CA2354065A1 - Implant with composite coating - Google Patents
Implant with composite coating Download PDFInfo
- Publication number
- CA2354065A1 CA2354065A1 CA002354065A CA2354065A CA2354065A1 CA 2354065 A1 CA2354065 A1 CA 2354065A1 CA 002354065 A CA002354065 A CA 002354065A CA 2354065 A CA2354065 A CA 2354065A CA 2354065 A1 CA2354065 A1 CA 2354065A1
- Authority
- CA
- Canada
- Prior art keywords
- implant
- structured surface
- coating
- biocompatible
- substrate
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Abandoned
Links
Classifications
-
- 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
- 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
- A61F2/30767—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/28—Materials for coating prostheses
- A61L27/30—Inorganic materials
- A61L27/306—Other specific inorganic materials not covered by A61L27/303 - A61L27/32
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61P—SPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
- A61P19/00—Drugs for skeletal disorders
-
- 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
- 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
-
- 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
- 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
- A61F2/30965—Reinforcing the prosthesis by embedding particles or fibres during moulding or dipping
-
- 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
- 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
- A61F2/32—Joints for the hip
- A61F2/36—Femoral heads ; Femoral endoprostheses
-
- 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
- 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
- A61F2/32—Joints for the hip
- A61F2/36—Femoral heads ; Femoral endoprostheses
- A61F2/3662—Femoral shafts
-
- 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
- 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
- A61F2/32—Joints for the hip
- A61F2/36—Femoral heads ; Femoral endoprostheses
- A61F2/3662—Femoral shafts
- A61F2/367—Proximal or metaphyseal parts of shafts
-
- 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
- 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
- A61F2/38—Joints for elbows or knees
- A61F2/3859—Femoral components
-
- 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
- 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
- A61F2002/30001—Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
- A61F2002/30003—Material related properties of the prosthesis or of a coating on the prosthesis
- A61F2002/30004—Material related properties of the prosthesis or of a coating on the prosthesis the prosthesis being made from materials having different values of a given property at different locations within the same prosthesis
- A61F2002/30016—Material related properties of the prosthesis or of a coating on the prosthesis the prosthesis being made from materials having different values of a given property at different locations within the same prosthesis differing in hardness, e.g. Vickers, Shore, Brinell
-
- 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
- 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
- A61F2/30767—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth
- A61F2002/30906—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth shot- sand- or grit-blasted
-
- 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
- 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
- A61F2/30767—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth
- A61F2002/30925—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth etched
-
- 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
- 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
- A61F2/30767—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth
- A61F2002/30929—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth having at least two superposed coatings
-
- 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
- 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
- A61F2002/30968—Sintering
-
- 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
- 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
- A61F2002/3097—Designing or manufacturing processes using laser
-
- 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
- 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
- A61F2/32—Joints for the hip
- A61F2/36—Femoral heads ; Femoral endoprostheses
- A61F2/3609—Femoral heads or necks; Connections of endoprosthetic heads or necks to endoprosthetic femoral shafts
- A61F2002/3611—Heads or epiphyseal parts of femur
-
- 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
- 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
- A61F2/32—Joints for the hip
- A61F2/36—Femoral heads ; Femoral endoprostheses
- A61F2/3609—Femoral heads or necks; Connections of endoprosthetic heads or necks to endoprosthetic femoral shafts
- A61F2002/3625—Necks
-
- 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
- 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
- A61F2/32—Joints for the hip
- A61F2/36—Femoral heads ; Femoral endoprostheses
- A61F2/3609—Femoral heads or necks; Connections of endoprosthetic heads or necks to endoprosthetic femoral shafts
- A61F2002/3625—Necks
- A61F2002/3631—Necks with an integral complete or partial peripheral collar or bearing shoulder at its base
-
- 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
- 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
- A61F2/32—Joints for the hip
- A61F2/36—Femoral heads ; Femoral endoprostheses
- A61F2/3609—Femoral heads or necks; Connections of endoprosthetic heads or necks to endoprosthetic femoral shafts
- A61F2002/365—Connections of heads to necks
-
- 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
- A61F2250/0019—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 hardness, e.g. Vickers, Shore, Brinell
-
- 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
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00011—Metals or alloys
- A61F2310/00017—Iron- or Fe-based alloys, e.g. stainless steel
-
- 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
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00011—Metals or alloys
- A61F2310/00023—Titanium or titanium-based alloys, e.g. Ti-Ni alloys
-
- 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
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00011—Metals or alloys
- A61F2310/00029—Cobalt-based alloys, e.g. Co-Cr alloys or Vitallium
-
- 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
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00011—Metals or alloys
- A61F2310/00035—Other metals or alloys
- A61F2310/00131—Tantalum or Ta-based alloys
-
- 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
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00179—Ceramics or ceramic-like structures
-
- 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
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00389—The prosthesis being coated or covered with a particular material
- A61F2310/00395—Coating or prosthesis-covering structure made of metals or of alloys
- A61F2310/00407—Coating made of titanium or of Ti-based alloys
-
- 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
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00389—The prosthesis being coated or covered with a particular material
- A61F2310/00395—Coating or prosthesis-covering structure made of metals or of alloys
- A61F2310/00419—Other metals
- A61F2310/00485—Coating made of zirconium or Zr-based alloys
-
- 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
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00389—The prosthesis being coated or covered with a particular material
- A61F2310/00395—Coating or prosthesis-covering structure made of metals or of alloys
- A61F2310/00419—Other metals
- A61F2310/00491—Coating made of niobium or Nb-based alloys
-
- 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
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00389—The prosthesis being coated or covered with a particular material
- A61F2310/00395—Coating or prosthesis-covering structure made of metals or of alloys
- A61F2310/00419—Other metals
- A61F2310/00538—Coating made of hafnium or Hf-based alloys
-
- 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
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00389—The prosthesis being coated or covered with a particular material
- A61F2310/00395—Coating or prosthesis-covering structure made of metals or of alloys
- A61F2310/00419—Other metals
- A61F2310/00544—Coating made of tantalum or Ta-based alloys
-
- 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
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00389—The prosthesis being coated or covered with a particular material
- A61F2310/00574—Coating or prosthesis-covering structure made of carbon, e.g. of pyrocarbon
-
- 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
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00389—The prosthesis being coated or covered with a particular material
- A61F2310/00574—Coating or prosthesis-covering structure made of carbon, e.g. of pyrocarbon
- A61F2310/0058—Coating made of diamond or of diamond-like carbon DLC
-
- 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
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00389—The prosthesis being coated or covered with a particular material
- A61F2310/00592—Coating or prosthesis-covering structure made of ceramics or of ceramic-like compounds
- A61F2310/00796—Coating or prosthesis-covering structure made of a phosphorus-containing compound, e.g. hydroxy(l)apatite
-
- 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
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00389—The prosthesis being coated or covered with a particular material
- A61F2310/00976—Coating or prosthesis-covering structure made of proteins or of polypeptides, e.g. of bone morphogenic proteins BMP or of transforming growth factors TGF
Abstract
Systems and methods are described for implants with composite coatings to promote tissue in-growth and/or on-growth. An implant includes: a substrate; a structured surface formed on at least a portion of the substrate; and a biocompatible coating deposited on at least a fraction of the structured surface. The systems and methods provide advantages in that the implant has good biocompatibility while the biocompatible coating has good strength.</SD OAB>
Description
IMPLANT WITH COMPOSITE COATING
BACKGROUND OF THE INVENTION
1. Field of the Invention The invention relates generally to the field of in vivo implants. More particularly, preferred embodiments of the invention are directed to an orthopedic prosthesis having a composite coating to promote tissue in-growth and/or tissue on-growth.
