087A1 (en) * | 2008-02-01 | 2011-02-24 | Synthes Gmbh | Porous biocompatible polymer material and methods |
EP2319462A1 (en) | 2009-10-30 | 2011-05-11 | DePuy Products, Inc. | Prosthesis with composite component |
US20110144752A1 (en) * | 2008-08-14 | 2011-06-16 | Defelice Scott F | Customized implants for bone replacement |
US8128703B2 (en) | 2007-09-28 | 2012-03-06 | Depuy Products, Inc. | Fixed-bearing knee prosthesis having interchangeable components |
WO2012051420A2 (en) * | 2010-10-13 | 2012-04-19 | Cibor, Inc. | Synthetic bone grafts constructed from carbon foam materials |
WO2012065068A1 (en) * | 2010-11-11 | 2012-05-18 | Zimmer, Inc. | Orthopedic implant with porous polymer bone contacting surface |
US8187335B2 (en) | 2008-06-30 | 2012-05-29 | Depuy Products, Inc. | Posterior stabilized orthopaedic knee prosthesis having controlled condylar curvature |
US8192498B2 (en) | 2008-06-30 | 2012-06-05 | Depuy Products, Inc. | Posterior cructiate-retaining orthopaedic knee prosthesis having controlled condylar curvature |
WO2012045013A3 (en) * | 2010-10-01 | 2012-06-21 | Skeletal Kinetics, Llc | Porogen containing calcium phosphate cement compositions |
US8206451B2 (en) | 2008-06-30 | 2012-06-26 | Depuy Products, Inc. | Posterior stabilized orthopaedic prosthesis |
WO2012098378A1 (en) * | 2011-01-18 | 2012-07-26 | Invibio Limited | Polymeric materials |
US8236061B2 (en) | 2008-06-30 | 2012-08-07 | Depuy Products, Inc. | Orthopaedic knee prosthesis having controlled condylar curvature |
CN102642288A (en) * | 2011-02-17 | 2012-08-22 | 赢创德固赛有限公司 | Method for manufacturing rods and their use as implants |
WO2012110803A1 (en) * | 2011-02-14 | 2012-08-23 | Invibio Limited | Components incorporating bioactive material |
CN102727937A (en) * | 2012-06-28 | 2012-10-17 | 哈尔滨工程大学 | Biodegradable zinc (or zinc alloy) and porous biphase calcium phosphate composite material and preparation method thereof |
KR101196062B1 (en) | 2010-05-03 | 2012-11-01 | 순천향대학교 산학협력단 | Method for preparing porous biphasic calciumphosphate granules |
US20130085590A1 (en) * | 2011-10-03 | 2013-04-04 | Jason A. Bryan | Synthetic bone model and method for providing same |
WO2013181375A1 (en) * | 2012-05-30 | 2013-12-05 | New York University | Tissue repair devices and scaffolds |
WO2013079655A3 (en) * | 2011-12-01 | 2014-01-09 | Technische Universität Hamburg-Harburg | Method for producing a composite material, the composite material and the use of the composite material for producing specific products |
US8632600B2 (en) | 2007-09-25 | 2014-01-21 | Depuy (Ireland) | Prosthesis with modular extensions |
US8715359B2 (en) | 2009-10-30 | 2014-05-06 | Depuy (Ireland) | Prosthesis for cemented fixation and method for making the prosthesis |
US8722783B2 (en) | 2006-11-30 | 2014-05-13 | Smith & Nephew, Inc. | Fiber reinforced composite material |
US20140221615A1 (en) * | 2011-08-30 | 2014-08-07 | Kyoto University | Porous scaffold material, and method for producing same |
US8828086B2 (en) | 2008-06-30 | 2014-09-09 | Depuy (Ireland) | Orthopaedic femoral component having controlled condylar curvature |
WO2014153127A1 (en) * | 2013-03-14 | 2014-09-25 | Skeletal Kinetics, Llc | Calcium phosphate cement compositions that set into high strength porous structures |
US20150018956A1 (en) * | 2012-06-21 | 2015-01-15 | Renovis Surgical, Inc. | Surgical implant devices incorporating porous surfaces |
US9000066B2 (en) | 2007-04-19 | 2015-04-07 | Smith & Nephew, Inc. | Multi-modal shape memory polymers |
US9011547B2 (en) | 2010-01-21 | 2015-04-21 | Depuy (Ireland) | Knee prosthesis system |
US9120919B2 (en) | 2003-12-23 | 2015-09-01 | Smith & Nephew, Inc. | Tunable segmented polyacetal |
US9119723B2 (en) | 2008-06-30 | 2015-09-01 | Depuy (Ireland) | Posterior stabilized orthopaedic prosthesis assembly |
US9119728B2 (en) | 2011-01-17 | 2015-09-01 | Cibor, Inc. | Reinforced carbon fiber/carbon foam intervertebral spine fusion device |
US9168145B2 (en) | 2008-06-30 | 2015-10-27 | Depuy (Ireland) | Posterior stabilized orthopaedic knee prosthesis having controlled condylar curvature |
US9204967B2 (en) | 2007-09-28 | 2015-12-08 | Depuy (Ireland) | Fixed-bearing knee prosthesis having interchangeable components |
CN105233335A (en) * | 2015-11-06 | 2016-01-13 | 四川大学 | Porous polyaryletherketone material with bioactivity, and preparation method and application thereof |
US9295565B2 (en) | 2013-10-18 | 2016-03-29 | Spine Wave, Inc. | Method of expanding an intradiscal space and providing an osteoconductive path during expansion |
CN105559950A (en) * | 2016-02-03 | 2016-05-11 | 北京纳通科技集团有限公司 | Fusion cage |
WO2016105286A1 (en) * | 2014-12-25 | 2016-06-30 | Hasirci Vasif Nejat | A new prosthesis material developed for use in the treatment of cervical and lumbar disc hernia |
WO2016108769A1 (en) * | 2014-12-29 | 2016-07-07 | Hasirci Vasif Nejat | Craniofacial implants |
US9492280B2 (en) | 2000-11-28 | 2016-11-15 | Medidea, Llc | Multiple-cam, posterior-stabilized knee prosthesis |
CN106344221A (en) * | 2016-10-26 | 2017-01-25 | 四川大学 | Bonelike porous biomechanical bionic designed spinal fusion device and preparation method and use thereof |
US20170021054A1 (en) * | 2014-10-14 | 2017-01-26 | Lynch Samuel E | Compositions for treating wounds |
FR3039988A1 (en) * | 2015-08-11 | 2017-02-17 | Abdelmadjid Djemai | EXPANDED SPRING INTERSOMATIC CAGE, DOUBLE-STRUCKED DOUBLE STRUCK HINGE AND METHOD FOR MANUFACTURING THE SAME |
CN106435544A (en) * | 2016-11-09 | 2017-02-22 | 北京科技大学 | Method for preparing nano-hydroxyapatite gradient coating on titanium alloy matrix |
EP3024419A4 (en) * | 2013-07-24 | 2017-03-08 | Renovis Surgical Technologies Inc. | Surgical implant devices incorporating porous surfaces |
US20170165790A1 (en) * | 2015-12-15 | 2017-06-15 | Howmedica Osteonics Corp. | Porous structures produced by additive layer manufacturing |
CN106913406A (en) * | 2015-12-25 | 2017-07-04 | 苏州微创脊柱创伤医疗科技有限公司 | A kind of spinal fusion device and preparation method thereof |
US9770534B2 (en) | 2007-04-19 | 2017-09-26 | Smith & Nephew, Inc. | Graft fixation |
US9815240B2 (en) | 2007-04-18 | 2017-11-14 | Smith & Nephew, Inc. | Expansion moulding of shape memory polymers |
US20180125675A1 (en) * | 2006-10-30 | 2018-05-10 | DePuy Synthes Products, Inc. | Degradable Cage For Bone Fusion |
CN108309517A (en) * | 2018-01-25 | 2018-07-24 | 中国人民解放军新疆军区总医院 | A kind of absorbable cervical fusion cage and preparation method thereof |
US10064726B1 (en) * | 2017-04-18 | 2018-09-04 | Warsaw Orthopedic, Inc. | 3D printing of mesh implants for bone delivery |
US20180296343A1 (en) * | 2017-04-18 | 2018-10-18 | Warsaw Orthopedic, Inc. | 3-d printing of porous implants |