BACKGROUND OF THE INVENTION
1. Field of the Invention The invention relates generally to the field of in vivo implants. More particularly, preferred embodiments of the invention are directed to an orthopedic prosthesis having a composite coating to promote tissue in-growth and/or tissue on-growth.
2. Discussion of the Related Art Prior art implants are known to those skilled in the art. For example, conventional implants are typically composed of stainless steel, cobalt-chrome, or titanium alloy.
A problem with this technology has been that the best substrate materials are not the best materials to be in contact with living tissue. Therefore, what is required is a solution that can provide a biocompatible coating on a substrate.
One approach in an attempt to solve the above-discussed problems involves simply coating an implant substrate with a biocompatible material. However, a disadvantage of this approach is that biocompatible materials are often soft or brittle.
Another disadvantage of this approach has been relatively high cost and/or technical complexity. Therefore, what is also needed is a solution that meets the above-discussed requirements in a more simple and cost effective manner.
Heretofore, the requirements of good substrate properties, and good coating properties referred to above have not been fully met in combination. What is needed is a solution that simultaneously addresses both of these requirements.
SUMMARY OF THE INVENTION
A primary object of the invention is to provide implants with a composite coating to promote tissue in-growth and/or tissue on-growth. Another primary object of the invention is to provide a composition that can used as the composite coating. Another primary object of the invention is to provide implants having a composite coating that is located only on surface areas of the implant that are to be fixed with tissue in-growth and/or on-growth for stability. Another primary object of the invention is to provide methods of making the orthopedic implant.
In accordance with these objects, there is a particular need for an implant with a composite coating. Thus, it is rendered possible to simultaneously satisfy the above-discussed requirements of good substrate properties and good biocompatible coating properties, which, in the case of the prior art, are mutually contradicting and cannot be easily satisfied.
A first aspect of the invention is implemented in an embodiment that is based on an implant, comprising: a substrate; a structured surface defined by at least a portion of said substrate; and a biocompatible coating deposited on at least a fraction of said structured surface. A second aspect of the invention is implemented in an embodiment that is based on a composition for an implant, comprising: a biocompatible material coated on a structured surface defined by a substrate. A third aspect of the invention is implemented in an embodiment that is based on an implant, comprising: a substrate; a structured surface defined by a portion of said substrate; and a biocompatible coating deposited on at least a fraction of said structured surface, wherein said portion of said substrate is to be fixed with tissue in-growth and/or on-growth for stability. A fourth aspect of the invention is implemented in an embodiment that is based on a method of forming a composite coating, comprising:
depositing a biocompatible coating on a structured surface defined by at least a portion of a surface area of a substrate.
These, and other, objects and aspects of the invention will be better appreciated and understood when considered in conjunction with the following description and the accompanying drawings. It should be understood, however, that the following description, while indicating preferred embodiments of the invention and numerous specific details thereof, is given by way of illustration and not of limitation. Many changes and modifications may be made within the scope of the invention without departing from the spirit thereof, and the invention includes all such modifications.
BRIEF DESCRIPTION OF THE DRAWINGS
A clear conception of the advantages and features constituting the invention, and of the components and operation of model systems provided with the invention, will become more readily apparent by referring to the exemplary, and therefore nonlimiting, embodiments illustrated in the drawings accompanying and forming a part of this specification, wherein like reference characters (if they occur in more than one view) designate the same parts. It should be noted that the features illustrated in the drawings are not necessarily drawn to scale.
FIG. 1 illustrates a schematic perspective view of an orthopedic implant, representing an embodiment of the invention.
FIG. 2 illustrates a schematic perspective view of an orthopedic implant, representing an embodiment of the invention.
FIGS. 3a-3b illustrate micrograph views of a physical vapor deposited coating of titanium on a structured surface of cobalt-chrome alloy, representing an embodiment of the invention.
FIG. 4 illustrates a schematic view of a coating on a porous structured surface, representing an embodiment of the invention.
1 S FIG. 5 illustrates a schematic view of an apparatus and process for coating a structured surface, representing an embodiment of the invention.
FIGS. 6a-6b illustrate scanning electron micrographs of a biocompatible coating on CoCrMo particles after an electrochemical test, representing an embodiment of the invention.
FIGS. 7a-7d illustrate scanning electron micrographs of CoCrMo particles without the biocompatible coating after the electrochemical test, representing an embodiment of the invention.
FIGS. 8a-8b illustrate SEM of CoCrMo particles without coating before test, representing an embodiment of the invention.
DESCRIPTION OF PREFERRED EMBODIMENTS
The invention and the various features and advantageous details thereof are explained more fully with reference to the nonlimiting embodiments that are illustrated in the accompanying drawings and detailed in the following description. Descriptions of well known components and processing techniques are omitted so as not to unnecessarily obscure the invention in detail.
A problem with this technology has been that the best substrate materials are not the best materials to be in contact with living tissue. Therefore, what is required is a solution that can provide a biocompatible coating on a substrate.
One approach in an attempt to solve the above-discussed problems involves simply coating an implant substrate with a biocompatible material. However, a disadvantage of this approach is that biocompatible materials are often soft or brittle.
Another disadvantage of this approach has been relatively high cost and/or technical complexity. Therefore, what is also needed is a solution that meets the above-discussed requirements in a more simple and cost effective manner.
Heretofore, the requirements of good substrate properties, and good coating properties referred to above have not been fully met in combination. What is needed is a solution that simultaneously addresses both of these requirements.
SUMMARY OF THE INVENTION
A primary object of the invention is to provide implants with a composite coating to promote tissue in-growth and/or tissue on-growth. Another primary object of the invention is to provide a composition that can used as the composite coating. Another primary object of the invention is to provide implants having a composite coating that is located only on surface areas of the implant that are to be fixed with tissue in-growth and/or on-growth for stability. Another primary object of the invention is to provide methods of making the orthopedic implant.
In accordance with these objects, there is a particular need for an implant with a composite coating. Thus, it is rendered possible to simultaneously satisfy the above-discussed requirements of good substrate properties and good biocompatible coating properties, which, in the case of the prior art, are mutually contradicting and cannot be easily satisfied.
A first aspect of the invention is implemented in an embodiment that is based on an implant, comprising: a substrate; a structured surface defined by at least a portion of said substrate; and a biocompatible coating deposited on at least a fraction of said structured surface. A second aspect of the invention is implemented in an embodiment that is based on a composition for an implant, comprising: a biocompatible material coated on a structured surface defined by a substrate. A third aspect of the invention is implemented in an embodiment that is based on an implant, comprising: a substrate; a structured surface defined by a portion of said substrate; and a biocompatible coating deposited on at least a fraction of said structured surface, wherein said portion of said substrate is to be fixed with tissue in-growth and/or on-growth for stability. A fourth aspect of the invention is implemented in an embodiment that is based on a method of forming a composite coating, comprising:
depositing a biocompatible coating on a structured surface defined by at least a portion of a surface area of a substrate.
These, and other, objects and aspects of the invention will be better appreciated and understood when considered in conjunction with the following description and the accompanying drawings. It should be understood, however, that the following description, while indicating preferred embodiments of the invention and numerous specific details thereof, is given by way of illustration and not of limitation. Many changes and modifications may be made within the scope of the invention without departing from the spirit thereof, and the invention includes all such modifications.
BRIEF DESCRIPTION OF THE DRAWINGS
A clear conception of the advantages and features constituting the invention, and of the components and operation of model systems provided with the invention, will become more readily apparent by referring to the exemplary, and therefore nonlimiting, embodiments illustrated in the drawings accompanying and forming a part of this specification, wherein like reference characters (if they occur in more than one view) designate the same parts. It should be noted that the features illustrated in the drawings are not necessarily drawn to scale.
FIG. 1 illustrates a schematic perspective view of an orthopedic implant, representing an embodiment of the invention.
FIG. 2 illustrates a schematic perspective view of an orthopedic implant, representing an embodiment of the invention.
FIGS. 3a-3b illustrate micrograph views of a physical vapor deposited coating of titanium on a structured surface of cobalt-chrome alloy, representing an embodiment of the invention.
FIG. 4 illustrates a schematic view of a coating on a porous structured surface, representing an embodiment of the invention.
1 S FIG. 5 illustrates a schematic view of an apparatus and process for coating a structured surface, representing an embodiment of the invention.
FIGS. 6a-6b illustrate scanning electron micrographs of a biocompatible coating on CoCrMo particles after an electrochemical test, representing an embodiment of the invention.
FIGS. 7a-7d illustrate scanning electron micrographs of CoCrMo particles without the biocompatible coating after the electrochemical test, representing an embodiment of the invention.
FIGS. 8a-8b illustrate SEM of CoCrMo particles without coating before test, representing an embodiment of the invention.
DESCRIPTION OF PREFERRED EMBODIMENTS
The invention and the various features and advantageous details thereof are explained more fully with reference to the nonlimiting embodiments that are illustrated in the accompanying drawings and detailed in the following description. Descriptions of well known components and processing techniques are omitted so as not to unnecessarily obscure the invention in detail.
The context of the invention is providing an implant to be positioned in vivo during surgery, especially orthopedic surgery to replace a joint, such as, for example, a knee joint or a hip joint. Thus, the implant can be used in a method for orthopedic surgery that includes surgically positioning the implant within a vertebrate in need thereof. If bone growth is facilitated, the implant can be termed part of an osteoconductive process that includes contacting a bone under in vivo conditions with the implant:
Referring to the drawings, a detailed description of preferred embodiments of the invention is provided with respect to FIGS. 1 through 5. The invention is not limited to the specific embodiments illustrated in FIGS. 1-5.
Referring now to FIG. 1, a component 110 of an artificial knee joint is depicted. The component 110 includes a bearing surface 120 and a tissue fixation surface 130. The bearing surface 120 is for sliding. The tissue fixation surface 130 is for tissue in-growth and/or tissue on-growth. The tissue fixation surface 130 can be a coating that is deposited on at least a fraction of a structured surface that is defined by, or formed on, or composed by at least a portion of a substrate.
The substrate can be composed, or formed, of, for example, carbon-composite, stainless steel, cobalt-chromium, titanium alloy, tantalum, and/or ceramic, and combinations thereof. The structured surface can be defined by; or composed of, or formed of a material that includes a plurality of particles that are sintered together to form a continuous porous phase. Alternatively, the structured surface can be prepared by at least one method selected from the group consisting of flame spraying, acid etching, grit blasting, casting-in, forging-in, laser texturing, and micromachining.
The coating should be a biocompatible coating. The biocompatible coating can include one, or more, of titanium, tantalum, carbon, calcium phosphate, zirconium, niobium, hafnium, hydroxyapatite, tissue in-growth and/or on-growth facilitating proteins, and combinations thereof. If carbon is used, it can optionally be diamond-like carbon, pyrolytic carbon, amorphous diamond-like carbon, and combinations thereof.
It can be advantageous that the coating be more biocompatible than the structured surface. Similarly, it can be advantageous that the coating be more biocompatible than the substrate. One aspect, albeit optional, of biocompatibility is softness. It can be advantageous that the coating be softer than the structured surface.
Similarly, it can be advantageous that the coating be softer than the substrate. Although the preferred embodiment shown in FIG. 1 includes a coating located on specific portions of the substrate, it is within the level of ordinary skill in the art after having knowledge of the invention disclosed herein to coat any surfaces) of the substrate.