US10183442B1 (en) | 2018-03-02 | 2019-01-22 | Additive Device, Inc. | Medical devices and methods for producing the same |
US10207027B2 (en) | 2012-06-11 | 2019-02-19 | Globus Medical, Inc. | Bioactive bone graft substitutes |
US10226883B2 (en) | 2014-06-26 | 2019-03-12 | Vertera, Inc. | Mold and process for producing porous devices |
JP2019513495A (en) * | 2016-04-19 | 2019-05-30 | カール ライビンガー メディツィンテヒニーク ゲーエムベーハー ウント コーカーゲーKarl Leibinger Medizintechnik Gmbh & Co. Kg | Hybrid implant consisting of composite material |
US10405962B2 (en) | 2014-06-26 | 2019-09-10 | Vertera, Inc. | Porous devices and methods of producing the same |
CN110418624A (en) * | 2016-10-25 | 2019-11-05 | 肌肉骨骼科学教育研究所有限公司 | Implantation material with multilayer bone engagement screen work |
USD870888S1 (en) | 2018-03-02 | 2019-12-24 | Restor3D, Inc. | Accordion airway stent |
USD870889S1 (en) | 2018-03-02 | 2019-12-24 | Restor3D, Inc. | Cutout airway stent |
USD870890S1 (en) | 2018-03-02 | 2019-12-24 | Restor3D, Inc. | Spiral airway stent |
USD871577S1 (en) | 2018-03-02 | 2019-12-31 | Restor3D, Inc. | Studded airway stent |
US10660764B2 (en) * | 2016-06-14 | 2020-05-26 | The Trustees Of The Stevens Institute Of Technology | Load sustaining bone scaffolds for spinal fusion utilizing hyperbolic struts and translational strength gradients |
KR20200104856A (en) * | 2017-11-14 | 2020-09-04 | 스노우플레이크 인코포레이티드 | Database metadata within an immutable repository |
US10772732B1 (en) | 2020-01-08 | 2020-09-15 | Restor3D, Inc. | Sheet based triply periodic minimal surface implants for promoting osseointegration and methods for producing same |
CN112060574A (en) * | 2020-07-21 | 2020-12-11 | 陈勃生 | Additive manufacturing method of three-dimensional implant made of biological composite material |
US10889053B1 (en) | 2019-03-25 | 2021-01-12 | Restor3D, Inc. | Custom surgical devices and method for manufacturing the same |
US10888362B2 (en) | 2017-11-03 | 2021-01-12 | Howmedica Osteonics Corp. | Flexible construct for femoral reconstruction |
US10945854B2 (en) | 2007-02-28 | 2021-03-16 | Happe Spine, Llc | Porous composite biomaterials and related methods |
USD920517S1 (en) | 2020-01-08 | 2021-05-25 | Restor3D, Inc. | Osteotomy wedge |
USD920515S1 (en) | 2020-01-08 | 2021-05-25 | Restor3D, Inc. | Spinal implant |
USD920516S1 (en) | 2020-01-08 | 2021-05-25 | Restor3D, Inc. | Osteotomy wedge |
CN113103576A (en) * | 2021-04-07 | 2021-07-13 | 吉林大学 | 3D printing system and method for ordered gradient porous material |
US11179243B2 (en) | 2007-02-28 | 2021-11-23 | Happe Spine Llc | Implantable devices |
CN113842499A (en) * | 2021-09-17 | 2021-12-28 | 中国科学院宁波材料技术与工程研究所 | Ultrahigh molecular weight polyethylene composite material and preparation method and application thereof |
USD944990S1 (en) | 2015-06-23 | 2022-03-01 | Vertera, Inc. | Cervical interbody fusion device |
EP3984501A1 (en) * | 2020-10-14 | 2022-04-20 | Warsaw Orthopedic, Inc. | Additive-manufactured non-woven fibrous implants, systems, and related manufacturing methods |
US11364122B2 (en) | 2017-03-10 | 2022-06-21 | Vestlandets Innovasjonsselskap As | Tissue engineering scaffolds |
US11364323B2 (en) * | 2018-09-17 | 2022-06-21 | Rejuvablast LLC | Combination grafts for tissue repair or regeneration applications |
US20220203589A1 (en) * | 2020-12-24 | 2022-06-30 | Next Chapter Manufacturing Corporation | Vented Mold Pin |
WO2022197859A1 (en) * | 2021-03-16 | 2022-09-22 | Orthomod Llc | Bioceramic-containing thermoplastic extrusion and method of surgical implant manufacture |
US11458027B2 (en) | 2010-12-21 | 2022-10-04 | DePuy Synthes Products, Inc. | Intervertebral implants, systems, and methods of use |
US11517444B2 (en) | 2008-11-07 | 2022-12-06 | DePuy Synthes Products, Inc. | Zero-profile interbody spacer and coupled plate assembly |
US11524094B2 (en) * | 2016-09-19 | 2022-12-13 | Biomendex Oy | Porous composite material |
US11540927B2 (en) | 2014-10-22 | 2023-01-03 | DePuy Synthes Products, Inc. | Intervertebral implants, systems, and methods of use |
US11607476B2 (en) | 2019-03-12 | 2023-03-21 | Happe Spine Llc | Implantable medical device with thermoplastic composite body and method for forming thermoplastic composite body |
US11628517B2 (en) | 2017-06-15 | 2023-04-18 | Howmedica Osteonics Corp. | Porous structures produced by additive layer manufacturing |
US20230132015A1 (en) * | 2013-03-07 | 2023-04-27 | Howmedica Osteonics Corp. | Partially Porous Tibial Component |
EP3256079B1 (en) * | 2015-02-13 | 2023-05-03 | Eit Emerging Implant Technologies GmbH | Spinal implants with engineered cellular structure and internal imaging markers |
US11685113B2 (en) * | 2017-03-06 | 2023-06-27 | Katholieke Universiteit Leuven | 3D printing of porous liquid handling device |
US11696837B2 (en) | 2006-02-27 | 2023-07-11 | DePuy Synthes Products, Inc. | Intervertebral implant with fixation geometry |
WO2023137124A3 (en) * | 2022-01-12 | 2023-08-24 | Orthofundamentals, Llc | Medical implants for generating fusion between two bones |
US11780175B2 (en) | 2012-08-21 | 2023-10-10 | Nuvasive, Inc. | Systems and methods for making porous films, fibers, spheres, and other articles |
US11806028B1 (en) | 2022-10-04 | 2023-11-07 | Restor3D, Inc. | Surgical guides and processes for producing and using the same |
US11850144B1 (en) | 2022-09-28 | 2023-12-26 | Restor3D, Inc. | Ligament docking implants and processes for making and using same |
US11872136B2 (en) | 2012-01-17 | 2024-01-16 | KYOCERA Medical Technologies, Inc. | Surgical implant devices incorporating porous surfaces and associated method of manufacture |
Families Citing this family (23)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8843229B2 (en) * | 2012-07-20 | 2014-09-23 | Biomet Manufacturing, Llc | Metallic structures having porous regions from imaged bone at pre-defined anatomic locations |
US9550012B2 (en) | 2013-08-05 | 2017-01-24 | University Of Notre Dame Du Lac | Tissue scaffolds having bone growth factors |
US10279081B2 (en) | 2014-10-24 | 2019-05-07 | Allosource | Composite grafts, systems, and methods |
US20160167306A1 (en) * | 2014-12-11 | 2016-06-16 | Massachusetts Institute Of Technology | Systems and methods of hierarchical material design for additive fabrication |
US9486960B2 (en) | 2014-12-19 | 2016-11-08 | Palo Alto Research Center Incorporated | System for digital fabrication of graded, hierarchical material structures |
US9821339B2 (en) * | 2014-12-19 | 2017-11-21 | Palo Alto Research Center Incorporated | System and method for digital fabrication of graded, hierarchical material structures |
CN104623728B (en) * | 2015-01-12 | 2016-05-11 | 四川大学 | Anisotropy bone replacement composites of a kind of injection mo(u)lding and preparation method thereof |