Referring now to FIG. 2, an artificial hip joint is depicted. The hip joint includes a 5 femoral head 210 and distal portion 220. The femoral head 210 includes a joint motion surface 230 for bearing and sliding. The distal portion 220 includes a taper connection 240, a tissue fixation surface 250, and a distal stem 260. The tissue fixation surface 250 can be a coating that is deposited on at least a fraction of a structured surface that is defined by, or formed on, or composed by at least a portion of a substrate. As noted above, the coating should be a biocompatible coating. The biocompatible coating can include mufti-layers.
These mufti-layers can be nano-layers. Although the preferred embodiment shown in FIG. 2 includes the coating located on a specific portion of the substrate, it is within the level of ordinary skill in the art after having knowledge of the invention disclosed herein to coat any surfaces) of the substrate.
Referring now to FIGS. 3a-3b, two images of a structured surface coated according to the invention are depicted. FIGS. 3a-3b are two images of the same sample acquired at different locations. FIG. 3a illustrates a coating 310 on a structured surface 320 at an outermost location. The structure surface 320 is defined by a sintered layer having interconnected porosity. The thickness of the coating 310 is approximately 10.78 microns at this outermost location of the structured surface 320. FIG. 3b illustrates the coating 310 on the structured surface 320 at an innermost location. The thickness of the coating is approximately 2.0 microns at this innermost location of the structured surface 320.
Still referring to FIGS. 3a-3b, a coating 310 is adhered to a structured surface 320. In this particular embodiment, the coating 310 is composed of a first material that includes titanium. The coating is preferably a biocompatible coating. In this particular embodiment, the structured surface 320 is defined by a second material that includes cobalt and chrome.
In this particular embodiment, the structured surface was conditioned by cathodic arc ion plating of titanium before the coating 310 was deposited using the same apparatus used to effect the ion plating. In this particular embodiment, the average thickness of the coating 310 is approximately 10.78 microns. If the structured surface 320 includes crevices and/or undercuts 330, the biocompatible material that composes the coating 310 can coat the crevices and/or undercuts 330 in the structured surface.
Referring to the drawings, a detailed description of preferred embodiments of the invention is provided with respect to FIGS. 1 through 5. The invention is not limited to the specific embodiments illustrated in FIGS. 1-5.
Referring now to FIG. 1, a component 110 of an artificial knee joint is depicted. The component 110 includes a bearing surface 120 and a tissue fixation surface 130. The bearing surface 120 is for sliding. The tissue fixation surface 130 is for tissue in-growth and/or tissue on-growth. The tissue fixation surface 130 can be a coating that is deposited on at least a fraction of a structured surface that is defined by, or formed on, or composed by at least a portion of a substrate.
The substrate can be composed, or formed, of, for example, carbon-composite, stainless steel, cobalt-chromium, titanium alloy, tantalum, and/or ceramic, and combinations thereof. The structured surface can be defined by; or composed of, or formed of a material that includes a plurality of particles that are sintered together to form a continuous porous phase. Alternatively, the structured surface can be prepared by at least one method selected from the group consisting of flame spraying, acid etching, grit blasting, casting-in, forging-in, laser texturing, and micromachining.
The coating should be a biocompatible coating. The biocompatible coating can include one, or more, of titanium, tantalum, carbon, calcium phosphate, zirconium, niobium, hafnium, hydroxyapatite, tissue in-growth and/or on-growth facilitating proteins, and combinations thereof. If carbon is used, it can optionally be diamond-like carbon, pyrolytic carbon, amorphous diamond-like carbon, and combinations thereof.
It can be advantageous that the coating be more biocompatible than the structured surface. Similarly, it can be advantageous that the coating be more biocompatible than the substrate. One aspect, albeit optional, of biocompatibility is softness. It can be advantageous that the coating be softer than the structured surface.
Similarly, it can be advantageous that the coating be softer than the substrate. Although the preferred embodiment shown in FIG. 1 includes a coating located on specific portions of the substrate, it is within the level of ordinary skill in the art after having knowledge of the invention disclosed herein to coat any surfaces) of the substrate.
Referring now to FIG. 2, an artificial hip joint is depicted. The hip joint includes a 5 femoral head 210 and distal portion 220. The femoral head 210 includes a joint motion surface 230 for bearing and sliding. The distal portion 220 includes a taper connection 240, a tissue fixation surface 250, and a distal stem 260. The tissue fixation surface 250 can be a coating that is deposited on at least a fraction of a structured surface that is defined by, or formed on, or composed by at least a portion of a substrate. As noted above, the coating should be a biocompatible coating. The biocompatible coating can include mufti-layers.
These mufti-layers can be nano-layers. Although the preferred embodiment shown in FIG. 2 includes the coating located on a specific portion of the substrate, it is within the level of ordinary skill in the art after having knowledge of the invention disclosed herein to coat any surfaces) of the substrate.
Referring now to FIGS. 3a-3b, two images of a structured surface coated according to the invention are depicted. FIGS. 3a-3b are two images of the same sample acquired at different locations. FIG. 3a illustrates a coating 310 on a structured surface 320 at an outermost location. The structure surface 320 is defined by a sintered layer having interconnected porosity. The thickness of the coating 310 is approximately 10.78 microns at this outermost location of the structured surface 320. FIG. 3b illustrates the coating 310 on the structured surface 320 at an innermost location. The thickness of the coating is approximately 2.0 microns at this innermost location of the structured surface 320.
Still referring to FIGS. 3a-3b, a coating 310 is adhered to a structured surface 320. In this particular embodiment, the coating 310 is composed of a first material that includes titanium. The coating is preferably a biocompatible coating. In this particular embodiment, the structured surface 320 is defined by a second material that includes cobalt and chrome.
In this particular embodiment, the structured surface was conditioned by cathodic arc ion plating of titanium before the coating 310 was deposited using the same apparatus used to effect the ion plating. In this particular embodiment, the average thickness of the coating 310 is approximately 10.78 microns. If the structured surface 320 includes crevices and/or undercuts 330, the biocompatible material that composes the coating 310 can coat the crevices and/or undercuts 330 in the structured surface.