US10485897B2 (en) * | 2015-10-12 | 2019-11-26 | Erik Erbe | Osteogenic and angiogenic implant material |
EP3389570A1 (en) * | 2015-12-16 | 2018-10-24 | Nuvasive, Inc. | Porous spinal fusion implant |
KR20180127641A (en) * | 2016-03-18 | 2018-11-29 | 알로소스 | Composite medical implants and methods for their use and manufacturing |
CA3018116A1 (en) * | 2016-03-18 | 2017-09-21 | Allosource | Composite medical grafts and methods of use and manufacture |
WO2017201371A1 (en) * | 2016-05-19 | 2017-11-23 | University Of Pittsburgh-Of The Commonwealth System Of Higher Education | Biomimetic plywood motifs for bone tissue engineering |
US11638645B2 (en) | 2016-05-19 | 2023-05-02 | University of Pittsburgh—of the Commonwealth System of Higher Education | Biomimetic plywood motifs for bone tissue engineering |
EP3592300A1 (en) * | 2017-03-10 | 2020-01-15 | Life Spine, Inc. (a Delaware Corporation) | 3-d printed orthopedic implants |
US11660196B2 (en) | 2017-04-21 | 2023-05-30 | Warsaw Orthopedic, Inc. | 3-D printing of bone grafts |
US20180339082A1 (en) * | 2017-05-23 | 2018-11-29 | Bioalpha Corporation | Polyether ether ketone surface-modified with hydroxyapatite |
CN107320220B (en) * | 2017-06-14 | 2019-12-24 | 西安交通大学 | Preparation method of porous implant based on ceramic additive manufacturing |
EP3773347A4 (en) * | 2018-03-26 | 2022-01-05 | The Regents of The University of California | Medical implants and other articles of manufacture based on trabecular bone lattices |
US10947419B2 (en) | 2018-07-23 | 2021-03-16 | Palo Alto Research Center Incorporated | Method for joining dissimilar materials |
WO2020061176A1 (en) * | 2018-09-18 | 2020-03-26 | Happe Spine Llc | Implantable devices |
WO2022056384A1 (en) | 2020-09-11 | 2022-03-17 | Happe Spine Llc | Method for forming an implantable medical device with varied composition and porosity |
EP3984715B1 (en) * | 2020-10-13 | 2023-11-15 | Technische Universität München | Fiber-reinforced soluble core and method for its manufacture |
CN115120781A (en) * | 2022-07-11 | 2022-09-30 | 运怡(北京)医疗器械有限公司 | Medical composite high polymer material and preparation method thereof |
Citations (39)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5514378A (en) * | 1993-02-01 | 1996-05-07 | Massachusetts Institute Of Technology | Biocompatible polymer membranes and methods of preparation of three dimensional membrane structures |
US5522895A (en) * | 1993-07-23 | 1996-06-04 | Rice University | Biodegradable bone templates |
US5766618A (en) * | 1994-04-01 | 1998-06-16 | Massachusetts Institute Of Technology | Polymeric-hydroxyapatite bone composite |
US5866155A (en) * | 1996-11-20 | 1999-02-02 | Allegheny Health, Education And Research Foundation | Methods for using microsphere polymers in bone replacement matrices and composition produced thereby |
US5981619A (en) * | 1995-09-14 | 1999-11-09 | Takiron Co., Ltd. | Material for osteosynthesis and composite implant material, and production processes thereof |
US6306424B1 (en) * | 1999-06-30 | 2001-10-23 | Ethicon, Inc. | Foam composite for the repair or regeneration of tissue |
US6333029B1 (en) * | 1999-06-30 | 2001-12-25 | Ethicon, Inc. | Porous tissue scaffoldings for the repair of regeneration of tissue |
US6355699B1 (en) * | 1999-06-30 | 2002-03-12 | Ethicon, Inc. | Process for manufacturing biomedical foams |
US20020035401A1 (en) * | 2000-07-03 | 2002-03-21 | Osteotech, Inc. | Osteogenic implants derived from bone |
US6423252B1 (en) * | 2000-06-23 | 2002-07-23 | Ethicon, Inc. | Methods of making micropatterned foams |
US20020115742A1 (en) * | 2001-02-22 | 2002-08-22 | Trieu Hai H. | Bioactive nanocomposites and methods for their use |
US20020183761A1 (en) * | 2001-03-08 | 2002-12-05 | Wes Johnson | Tissue distraction device |
US20030031698A1 (en) * | 2000-01-31 | 2003-02-13 | Roeder Ryan K. | Composite biomaterial including anisometric calcium phosphate reinforcement particles and related methods |
US20030078661A1 (en) * | 2001-09-27 | 2003-04-24 | Houfburg Rodney L. | Modular spinal fusion device |
US20040002770A1 (en) * | 2002-06-28 | 2004-01-01 | King Richard S. | Polymer-bioceramic composite for orthopaedic applications and method of manufacture thereof |
US6673285B2 (en) * | 2000-05-12 | 2004-01-06 | The Regents Of The University Of Michigan | Reverse fabrication of porous materials |
US6689608B1 (en) * | 1993-02-01 | 2004-02-10 | Massachusetts Institute Of Technology | Porous biodegradable polymeric materials for cell transplantation |
US6712850B2 (en) * | 2001-11-30 | 2004-03-30 | Ethicon, Inc. | Porous tissue scaffolds for the repair and regeneration of dermal tissue |
US6758862B2 (en) * | 2002-03-21 | 2004-07-06 | Sdgi Holdings, Inc. | Vertebral body and disc space replacement devices |
US20040193270A1 (en) * | 2003-03-31 | 2004-09-30 | Depuyacromed, Inc. | Implantable bone graft |
US6887408B2 (en) * | 2003-05-05 | 2005-05-03 | Porogen Llc | Porous poly(aryl ether ketone) membranes, processes for their preparation and use thereof |
US20050100578A1 (en) * | 2003-11-06 | 2005-05-12 | Schmid Steven R. | Bone and tissue scaffolding and method for producing same |
US20050125073A1 (en) * | 2003-12-08 | 2005-06-09 | Orban Janine M. | Implant device for cartilage regeneration in load bearing articulation regions |
US20050143822A1 (en) * | 2003-12-29 | 2005-06-30 | Paul David C. | Spinal fusion implant |
US20050149193A1 (en) * | 2003-11-20 | 2005-07-07 | St. Francis Medical Technology, Inc. | Intervertebral body fusion cage with keels and implantation methods |
US20050149192A1 (en) * | 2003-11-20 | 2005-07-07 | St. Francis Medical Technologies, Inc. | Intervertebral body fusion cage with keels and implantation method |
US20050177238A1 (en) * | 2001-05-01 | 2005-08-11 | Khandkar Ashok C. | Radiolucent bone graft |
US20050209704A1 (en) * | 2002-03-14 | 2005-09-22 | Maspero Fabrizio A | Porous biocompatible implant material and method for its fabrication |
US6987136B2 (en) * | 2001-07-13 | 2006-01-17 | Vita Special Purpose Corporation | Bioactive spinal implant material and method of manufacture thereof |
US6991653B2 (en) * | 2002-03-21 | 2006-01-31 | Sdgi Holdings, Inc. | Vertebral body and disc space replacement devices |
US20060041258A1 (en) * | 2004-08-19 | 2006-02-23 | Foster-Miller, Inc. | Support system for intervertebral fusion |
US7022522B2 (en) * | 1998-11-13 | 2006-04-04 | Limin Guan | Macroporous polymer scaffold containing calcium phosphate particles |
US7049348B2 (en) * | 2002-07-06 | 2006-05-23 | Kensey Nash Corporation | Resorbable structure for treating and healing of tissue defects |
US7060073B2 (en) * | 1999-10-21 | 2006-06-13 | Sdgi Holdings, Inc. | Devices and techniques for a posterior lateral disc space approach |
US20060212118A1 (en) * | 2005-03-16 | 2006-09-21 | Abernathie Dennis L | Spinal fusion cage and method of use |
US20070043442A1 (en) * | 2005-03-16 | 2007-02-22 | Abernathie Dennis L | Spinal Fusion Cage, Method of Design, and Method of Use |
US7189263B2 (en) * | 2004-02-03 | 2007-03-13 | Vita Special Purpose Corporation | Biocompatible bone graft material |
US7368526B2 (en) * | 2004-11-03 | 2008-05-06 | Porogen Corporation | Functionalized porous poly(aryl ether ketone) materials and their use |
US20080161927A1 (en) * | 2006-10-18 | 2008-07-03 | Warsaw Orthopedic, Inc. | Intervertebral Implant with Porous Portions |
Family Cites Families (34)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6472210B1 (en) * | 1997-11-14 | 2002-10-29 | Bonetec Corporation | Polymer scaffold having microporous polymer struts defining interconnected macropores |
US20050251267A1 (en) | 2004-05-04 | 2005-11-10 | John Winterbottom | Cell permeable structural implant |
WO2005032418A2 (en) | 2003-10-01 | 2005-04-14 | University Of Washington | Novel porous biomaterials |
WO2006113642A1 (en) | 2005-04-18 | 2006-10-26 | Duke University | Three-dimensional fiber scaffolds for tissue engineering |
US7687098B1 (en) | 2005-08-26 | 2010-03-30 | Charlie W. Chi | Chemical mechanical vapor deposition device for production of bone substitute material |
CA2627895C (en) | 2005-11-04 | 2014-10-14 | Ppd Meditech | Porous material and method for fabricating same |
GB0604061D0 (en) | 2006-03-01 | 2006-04-12 | Invibio Ltd | Polymetric materials |
DE102006041023B4 (en) | 2006-09-01 | 2014-06-12 | Biocer Entwicklungs Gmbh | Structured coatings for implants and process for their preparation |
JP5378218B2 (en) | 2006-09-25 | 2013-12-25 | オーソビタ, インコーポレイテッド | Bioactive load-supporting complex |
US20080206297A1 (en) | 2007-02-28 | 2008-08-28 | Roeder Ryan K | Porous composite biomaterials and related methods |
JP2010522620A (en) | 2007-03-26 | 2010-07-08 | ユニヴァーシティ オブ コネチカット | Electrospun apatite / polymer nanocomposite skeleton |
US20110035018A1 (en) | 2007-09-25 | 2011-02-10 | Depuy Products, Inc. | Prosthesis with composite component |
WO2009095960A1 (en) | 2008-01-28 | 2009-08-06 | Ngk Spark Plug Co., Ltd. | Surface foamed article, biological implant and method of producing the same |
EP2238192B1 (en) | 2008-02-01 | 2017-03-01 | Synthes GmbH | Porous biocompatible polymer material and methods |
GB0813093D0 (en) | 2008-07-17 | 2008-08-27 | Invibio Ltd | Polymeric materials |
US8323722B2 (en) | 2008-07-18 | 2012-12-04 | North Carolina State University | Processing of biocompatible coating on polymeric implants |
GB0818156D0 (en) | 2008-10-03 | 2008-11-12 | Smith & Nephew Orthopaedics Ag | Plasma spray process and products formed thereby |
GB0819055D0 (en) | 2008-10-17 | 2008-11-26 | Invibio Ltd | Polymeric materials |
US20100145393A1 (en) | 2008-12-05 | 2010-06-10 | Medicinelodge, Inc. | Medical and dental porous implants |
US20100168798A1 (en) | 2008-12-30 | 2010-07-01 | Clineff Theodore D | Bioactive composites of polymer and glass and method for making same |
US8609127B2 (en) | 2009-04-03 | 2013-12-17 | Warsaw Orthopedic, Inc. | Medical implant with bioactive material and method of making the medical implant |
GB2469991B (en) | 2009-04-21 | 2013-08-07 | Invibio Ltd | Polymeric materials |
US8486143B2 (en) | 2009-05-22 | 2013-07-16 | Soft Tissue Regeneration, Inc. | Mechanically competent scaffold for ligament and tendon regeneration |
DE102009026622A1 (en) | 2009-05-29 | 2010-12-02 | Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. | Shaped bodies with embedded coupling particles for biomolecules |
US9399086B2 (en) | 2009-07-24 | 2016-07-26 | Warsaw Orthopedic, Inc | Implantable medical devices |
US8226725B2 (en) | 2009-09-01 | 2012-07-24 | Howmedica Osteonics Corp. | Prosthesis having a soft tissue attachment element |
ES2664944T3 (en) | 2009-12-23 | 2018-04-24 | Fundacion Inasmet | Porous PEEK article as an implant |
GB201005122D0 (en) | 2010-03-26 | 2010-05-12 | Invibio Ltd | Medical device |
GB2488111A (en) | 2011-02-14 | 2012-08-22 | Invibio Ltd | Components incorporating bioactive material |
GB201104805D0 (en) | 2011-03-22 | 2011-05-04 | Invibio Ltd | Medical device |
GB201110729D0 (en) | 2011-06-24 | 2011-08-10 | Invibio Ltd | Polymeric materials |
GB201120375D0 (en) | 2011-11-25 | 2012-01-11 | Invibio Ltd | Prosthodontic device |
GB201219686D0 (en) | 2012-11-01 | 2012-12-12 | Invibio Ltd | Orthopaedic polymer-on-polymer bearings |
US8829096B2 (en) | 2013-02-08 | 2014-09-09 | Invibio Limited | Polymeric materials |
-
2008
- 2008-02-28 US US12/039,666 patent/US20080206297A1/en not_active Abandoned
- 2008-02-28 WO PCT/US2008/055391 patent/WO2008106625A2/en active Application Filing
-
2013
- 2013-11-13 US US14/078,614 patent/US10945854B2/en active Active
-
2021
- 2021-02-22 US US17/180,935 patent/US20210177620A1/en not_active Abandoned
- 2021-11-04 US US17/519,336 patent/US20220062004A1/en active Pending
Patent Citations (53)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5514378A (en) * | 1993-02-01 | 1996-05-07 | Massachusetts Institute Of Technology | Biocompatible polymer membranes and methods of preparation of three dimensional membrane structures |
US6689608B1 (en) * | 1993-02-01 | 2004-02-10 | Massachusetts Institute Of Technology | Porous biodegradable polymeric materials for cell transplantation |
US5522895A (en) * | 1993-07-23 | 1996-06-04 | Rice University | Biodegradable bone templates |
US5766618A (en) * | 1994-04-01 | 1998-06-16 | Massachusetts Institute Of Technology | Polymeric-hydroxyapatite bone composite |
US5981619A (en) * | 1995-09-14 | 1999-11-09 | Takiron Co., Ltd. | Material for osteosynthesis and composite implant material, and production processes thereof |
US5866155A (en) * | 1996-11-20 | 1999-02-02 | Allegheny Health, Education And Research Foundation | Methods for using microsphere polymers in bone replacement matrices and composition produced thereby |
US7022522B2 (en) * | 1998-11-13 | 2006-04-04 | Limin Guan | Macroporous polymer scaffold containing calcium phosphate particles |
US6306424B1 (en) * | 1999-06-30 | 2001-10-23 | Ethicon, Inc. | Foam composite for the repair or regeneration of tissue |
US6365149B2 (en) * | 1999-06-30 | 2002-04-02 | Ethicon, Inc. | Porous tissue scaffoldings for the repair or regeneration of tissue |
US6355699B1 (en) * | 1999-06-30 | 2002-03-12 | Ethicon, Inc. | Process for manufacturing biomedical foams |
US6534084B1 (en) * | 1999-06-30 | 2003-03-18 | Ethicon, Inc. | Porous tissue scaffoldings for the repair or regeneration of tissue |
US6333029B1 (en) * | 1999-06-30 | 2001-12-25 | Ethicon, Inc. | Porous tissue scaffoldings for the repair of regeneration of tissue |