It can be advantageous if the biocompatible material conforms to the crevices and/or undercuts and thereby defines a textured (e.g., rough) topology at the upper surface of the biocompatible material. This is advantageous because such a topology gives tissue a better hold via tissue in-growth and/or on-growth. Further, if there are pores in and/or beneath the structured surface the, biocompatible material can coat the pores. It can be advantageous if the biocompatible material coats interconnected pores located beneath the structured surface and thereby define voids (pores) and/or interconnected pores in which tissue in-growth and/or on-growth can occur.
The effect of cathodic arc ion plating with a high bias voltage is to cause an intermixing of titanium into the cobalt-chrome substrate due to high ion energies. It can be appreciated that there is an inter-penetration of the coating material into the structured surface material between the interface and the bulk of the material that composes the structured surface. Specifically, the amount of coating material that composes the substrate that defines the structured surface decreases as the depth from the interface increases. When the bias voltage is increased, the inter-penetration depth increases. The depth of this intermixing can range from approximately 0.5 nm to approximately 500 nm, preferably approximately 50 nm to approximately 100 nm. When the bias voltage is sufficient, substantial inter-penetration occurs. This result is advantageous because the inter-penetration improves the adhesion of the coating to the structured surface, thereby minimizing flaking, peeling, and other disruptions of the coating. This is very important for at least the following two reasons. First, the coating will be subject to tissue in-growth and/or on-growth and, therefore, can be subject to dynamic loading from adjacent tissue structures, such as, for example, bones. By improving the adhesion, the coating is better able to withstand loading. Second, the implant may be expected to remain in vivo for many years and it is highly desirable that all of the implant remain fixed in place. By improving the adhesion of the coating to the structured surface, the long term stability of the coating is enhanced.
Referring now to FIG. 4, a porous structured surface 410 with a coating 420 is depicted. The coating 420 includes titanium and can be deposited via physical vapor deposition with a gas, preferably an inert gas, such as, for example, argon and/or helium. It can be advantageous to use argon as the gas because it is inert and has a relatively high atomic weight. Significantly, the coating 420 covers portions of a structured surface defined 7 PCT/US99/084~6 by an interconnected pore 430 that is hidden from line-of sight deposition (i.e., the pore 430 cannot be seen from the point of view of the deposition source). The structured surface is also defined by a plurality of particles covering a substrate 440 (i.e., the structured surface is defined by the interface between the substrate 440 and the plurality of particles).
Nevertheless, the surface defined by the interconnected pore 430 is coated and provides an area for tissue in-growth and/or on-growth because an inert gas is present in the deposition chamber while the coating 420 is being applied. Although the preferred embodiment shown in FIG. 4 includes the coating of the surface defined by the interconnected pore 430, it is within the level of ordinary skill in the art after having knowledge of the invention disclosed herein to coat any undercut, or vertical, or line-of sight hidden surface area.
FIG. 4 demonstrates substantially improved results that are unexpected.
Specifically, the coating of internal pores demonstrates the significant unexpected advantageous result that when an inert gas is present during the deposition process, the coating is deposited on line-of sight hidden surfaces (e.g. interconnected pores). It can be appreciated that the structured surface 410 is coated because the exterior of the particles appears rough.
Normally, in the case of an uncoated particle, the perimeter would be smooth and more nearly circular. The roughness is the coating. This result is advantageous because it significantly improves adhesion of the surrounding tissue to the implant.
Adhesion is significantly improved because tissue on-growth and/or in-growth can take place on undercuts, crevices, cul de sacs, conduits, caves, tunnels, and interconnected pores that are hidden from line-of sight deposition, thereby significantly improving the strength of the connection between the surrounding tissue and the implant. The strength of the connection is significantly improved because the tissue grows into the undercuts, crevices, cul de sacs, conduits, caves, tunnels, and interconnected pores creating a tissue structure that interlocks with the structured surface on a macroscopic level. It can be advantageous if the coating covers a continuous length of a void structure (e.g., undercuts, crevices, cul de sacs, conduits, caves, tunnels, interconnected pores, etc.) that is open to adjacent tissue in at least two places. For example, if the tissue grows through a tunnel, the strength of the connection will be based not only on the interface adhesion between the wall of the tunnel and the tissue, but also on the inherent mechanical strength of the loop of tissue that is routed through the tunnel.
g The particular manufacturing process used for depositing the coating should be inexpensive and reproducible. Conveniently, the deposition of the coating can be carried out by using any vapor deposition method. Vapor deposition methods include chemical vapor deposition (CVD) (e.g., plasma assisted CVD) and physical vapor deposition (PVD) (e.g., arc evaporation, e-beam, molten pool, sputtering, evaporative ion plating, and cathodic arc ion plating). It is preferred that the process be a physical vapor deposition.
For the manufacturing operation, it is moreover an advantage to employ an arc evaporation physical vapor deposition method.
FIG. S depicts an arc evaporation physical vapor deposition apparatus and method for coating a structured surface on a substrate. A water cooled chamber 510 functions as an anode. A vacuum pump 520 and a conduit 530 for a neutral gas and a reactive gas are connected to the chamber 510. The chamber includes a plurality of evaporators 540 that function as cathodes. Each of the evaporators includes a source of a material 545 from which the coating is to be formed (e.g., titanium). An arc power supply 550 can be connected to each of the plurality of evaporators 540 (only a single connection is shown in FIG. 5). Each of the evaporators 540 can generate a plasma 560 that includes a high number of ions together with electrons and neutral vapor atoms. (It should be noted that the plasma 560 is represented schematically for clarity.) The plasma 560 impinges upon a substrate 570 that is connected to a bias (-) power supply. By increasing the bias, the ions are accelerated toward the substrate more rapidly. The apparatus can also include one, or more, structures to steer and/or filter the plasma such as, for example internal and/or external magnets.
Still referring to FIG. 5, the substrate 570 includes a structured surface (not shown) onto which the coating can be deposited. Portions of the substrate that are not to be coated can be masked with a mask material that can be removed after the deposition of the coating is finished. In general, the coating can be formed by any thin film technique.
Thin film technique include physical vapor deposition and chemical vapor deposition, and combinations thereof.