US7112417B2 (en) * | 1999-06-30 | 2006-09-26 | Ethicon, Inc. | Foam composite for the repair or regeneration of tissue |
US7060073B2 (en) * | 1999-10-21 | 2006-06-13 | Sdgi Holdings, Inc. | Devices and techniques for a posterior lateral disc space approach |
US20030031698A1 (en) * | 2000-01-31 | 2003-02-13 | Roeder Ryan K. | Composite biomaterial including anisometric calcium phosphate reinforcement particles and related methods |
US6673285B2 (en) * | 2000-05-12 | 2004-01-06 | The Regents Of The University Of Michigan | Reverse fabrication of porous materials |
US6423252B1 (en) * | 2000-06-23 | 2002-07-23 | Ethicon, Inc. | Methods of making micropatterned foams |
US20020035401A1 (en) * | 2000-07-03 | 2002-03-21 | Osteotech, Inc. | Osteogenic implants derived from bone |
US20020115742A1 (en) * | 2001-02-22 | 2002-08-22 | Trieu Hai H. | Bioactive nanocomposites and methods for their use |
US20040024081A1 (en) * | 2001-02-22 | 2004-02-05 | Trieu Hai H. | Bioactive nanocomposites and methods for their use |
US6595998B2 (en) * | 2001-03-08 | 2003-07-22 | Spinewave, Inc. | Tissue distraction device |
US20020183761A1 (en) * | 2001-03-08 | 2002-12-05 | Wes Johnson | Tissue distraction device |
US20050171552A1 (en) * | 2001-03-08 | 2005-08-04 | Wes Johnson | Tissue distraction device |
US20040064144A1 (en) * | 2001-03-08 | 2004-04-01 | Wes Johnson | Tissue distraction device |
US20060161166A1 (en) * | 2001-03-08 | 2006-07-20 | Spine Wave, Inc. | Tissue distraction device |
US20040220580A1 (en) * | 2001-03-08 | 2004-11-04 | Wes Johnson | Tissue distraction device |
US20050187558A1 (en) * | 2001-03-08 | 2005-08-25 | Johnson Wesley D. | Tissue distraction device |
US20040019354A1 (en) * | 2001-03-08 | 2004-01-29 | Wes Johnson | Tissue distraction device |
US20050177238A1 (en) * | 2001-05-01 | 2005-08-11 | Khandkar Ashok C. | Radiolucent bone graft |
US6987136B2 (en) * | 2001-07-13 | 2006-01-17 | Vita Special Purpose Corporation | Bioactive spinal implant material and method of manufacture thereof |
US20030078661A1 (en) * | 2001-09-27 | 2003-04-24 | Houfburg Rodney L. | Modular spinal fusion device |
US7037339B2 (en) * | 2001-09-27 | 2006-05-02 | Zimmer Spine, Inc. | Modular spinal fusion device |
US6712850B2 (en) * | 2001-11-30 | 2004-03-30 | Ethicon, Inc. | Porous tissue scaffolds for the repair and regeneration of dermal tissue |
US20050209704A1 (en) * | 2002-03-14 | 2005-09-22 | Maspero Fabrizio A | Porous biocompatible implant material and method for its fabrication |
US6991653B2 (en) * | 2002-03-21 | 2006-01-31 | Sdgi Holdings, Inc. | Vertebral body and disc space replacement devices |
US6758862B2 (en) * | 2002-03-21 | 2004-07-06 | Sdgi Holdings, Inc. | Vertebral body and disc space replacement devices |
US20040002770A1 (en) * | 2002-06-28 | 2004-01-01 | King Richard S. | Polymer-bioceramic composite for orthopaedic applications and method of manufacture thereof |
US7049348B2 (en) * | 2002-07-06 | 2006-05-23 | Kensey Nash Corporation | Resorbable structure for treating and healing of tissue defects |
US20060210598A1 (en) * | 2002-07-06 | 2006-09-21 | Evans Douglas G | Resorbable structure for treating and healing of tissue defects |
US20040193270A1 (en) * | 2003-03-31 | 2004-09-30 | Depuyacromed, Inc. | Implantable bone graft |
US6887408B2 (en) * | 2003-05-05 | 2005-05-03 | Porogen Llc | Porous poly(aryl ether ketone) membranes, processes for their preparation and use thereof |
US20050100578A1 (en) * | 2003-11-06 | 2005-05-12 | Schmid Steven R. | Bone and tissue scaffolding and method for producing same |
US20050149193A1 (en) * | 2003-11-20 | 2005-07-07 | St. Francis Medical Technology, Inc. | Intervertebral body fusion cage with keels and implantation methods |
US20050149192A1 (en) * | 2003-11-20 | 2005-07-07 | St. Francis Medical Technologies, Inc. | Intervertebral body fusion cage with keels and implantation method |
US20050125073A1 (en) * | 2003-12-08 | 2005-06-09 | Orban Janine M. | Implant device for cartilage regeneration in load bearing articulation regions |
US20050143822A1 (en) * | 2003-12-29 | 2005-06-30 | Paul David C. | Spinal fusion implant |
US7137997B2 (en) * | 2003-12-29 | 2006-11-21 | Globus Medical, Inc. | Spinal fusion implant |
US7189263B2 (en) * | 2004-02-03 | 2007-03-13 | Vita Special Purpose Corporation | Biocompatible bone graft material |
US20060041258A1 (en) * | 2004-08-19 | 2006-02-23 | Foster-Miller, Inc. | Support system for intervertebral fusion |
US7368526B2 (en) * | 2004-11-03 | 2008-05-06 | Porogen Corporation | Functionalized porous poly(aryl ether ketone) materials and their use |
US20060212118A1 (en) * | 2005-03-16 | 2006-09-21 | Abernathie Dennis L | Spinal fusion cage and method of use |
US20070043442A1 (en) * | 2005-03-16 | 2007-02-22 | Abernathie Dennis L | Spinal Fusion Cage, Method of Design, and Method of Use |
US20080161927A1 (en) * | 2006-10-18 | 2008-07-03 | Warsaw Orthopedic, Inc. | Intervertebral Implant with Porous Portions |
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Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9492280B2 (en) | 2000-11-28 | 2016-11-15 | Medidea, Llc | Multiple-cam, posterior-stabilized knee prosthesis |
US10188521B2 (en) | 2000-11-28 | 2019-01-29 | Medidea, Llc | Multiple-cam, posterior-stabilized knee prosthesis |
US9120919B2 (en) | 2003-12-23 | 2015-09-01 | Smith & Nephew, Inc. | Tunable segmented polyacetal |
US11696837B2 (en) | 2006-02-27 | 2023-07-11 | DePuy Synthes Products, Inc. | Intervertebral implant with fixation geometry |
US20180125675A1 (en) * | 2006-10-30 | 2018-05-10 | DePuy Synthes Products, Inc. | Degradable Cage For Bone Fusion |
US8722783B2 (en) | 2006-11-30 | 2014-05-13 | Smith & Nephew, Inc. | Fiber reinforced composite material |
US11179243B2 (en) | 2007-02-28 | 2021-11-23 | Happe Spine Llc | Implantable devices |
US10945854B2 (en) | 2007-02-28 | 2021-03-16 | Happe Spine, Llc | Porous composite biomaterials and related methods |
US9815240B2 (en) | 2007-04-18 | 2017-11-14 | Smith & Nephew, Inc. | Expansion moulding of shape memory polymers |
US9770534B2 (en) | 2007-04-19 | 2017-09-26 | Smith & Nephew, Inc. | Graft fixation |
US9000066B2 (en) | 2007-04-19 | 2015-04-07 | Smith & Nephew, Inc. | Multi-modal shape memory polymers |
US9308293B2 (en) | 2007-04-19 | 2016-04-12 | Smith & Nephew, Inc. | Multi-modal shape memory polymers |
US20110035017A1 (en) * | 2007-09-25 | 2011-02-10 | Depuy Products, Inc. | Prosthesis with cut-off pegs and surgical method |
US9278003B2 (en) | 2007-09-25 | 2016-03-08 | Depuy (Ireland) | Prosthesis for cementless fixation |
US9398956B2 (en) | 2007-09-25 | 2016-07-26 | Depuy (Ireland) | Fixed-bearing knee prosthesis having interchangeable components |