Still referring to FIG. 5, the method of using the illustrated apparatus begins by loading the substrate 570 into the chamber 510. A vacuum is then created in the chamber 510 using the vacuum pump 520. A test for leaks is then conducted. A
conditioning arid heating subprocess can then be performed. One reason to conduct this subprocess is to heat and remove any oxides from the structured surface. This subprocess can be based on radiant heating. This subprocess can also be based on glow discharge with a high bias voltage to effect an ion bombardment by a gas, or gas mixture. This subprocess can also be based on ion bombardment with the material from which the coating is to be formed (e.g., titanium) with a high bias voltage (e.g., from approximately 1000 to approximately 1500 volts). This latter technique causes an intermixing of the coating material (e.g., titanium) into the material that defines the structured surface (e.g., CoCr). After the conclusion of the subprocess, the coating is applied. The bias voltage is lowered to deposit and build up the coating. By adding a gas, preferably an inert gas, such as, for example, argon or helium (most preferably argon), full coverage of undercuts and full coverage within pore structures can be obtained.
While not being limited to any particular theory, it is believed that the presence of the gas reduces the average velocity and increases the scattering of the coating vapor as it moves from the cathode to the structured surface, thereby allowing better migration of the coating vapor inside the undercuts, crevices, cul de sacs, conduits, caves, tunnels, interconnected pores, etc., before the vapor is deposited (i.e., fixed) on the structured surface. This relationship may be due to an increase in scattered vector components representing the speed and direction of the vapor molecules due to collisions between the vapor molecules and the gas molecules, with a corresponding decrease in the magnitude of a primary vector representing the average speed and velocity of all the vapor molecules.
Still referring to FIG. 5, the process temperature can range from approximately 500 to approximately 900 deg. F. The operating pressure during radiant heating can range from approximately 1.0 millitorr to approximately 0.01 millitorr. The operating pressure during the bombard phase (e.g., titanium without any dampening gas) can range from approximately 10.0 millitorr to approximately 0.001 millitorr. The operating pressure during the coating phase (e.g., titanium with optional dampening gas) can range from approximately less than 1 millitorr to approximately 100 millitorr. The arc voltage can range from approximately 10 to approximately 100 volts/evaporator. The bias voltage can range from approximately 1000 to approximately 1500 volts during bombardment, and from approximately 10 to approximately 500 volts during coating.
However, the particular manufacturing process used for depositing the coating is not essential to the invention as long as it provides the described biocompatible coating.
Normally those who make or use the invention will select the manufacturing process based upon tooling and energy requirements, the expected application requirements of the final product, and the demands of the overall manufacturing process.
Referring now to FIGS. 6a-6b, scanning electron micrographs of a biocompatible coating including titanium on a structured surface defined by CoCrMo particles after an electrochemical test (ASTM F746)are depicted. FIG. 6a was acquired at x300.
FIG. 6b was acquired at x700.
Referring now to FIGS. 7a-7d, electron micrographs of a structured surface defined by CoCrMo particles without the biocompatible coating after the electrochemical test (ASTM F746) are depicted. FIG. 7b was acquired at x 120. FIG. 7d was acquired at x650.
10 By comparing the results shown in FIGS. 7a-7b with the results shown in FIGS. 6a-6b, it can be appreciated that the biocompatible coating significantly inhibits corrosion. For example, FIGS. 7a-7d show significant evidence of intergranular corrosion attacks while FIGS. 6a-6b do not show significant evidence of intergranular corrosion attacks.
Referring now to Figs. 8a-8b, electron micrographs of a structured surface defined by CoCrMo particles without the biocompatible coating before the electrochemical test (ASTM
F746) (i.e., before any corrosion test) are depicted. FIG. 8a was acquired at xI20. FIG. 8b was acquired at x600.
The particular material used for the substrate should be strong. Some examples of substrate materials include ASTM F67, F75, F90, F136, F138, F560, F562, F620, F621, F799, F961, F1058, F1295, F1341, F1472, F1537, and F1586. These are all grades of titanium, CoCr, stainless steel, tantalum, or alloys) thereof. It is preferred that the substrate material be a cobalt-chrome alloy. The substrate can be manufactured as a wrought, forged, or cast form.
The particular material used to define the structured surface should also be strong. It is preferred that the material used to define the structured surface be the same as the material used for the substrate (e.g., cobalt-chrome). However, the material used to define the structured surface can be different and include any one or more of, for example, titanium, CoCr, stainless steel, and tantalum, or alloys) thereof. The structured surface can be manufactured in various forms, including, but not limited to, sintered, flame sprayed, acid etched, grit blasted, cast-in, forged-in, laser textured, or micromachined form. For the manufacturing operation, it is an advantage to employ a partially sintered (porous) structure obtained by forming a layer of a mixture that contains a plurality of particles and a binder, and optionally a sacrificial filler.
For non-interconnecting (nonporous) structures, the surface roughness (Ra or RZ) of the structured surface can range from approximately 100 to approximately 40,000 ,/inch, preferably from approximately 3,000 to approximately 30,000 ,/inch. When the structured surface is defined by a porous layer, the layer can have a thickness from approximately 0.010 to 0.080 inch deep, preferably from approximately 0.010 to 0.060 inch deep. In the case of porous structures, the pore sizes can be from approximately 50 to approximately 500 microns, preferably from approximately 200 to 450 microns.
The particular material used for the coating should be biocompatible and provide a suitable surface for tissue in-growth and/or on-growth. It is preferred that the coating be titanium. However, the coating can include one or more of, for example, titanium, tantalum, calcium phosphate, hydroxyapatite, and tissue in-growth andlor on-growth promoting proteins, or alloys thereof.
When the thickness of the coating is excessively thin, parts of the structured surface may not be covered. On the other hand, when the thickness of the coating is excessively high, the strength of the coating may go down due to residual, thermal induced stress. For the specific embodiment of pure titanium on a structured surface defined by a sintered plurality of particles with interconnected porosity, in the deepest region (e.g., bottom of the lowest pore), the minimum coating thickness can be approximately 1 micron. In the outermost region (e.g., top of the highest particle), the maximum coating thickness can be approximately 20 microns.
However, the particular materials selected for coating and substrate are not essential to the invention, as long as they provide the described functions. Normally, those who make or use the invention will select the best commercially available materials based upon the economics of cost and availability, the expected specific application requirements of the final product, and the demands of the overall manufacturing process.
The disclosed embodiments show a continuous coating deposited in one or more zones across at least a portion of a structured surface as the structure for performing the function of facilitating tissue in-growth and/or on-growth. However, the structure for promoting tissue in-growth and/or on-growth can be any other structure capable of performing the function of achieving tissue adhesion, including, by way of example, a pattern such as an array of dots, or lines, or any other geometric pattern.