US8632600B2 (en) | 2007-09-25 | 2014-01-21 | Depuy (Ireland) | Prosthesis with modular extensions |
US9204967B2 (en) | 2007-09-28 | 2015-12-08 | Depuy (Ireland) | Fixed-bearing knee prosthesis having interchangeable components |
US8128703B2 (en) | 2007-09-28 | 2012-03-06 | Depuy Products, Inc. | Fixed-bearing knee prosthesis having interchangeable components |
US20140207237A1 (en) * | 2008-02-01 | 2014-07-24 | DePuy Synthes Products, LLC | Porous Biocompatible Polymer Material and Methods |
US20160184483A1 (en) * | 2008-02-01 | 2016-06-30 | DePuy Synthes Products, Inc. | Porous biocompatible polymer material and methods |
US20110045087A1 (en) * | 2008-02-01 | 2011-02-24 | Synthes Gmbh | Porous biocompatible polymer material and methods |
US9308297B2 (en) * | 2008-02-01 | 2016-04-12 | DePuy Synthes Products, Inc. | Porous biocompatible polymer material and methods |
US10549014B2 (en) * | 2008-02-01 | 2020-02-04 | DePuy Synthes Products, Inc. | Porous biocompatible polymer material and methods |
US11679181B2 (en) * | 2008-02-01 | 2023-06-20 | DePuy Synthes Products, Inc. | Porous biocompatible polymer material and methods |
US8530560B2 (en) * | 2008-02-01 | 2013-09-10 | DePuy Synthes Products, LLC | Porous biocompatible polymer material and methods |
US8192498B2 (en) | 2008-06-30 | 2012-06-05 | Depuy Products, Inc. | Posterior cructiate-retaining orthopaedic knee prosthesis having controlled condylar curvature |
US9168145B2 (en) | 2008-06-30 | 2015-10-27 | Depuy (Ireland) | Posterior stabilized orthopaedic knee prosthesis having controlled condylar curvature |
US9326864B2 (en) | 2008-06-30 | 2016-05-03 | Depuy (Ireland) | Orthopaedic knee prosthesis having controlled condylar curvature |
US10265180B2 (en) | 2008-06-30 | 2019-04-23 | Depuy Ireland Unlimited Company | Orthopaedic knee prosthesis having controlled condylar curvature |
US11369478B2 (en) | 2008-06-30 | 2022-06-28 | Depuy Ireland Unlimited Company | Orthopaedic knee prosthesis having controlled condylar curvature |
US10179051B2 (en) | 2008-06-30 | 2019-01-15 | Depuy Ireland Unlimited Company | Orthopaedic knee prosthesis having controlled condylar curvature |
US9452053B2 (en) | 2008-06-30 | 2016-09-27 | Depuy (Ireland) | Orthopaedic knee prosthesis having controlled condylar curvature |
US10543098B2 (en) | 2008-06-30 | 2020-01-28 | Depuy Ireland Unlimited Company | Orthopaedic femoral component having controlled condylar curvature |
US9220601B2 (en) | 2008-06-30 | 2015-12-29 | Depuy (Ireland) | Orthopaedic femoral component having controlled condylar curvature |
US9204968B2 (en) | 2008-06-30 | 2015-12-08 | Depuy (Ireland) | Posterior stabilized orthopaedic prosthesis |
US8236061B2 (en) | 2008-06-30 | 2012-08-07 | Depuy Products, Inc. | Orthopaedic knee prosthesis having controlled condylar curvature |
US11337823B2 (en) | 2008-06-30 | 2022-05-24 | Depuy Ireland Unlimited Company | Orthopaedic femoral component having controlled condylar curvature |
US9539099B2 (en) | 2008-06-30 | 2017-01-10 | Depuy Ireland Unlimited Company | Orthopaedic knee prosthesis having controlled condylar curvature |
US8206451B2 (en) | 2008-06-30 | 2012-06-26 | Depuy Products, Inc. | Posterior stabilized orthopaedic prosthesis |
US10729551B2 (en) | 2008-06-30 | 2020-08-04 | Depuy Ireland Unlimited Company | Orthopaedic knee prosthesis having controlled condylar curvature |
US8734522B2 (en) | 2008-06-30 | 2014-05-27 | Depuy (Ireland) | Posterior stabilized orthopaedic prosthesis |
US8784496B2 (en) | 2008-06-30 | 2014-07-22 | Depuy (Ireland) | Orthopaedic knee prosthesis having controlled condylar curvature |
US8187335B2 (en) | 2008-06-30 | 2012-05-29 | Depuy Products, Inc. | Posterior stabilized orthopaedic knee prosthesis having controlled condylar curvature |
US10849760B2 (en) | 2008-06-30 | 2020-12-01 | Depuy Ireland Unlimited Company | Orthopaedic knee prosthesis having controlled condylar curvature |
US8795380B2 (en) | 2008-06-30 | 2014-08-05 | Depuy (Ireland) | Orthopaedic knee prosthesis having controlled condylar curvature |
US9937049B2 (en) | 2008-06-30 | 2018-04-10 | Depuy Ireland Unlimited Company | Orthopaedic knee prosthesis having controlled condylar curvature |
US8828086B2 (en) | 2008-06-30 | 2014-09-09 | Depuy (Ireland) | Orthopaedic femoral component having controlled condylar curvature |
US8834575B2 (en) | 2008-06-30 | 2014-09-16 | Depuy (Ireland) | Posterior stabilized orthopaedic knee prosthesis having controlled condylar curvature |
US9931216B2 (en) | 2008-06-30 | 2018-04-03 | Depuy Ireland Unlimited Company | Orthopaedic femoral component having controlled condylar curvature |
US9119723B2 (en) | 2008-06-30 | 2015-09-01 | Depuy (Ireland) | Posterior stabilized orthopaedic prosthesis assembly |
US11730602B2 (en) | 2008-06-30 | 2023-08-22 | Depuy Ireland Unlimited Company | Orthopaedic knee prosthesis having controlled condylar curvature |
US20110144752A1 (en) * | 2008-08-14 | 2011-06-16 | Defelice Scott F | Customized implants for bone replacement |
US10143555B2 (en) | 2008-08-14 | 2018-12-04 | Oxford Performance Materials, Llc | Customized implants for bone replacement |
US11517444B2 (en) | 2008-11-07 | 2022-12-06 | DePuy Synthes Products, Inc. | Zero-profile interbody spacer and coupled plate assembly |
US11612492B2 (en) * | 2008-11-07 | 2023-03-28 | DePuy Synthes Products, Inc. | Zero-profile interbody spacer and coupled plate assembly |
WO2010091223A1 (en) * | 2009-02-06 | 2010-08-12 | David Cheung | Biphasic collagen membrane or capsule for guided tissue regeneration |
US9833544B2 (en) | 2009-02-06 | 2017-12-05 | Osseous Technologies Of America | Biphasic collagen membrane or capsule for guided tissue regeneration |
US20100256758A1 (en) * | 2009-04-02 | 2010-10-07 | Synvasive Technology, Inc. | Monolithic orthopedic implant with an articular finished surface |
EP2413844A4 (en) * | 2009-04-02 | 2014-04-23 | Synvasive Technology Inc | Monolithic orthopedic implant with an articular finished surface |
EP2413844A1 (en) * | 2009-04-02 | 2012-02-08 | Synvasive Technology, Inc. | Monolithic orthopedic implant with an articular finished surface |
US20100255053A1 (en) * | 2009-04-03 | 2010-10-07 | Warsaw Orthopedic, Inc. | Medical implant with bioactive material and method of making the medical implant |
US8609127B2 (en) * | 2009-04-03 | 2013-12-17 | Warsaw Orthopedic, Inc. | Medical implant with bioactive material and method of making the medical implant |
CN102387822A (en) * | 2009-04-03 | 2012-03-21 | 华沙整形外科股份有限公司 | Medical implant with bioactive material and method of making the medical implant |
WO2010115132A3 (en) * | 2009-04-03 | 2011-01-06 | Warsaw Orthopedic, Inc. | Medical implant with bioactive material and method of making the medical implant |
US20100262224A1 (en) * | 2009-04-13 | 2010-10-14 | Kleiner Lothar W | Stent Made From An Ultra High Molecular Weight Bioabsorbable Polymer With High Fatigue And Fracture Resistance |
US9492587B2 (en) * | 2009-04-13 | 2016-11-15 | Abbott Cardiovascular Systems Inc. | Stent made from an ultra high molecular weight bioabsorbable polymer with high fatigue and fracture resistance |
US20100262244A1 (en) * | 2009-04-14 | 2010-10-14 | Warsaw Orthopedic, Inc. | Metal Coated Implant |
US10933172B2 (en) | 2009-07-24 | 2021-03-02 | Warsaw Orthopedic, Inc. | Implantable medical devices |
US20110022180A1 (en) * | 2009-07-24 | 2011-01-27 | Warsaw Orthopedic, Inc. | Implantable medical devices |
US9399086B2 (en) | 2009-07-24 | 2016-07-26 | Warsaw Orthopedic, Inc | Implantable medical devices |
US20110029026A1 (en) * | 2009-07-28 | 2011-02-03 | Southwest Research Institute | Micro-Structure Particles For Load Bearing Bone Growth |
US9039784B2 (en) * | 2009-07-28 | 2015-05-26 | Southwest Research Institute | Micro-structure particles for load bearing bone growth |
EP2606857A1 (en) | 2009-10-30 | 2013-06-26 | DePuy Products, Inc. | Prosthesis with composite component |
US8715359B2 (en) | 2009-10-30 | 2014-05-06 | Depuy (Ireland) | Prosthesis for cemented fixation and method for making the prosthesis |
EP2319462A1 (en) | 2009-10-30 | 2011-05-11 | DePuy Products, Inc. | Prosthesis with composite component |
US9011547B2 (en) | 2010-01-21 | 2015-04-21 | Depuy (Ireland) | Knee prosthesis system |
KR101196062B1 (en) | 2010-05-03 | 2012-11-01 | 순천향대학교 산학협력단 | Method for preparing porous biphasic calciumphosphate granules |
WO2012045013A3 (en) * | 2010-10-01 | 2012-06-21 | Skeletal Kinetics, Llc | Porogen containing calcium phosphate cement compositions |
WO2012051420A2 (en) * | 2010-10-13 | 2012-04-19 | Cibor, Inc. | Synthetic bone grafts constructed from carbon foam materials |
US9339387B2 (en) | 2010-10-13 | 2016-05-17 | Cibor, Inc. | Synthetic bone grafts constructed from carbon foam materials |
WO2012051420A3 (en) * | 2010-10-13 | 2012-07-12 | Cibor, Inc. | Synthetic bone grafts constructed from carbon foam materials |
WO2012065068A1 (en) * | 2010-11-11 | 2012-05-18 | Zimmer, Inc. | Orthopedic implant with porous polymer bone contacting surface |
US8998987B2 (en) | 2010-11-11 | 2015-04-07 | Zimmer, Inc. | Orthopedic implant with porous polymer bone contacting surface |
US11458027B2 (en) | 2010-12-21 | 2022-10-04 | DePuy Synthes Products, Inc. | Intervertebral implants, systems, and methods of use |
US9119728B2 (en) | 2011-01-17 | 2015-09-01 | Cibor, Inc. | Reinforced carbon fiber/carbon foam intervertebral spine fusion device |
WO2012098378A1 (en) * | 2011-01-18 | 2012-07-26 | Invibio Limited | Polymeric materials |
WO2012110803A1 (en) * | 2011-02-14 | 2012-08-23 | Invibio Limited | Components incorporating bioactive material |
JP2012171357A (en) * | 2011-02-17 | 2012-09-10 | Evonik Degussa Gmbh | Method for manufacturing rod |
EP2489494A1 (en) * | 2011-02-17 | 2012-08-22 | Evonik Degussa GmbH | Method for manufacturing rods and their use as implants |
CN102642288A (en) * | 2011-02-17 | 2012-08-22 | 赢创德固赛有限公司 | Method for manufacturing rods and their use as implants |
RU2598851C2 (en) * | 2011-02-17 | 2016-09-27 | Эвоник Дегусса Гмбх | Rod manufacturing method and use thereof |
US9603969B2 (en) * | 2011-08-30 | 2017-03-28 | Kyoto University | Porous scaffold material, and method for producing same |
US20140221615A1 (en) * | 2011-08-30 | 2014-08-07 | Kyoto University | Porous scaffold material, and method for producing same |
US20130085590A1 (en) * | 2011-10-03 | 2013-04-04 | Jason A. Bryan | Synthetic bone model and method for providing same |
CN103959359A (en) * | 2011-10-03 | 2014-07-30 | 克利夫兰临床医学基金会 | Synthetic bone model and method for providing same |
WO2013079655A3 (en) * | 2011-12-01 | 2014-01-09 | Technische Universität Hamburg-Harburg | Method for producing a composite material, the composite material and the use of the composite material for producing specific products |
US11872136B2 (en) | 2012-01-17 | 2024-01-16 | KYOCERA Medical Technologies, Inc. | Surgical implant devices incorporating porous surfaces and associated method of manufacture |
WO2013181375A1 (en) * | 2012-05-30 | 2013-12-05 | New York University | Tissue repair devices and scaffolds |
AU2013267381B2 (en) * | 2012-05-30 | 2016-03-31 | New York University | Tissue repair devices and scaffolds |
US10945845B2 (en) | 2012-05-30 | 2021-03-16 | New York University | Tissue repair devices and scaffolds |
EP2854886A4 (en) * | 2012-05-30 | 2016-03-23 | Univ New York | Tissue repair devices and scaffolds |
US20150150681A1 (en) * | 2012-05-30 | 2015-06-04 | John L. Ricci | Tissue repair devices and scaffolds |
US10792397B2 (en) | 2012-06-11 | 2020-10-06 | Globus Medical, Inc. | Bioactive bone graft substitutes |
US10207027B2 (en) | 2012-06-11 | 2019-02-19 | Globus Medical, Inc. | Bioactive bone graft substitutes |
US20150018956A1 (en) * | 2012-06-21 | 2015-01-15 | Renovis Surgical, Inc. | Surgical implant devices incorporating porous surfaces |
US10765530B2 (en) * | 2012-06-21 | 2020-09-08 | Renovis Surgical Technologies, Inc. | Surgical implant devices incorporating porous surfaces |
CN102727937A (en) * | 2012-06-28 | 2012-10-17 | 哈尔滨工程大学 | Biodegradable zinc (or zinc alloy) and porous biphase calcium phosphate composite material and preparation method thereof |
US11780175B2 (en) | 2012-08-21 | 2023-10-10 | Nuvasive, Inc. | Systems and methods for making porous films, fibers, spheres, and other articles |
US20230132015A1 (en) * | 2013-03-07 | 2023-04-27 | Howmedica Osteonics Corp. | Partially Porous Tibial Component |
WO2014153127A1 (en) * | 2013-03-14 | 2014-09-25 | Skeletal Kinetics, Llc | Calcium phosphate cement compositions that set into high strength porous structures |
EP3024419A4 (en) * | 2013-07-24 | 2017-03-08 | Renovis Surgical Technologies Inc. | Surgical implant devices incorporating porous surfaces |
WO2015013479A2 (en) | 2013-07-24 | 2015-01-29 | Renovis Surgical Technologies, Inc. | Surgical implant devices incorporating porous surfaces |
US9295565B2 (en) | 2013-10-18 | 2016-03-29 | Spine Wave, Inc. | Method of expanding an intradiscal space and providing an osteoconductive path during expansion |
US10226883B2 (en) | 2014-06-26 | 2019-03-12 | Vertera, Inc. | Mold and process for producing porous devices |
US10786344B2 (en) | 2014-06-26 | 2020-09-29 | Vertera, Inc. | Porous devices and processes for producing same |
US11672637B2 (en) | 2014-06-26 | 2023-06-13 | Nuvasive, Inc. | Porous devices and processes for producing same |
US11090843B2 (en) | 2014-06-26 | 2021-08-17 | Vertera, Inc. | Method for producing porous devices |