While not being limited to any particular performance indicator or diagnostic identifier, preferred embodiments of the invention can be identified one at a time by testing S for the presence of high adhesion between the coating and the structured surface. The test for the presence of high adhesion can be carried out without undue experimentation by the use of simple and conventional tribological and mechanical experiments. Among the other ways in which to seek embodiments having the attribute of high adhesion guidance toward the next preferred embodiment can be based on the presence of high coating coverage of undercut surfaces (e.g., hidden interconnected pores). The test for the presence of high coating coverage of undercut surfaces can be carried out without undue experimentation by the use of simple and conventional optical and/or electron microscope imaging techniques.
Practical Applications of the Invention A practical application of the invention that has value within the technological arts is I S the fabrication of an implant for the replacement of a knee joint or a hip joint. Further, the invention is useful in conjunction with other implants (such as pins used for the purpose of joining bones), or the like. There are virtually innumerable uses for the invention, all of which need not be detailed here.
Advantages of the Invention An implant, representing an embodiment of the invention, can be cost effective and advantageous for at least the following reasons. The implants are simple and economical to implement. The implants have increased strength due to the structured surface being defined by a high strength material and better biocompatibility due to the use of materials for the coating that are more biocompatible than the substrate. A single implant can posses different surface areas that are individually optimized with i} some areas bearing tissue in-growth and/or on-growth composite coating, ii) some areas exhibiting the properties of the substrate material(s), and iii) some areas bearing hard surfaces foamed by treatments, such as, for example, ion bombardment.
All the disclosed embodiments of the invention described herein can be realized and practiced without undue experimentation. Although the best mode of carrying out the invention contemplated by the inventors is disclosed above, practice of the invention is not WO 99/58167 PCT/US99/0845. 6 limited thereto. Accordingly, it will be appreciated by those skilled in the art that the invention may be practiced otherwise than as specifically described herein.
For example, the individual components need not be formed in the disclosed shapes, or assembled in the disclosed configuration, but could be provided in virtually any shape, S and assembled in virtually any configuration. Further, the individual components need not be fabricated from the disclosed materials, but could be fabricated from virtually any suitable materials. Further, although the implant described herein is a physically separate module, it will be manifest that the implant may be integrated into additional apparatus with which it is associated. Furthermore, all the disclosed elements and features of each disclosed embodiment can be combined with, or substituted for, the disclosed elements and features of every other disclosed embodiment except where such elements or features are mutually exclusive.
It will be manifest that various additions, modifications and rearrangements of the features of the invention may be made without deviating from the spirit and scope of the underlying inventive concept. It is intended that the scope of the invention as defined by the appended claims and their equivalents cover all such additions, modifications, and rearrangements. The appended claims are not to be interpreted as including means-plus-function limitations, unless such a limitation is explicitly recited in a given claim using the phrase "means-for." Expedient embodiments of the invention are differentiated by the appended subclaims.
The effect of cathodic arc ion plating with a high bias voltage is to cause an intermixing of titanium into the cobalt-chrome substrate due to high ion energies. It can be appreciated that there is an inter-penetration of the coating material into the structured surface material between the interface and the bulk of the material that composes the structured surface. Specifically, the amount of coating material that composes the substrate that defines the structured surface decreases as the depth from the interface increases. When the bias voltage is increased, the inter-penetration depth increases. The depth of this intermixing can range from approximately 0.5 nm to approximately 500 nm, preferably approximately 50 nm to approximately 100 nm. When the bias voltage is sufficient, substantial inter-penetration occurs. This result is advantageous because the inter-penetration improves the adhesion of the coating to the structured surface, thereby minimizing flaking, peeling, and other disruptions of the coating. This is very important for at least the following two reasons. First, the coating will be subject to tissue in-growth and/or on-growth and, therefore, can be subject to dynamic loading from adjacent tissue structures, such as, for example, bones. By improving the adhesion, the coating is better able to withstand loading. Second, the implant may be expected to remain in vivo for many years and it is highly desirable that all of the implant remain fixed in place. By improving the adhesion of the coating to the structured surface, the long term stability of the coating is enhanced.
Referring now to FIG. 4, a porous structured surface 410 with a coating 420 is depicted. The coating 420 includes titanium and can be deposited via physical vapor deposition with a gas, preferably an inert gas, such as, for example, argon and/or helium. It can be advantageous to use argon as the gas because it is inert and has a relatively high atomic weight. Significantly, the coating 420 covers portions of a structured surface defined 7 PCT/US99/084~6 by an interconnected pore 430 that is hidden from line-of sight deposition (i.e., the pore 430 cannot be seen from the point of view of the deposition source). The structured surface is also defined by a plurality of particles covering a substrate 440 (i.e., the structured surface is defined by the interface between the substrate 440 and the plurality of particles).
Nevertheless, the surface defined by the interconnected pore 430 is coated and provides an area for tissue in-growth and/or on-growth because an inert gas is present in the deposition chamber while the coating 420 is being applied. Although the preferred embodiment shown in FIG. 4 includes the coating of the surface defined by the interconnected pore 430, it is within the level of ordinary skill in the art after having knowledge of the invention disclosed herein to coat any undercut, or vertical, or line-of sight hidden surface area.
FIG. 4 demonstrates substantially improved results that are unexpected.
Specifically, the coating of internal pores demonstrates the significant unexpected advantageous result that when an inert gas is present during the deposition process, the coating is deposited on line-of sight hidden surfaces (e.g. interconnected pores). It can be appreciated that the structured surface 410 is coated because the exterior of the particles appears rough.
Normally, in the case of an uncoated particle, the perimeter would be smooth and more nearly circular. The roughness is the coating. This result is advantageous because it significantly improves adhesion of the surrounding tissue to the implant.