US11772306B2 (en) | 2014-06-26 | 2023-10-03 | Nuvasive, Inc. | Method for producing porous devices |
US11298217B2 (en) | 2014-06-26 | 2022-04-12 | Vertera, Inc. | Porous devices and processes for producing same |
US10405962B2 (en) | 2014-06-26 | 2019-09-10 | Vertera, Inc. | Porous devices and methods of producing the same |
US10507606B2 (en) | 2014-06-26 | 2019-12-17 | Vertera, Inc. | Mold and process for producing porous devices |
US20170021054A1 (en) * | 2014-10-14 | 2017-01-26 | Lynch Samuel E | Compositions for treating wounds |
US11540927B2 (en) | 2014-10-22 | 2023-01-03 | DePuy Synthes Products, Inc. | Intervertebral implants, systems, and methods of use |
WO2016105286A1 (en) * | 2014-12-25 | 2016-06-30 | Hasirci Vasif Nejat | A new prosthesis material developed for use in the treatment of cervical and lumbar disc hernia |
WO2016108769A1 (en) * | 2014-12-29 | 2016-07-07 | Hasirci Vasif Nejat | Craniofacial implants |
EP3256079B1 (en) * | 2015-02-13 | 2023-05-03 | Eit Emerging Implant Technologies GmbH | Spinal implants with engineered cellular structure and internal imaging markers |
USD944990S1 (en) | 2015-06-23 | 2022-03-01 | Vertera, Inc. | Cervical interbody fusion device |
FR3039988A1 (en) * | 2015-08-11 | 2017-02-17 | Abdelmadjid Djemai | EXPANDED SPRING INTERSOMATIC CAGE, DOUBLE-STRUCKED DOUBLE STRUCK HINGE AND METHOD FOR MANUFACTURING THE SAME |
CN105233335A (en) * | 2015-11-06 | 2016-01-13 | 四川大学 | Porous polyaryletherketone material with bioactivity, and preparation method and application thereof |
US20170165790A1 (en) * | 2015-12-15 | 2017-06-15 | Howmedica Osteonics Corp. | Porous structures produced by additive layer manufacturing |
US10596660B2 (en) * | 2015-12-15 | 2020-03-24 | Howmedica Osteonics Corp. | Porous structures produced by additive layer manufacturing |
CN106913406A (en) * | 2015-12-25 | 2017-07-04 | 苏州微创脊柱创伤医疗科技有限公司 | A kind of spinal fusion device and preparation method thereof |
CN105559950A (en) * | 2016-02-03 | 2016-05-11 | 北京纳通科技集团有限公司 | Fusion cage |
JP7077234B2 (en) | 2016-04-19 | 2022-05-30 | カール ライビンガー メディツィンテヒニーク ゲーエムベーハー ウント コーカーゲー | Hybrid implant made of composite material |
JP2019513495A (en) * | 2016-04-19 | 2019-05-30 | カール ライビンガー メディツィンテヒニーク ゲーエムベーハー ウント コーカーゲーKarl Leibinger Medizintechnik Gmbh & Co. Kg | Hybrid implant consisting of composite material |
US11103620B2 (en) | 2016-04-19 | 2021-08-31 | Karl Leibinger Medizintechnik Gmbh & Co. Kg | Hybrid implant made of a composite material |
US10660764B2 (en) * | 2016-06-14 | 2020-05-26 | The Trustees Of The Stevens Institute Of Technology | Load sustaining bone scaffolds for spinal fusion utilizing hyperbolic struts and translational strength gradients |
US11524094B2 (en) * | 2016-09-19 | 2022-12-13 | Biomendex Oy | Porous composite material |
CN110418624A (en) * | 2016-10-25 | 2019-11-05 | 肌肉骨骼科学教育研究所有限公司 | Implantation material with multilayer bone engagement screen work |
CN110418624B (en) * | 2016-10-25 | 2022-01-28 | 肌肉骨骼科学教育研究所有限公司 | Implant with multi-layered osteosynthesis lattice |
CN106344221A (en) * | 2016-10-26 | 2017-01-25 | 四川大学 | Bonelike porous biomechanical bionic designed spinal fusion device and preparation method and use thereof |
CN106435544A (en) * | 2016-11-09 | 2017-02-22 | 北京科技大学 | Method for preparing nano-hydroxyapatite gradient coating on titanium alloy matrix |
US11685113B2 (en) * | 2017-03-06 | 2023-06-27 | Katholieke Universiteit Leuven | 3D printing of porous liquid handling device |
US11364122B2 (en) | 2017-03-10 | 2022-06-21 | Vestlandets Innovasjonsselskap As | Tissue engineering scaffolds |
EP3592297B1 (en) * | 2017-03-10 | 2023-08-16 | Vestlandets Innovasjonsselskap AS | Tissue engineering scaffolds |
US20180296343A1 (en) * | 2017-04-18 | 2018-10-18 | Warsaw Orthopedic, Inc. | 3-d printing of porous implants |
US10064726B1 (en) * | 2017-04-18 | 2018-09-04 | Warsaw Orthopedic, Inc. | 3D printing of mesh implants for bone delivery |
US11628517B2 (en) | 2017-06-15 | 2023-04-18 | Howmedica Osteonics Corp. | Porous structures produced by additive layer manufacturing |
US10888362B2 (en) | 2017-11-03 | 2021-01-12 | Howmedica Osteonics Corp. | Flexible construct for femoral reconstruction |
US11890041B2 (en) | 2017-11-03 | 2024-02-06 | Howmedica Osteonics Corp. | Flexible construct for femoral reconstruction |
KR20200104856A (en) * | 2017-11-14 | 2020-09-04 | 스노우플레이크 인코포레이티드 | Database metadata within an immutable repository |
KR102461943B1 (en) | 2017-11-14 | 2022-11-03 | 스노우플레이크 인코포레이티드 | Database metadata within the immutable repository |
CN108309517A (en) * | 2018-01-25 | 2018-07-24 | 中国人民解放军新疆军区总医院 | A kind of absorbable cervical fusion cage and preparation method thereof |
US10850442B1 (en) | 2018-03-02 | 2020-12-01 | Restor3D, Inc. | Medical devices and methods for producing the same |
US10183442B1 (en) | 2018-03-02 | 2019-01-22 | Additive Device, Inc. | Medical devices and methods for producing the same |
USD870890S1 (en) | 2018-03-02 | 2019-12-24 | Restor3D, Inc. | Spiral airway stent |
USD870889S1 (en) | 2018-03-02 | 2019-12-24 | Restor3D, Inc. | Cutout airway stent |
USD871577S1 (en) | 2018-03-02 | 2019-12-31 | Restor3D, Inc. | Studded airway stent |
USD870888S1 (en) | 2018-03-02 | 2019-12-24 | Restor3D, Inc. | Accordion airway stent |
US11364323B2 (en) * | 2018-09-17 | 2022-06-21 | Rejuvablast LLC | Combination grafts for tissue repair or regeneration applications |
US11607476B2 (en) | 2019-03-12 | 2023-03-21 | Happe Spine Llc | Implantable medical device with thermoplastic composite body and method for forming thermoplastic composite body |
US11911535B2 (en) | 2019-03-12 | 2024-02-27 | Happe Spine Llc | Implantable medical device with thermoplastic composite body and method for forming thermoplastic composite body |
US10889053B1 (en) | 2019-03-25 | 2021-01-12 | Restor3D, Inc. | Custom surgical devices and method for manufacturing the same |
USD1013875S1 (en) | 2020-01-08 | 2024-02-06 | Restor3D, Inc. | Spinal implant |
USD920515S1 (en) | 2020-01-08 | 2021-05-25 | Restor3D, Inc. | Spinal implant |
USD1013876S1 (en) | 2020-01-08 | 2024-02-06 | Restor3D, Inc. | Osteotomy wedge |
US11484413B1 (en) | 2020-01-08 | 2022-11-01 | Restor3D, Inc. | Sheet based triply periodic minimal surface implants for promoting osseointegration and methods for producing same |
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US20210177620A1 (en) | 2021-06-17 |
WO2008106625A2 (en) | 2008-09-04 |
US10945854B2 (en) | 2021-03-16 |
US20210015977A9 (en) | 2021-01-21 |
US20220062004A1 (en) | 2022-03-03 |
WO2008106625A3 (en) | 2009-12-30 |
US20140236299A1 (en) | 2014-08-21 |
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