Adhesion is significantly improved because tissue on-growth and/or in-growth can take place on undercuts, crevices, cul de sacs, conduits, caves, tunnels, and interconnected pores that are hidden from line-of sight deposition, thereby significantly improving the strength of the connection between the surrounding tissue and the implant. The strength of the connection is significantly improved because the tissue grows into the undercuts, crevices, cul de sacs, conduits, caves, tunnels, and interconnected pores creating a tissue structure that interlocks with the structured surface on a macroscopic level. It can be advantageous if the coating covers a continuous length of a void structure (e.g., undercuts, crevices, cul de sacs, conduits, caves, tunnels, interconnected pores, etc.) that is open to adjacent tissue in at least two places. For example, if the tissue grows through a tunnel, the strength of the connection will be based not only on the interface adhesion between the wall of the tunnel and the tissue, but also on the inherent mechanical strength of the loop of tissue that is routed through the tunnel.
g The particular manufacturing process used for depositing the coating should be inexpensive and reproducible. Conveniently, the deposition of the coating can be carried out by using any vapor deposition method. Vapor deposition methods include chemical vapor deposition (CVD) (e.g., plasma assisted CVD) and physical vapor deposition (PVD) (e.g., arc evaporation, e-beam, molten pool, sputtering, evaporative ion plating, and cathodic arc ion plating). It is preferred that the process be a physical vapor deposition.
For the manufacturing operation, it is moreover an advantage to employ an arc evaporation physical vapor deposition method.
FIG. S depicts an arc evaporation physical vapor deposition apparatus and method for coating a structured surface on a substrate. A water cooled chamber 510 functions as an anode. A vacuum pump 520 and a conduit 530 for a neutral gas and a reactive gas are connected to the chamber 510. The chamber includes a plurality of evaporators 540 that function as cathodes. Each of the evaporators includes a source of a material 545 from which the coating is to be formed (e.g., titanium). An arc power supply 550 can be connected to each of the plurality of evaporators 540 (only a single connection is shown in FIG. 5). Each of the evaporators 540 can generate a plasma 560 that includes a high number of ions together with electrons and neutral vapor atoms. (It should be noted that the plasma 560 is represented schematically for clarity.) The plasma 560 impinges upon a substrate 570 that is connected to a bias (-) power supply. By increasing the bias, the ions are accelerated toward the substrate more rapidly. The apparatus can also include one, or more, structures to steer and/or filter the plasma such as, for example internal and/or external magnets.
Still referring to FIG. 5, the substrate 570 includes a structured surface (not shown) onto which the coating can be deposited. Portions of the substrate that are not to be coated can be masked with a mask material that can be removed after the deposition of the coating is finished. In general, the coating can be formed by any thin film technique.
Thin film technique include physical vapor deposition and chemical vapor deposition, and combinations thereof.
Still referring to FIG. 5, the method of using the illustrated apparatus begins by loading the substrate 570 into the chamber 510. A vacuum is then created in the chamber 510 using the vacuum pump 520. A test for leaks is then conducted. A
conditioning arid heating subprocess can then be performed. One reason to conduct this subprocess is to heat and remove any oxides from the structured surface. This subprocess can be based on radiant heating. This subprocess can also be based on glow discharge with a high bias voltage to effect an ion bombardment by a gas, or gas mixture. This subprocess can also be based on ion bombardment with the material from which the coating is to be formed (e.g., titanium) with a high bias voltage (e.g., from approximately 1000 to approximately 1500 volts). This latter technique causes an intermixing of the coating material (e.g., titanium) into the material that defines the structured surface (e.g., CoCr). After the conclusion of the subprocess, the coating is applied. The bias voltage is lowered to deposit and build up the coating. By adding a gas, preferably an inert gas, such as, for example, argon or helium (most preferably argon), full coverage of undercuts and full coverage within pore structures can be obtained.
While not being limited to any particular theory, it is believed that the presence of the gas reduces the average velocity and increases the scattering of the coating vapor as it moves from the cathode to the structured surface, thereby allowing better migration of the coating vapor inside the undercuts, crevices, cul de sacs, conduits, caves, tunnels, interconnected pores, etc., before the vapor is deposited (i.e., fixed) on the structured surface. This relationship may be due to an increase in scattered vector components representing the speed and direction of the vapor molecules due to collisions between the vapor molecules and the gas molecules, with a corresponding decrease in the magnitude of a primary vector representing the average speed and velocity of all the vapor molecules.
Still referring to FIG. 5, the process temperature can range from approximately 500 to approximately 900 deg. F. The operating pressure during radiant heating can range from approximately 1.0 millitorr to approximately 0.01 millitorr. The operating pressure during the bombard phase (e.g., titanium without any dampening gas) can range from approximately 10.0 millitorr to approximately 0.001 millitorr. The operating pressure during the coating phase (e.g., titanium with optional dampening gas) can range from approximately less than 1 millitorr to approximately 100 millitorr. The arc voltage can range from approximately 10 to approximately 100 volts/evaporator. The bias voltage can range from approximately 1000 to approximately 1500 volts during bombardment, and from approximately 10 to approximately 500 volts during coating.
However, the particular manufacturing process used for depositing the coating is not essential to the invention as long as it provides the described biocompatible coating.
Normally those who make or use the invention will select the manufacturing process based upon tooling and energy requirements, the expected application requirements of the final product, and the demands of the overall manufacturing process.
Referring now to FIGS. 6a-6b, scanning electron micrographs of a biocompatible coating including titanium on a structured surface defined by CoCrMo particles after an electrochemical test (ASTM F746)are depicted. FIG. 6a was acquired at x300.
FIG. 6b was acquired at x700.
Referring now to FIGS. 7a-7d, electron micrographs of a structured surface defined by CoCrMo particles without the biocompatible coating after the electrochemical test (ASTM F746) are depicted. FIG. 7b was acquired at x 120. FIG. 7d was acquired at x650.
10 By comparing the results shown in FIGS. 7a-7b with the results shown in FIGS. 6a-6b, it can be appreciated that the biocompatible coating significantly inhibits corrosion. For example, FIGS. 7a-7d show significant evidence of intergranular corrosion attacks while FIGS. 6a-6b do not show significant evidence of intergranular corrosion attacks.
Referring now to Figs. 8a-8b, electron micrographs of a structured surface defined by CoCrMo particles without the biocompatible coating before the electrochemical test (ASTM
F746) (i.e., before any corrosion test) are depicted. FIG. 8a was acquired at xI20. FIG. 8b was acquired at x600.
The particular material used for the substrate should be strong. Some examples of substrate materials include ASTM F67, F75, F90, F136, F138, F560, F562, F620, F621, F799, F961, F1058, F1295, F1341, F1472, F1537, and F1586. These are all grades of titanium, CoCr, stainless steel, tantalum, or alloys) thereof. It is preferred that the substrate material be a cobalt-chrome alloy. The substrate can be manufactured as a wrought, forged, or cast form.
The particular material used to define the structured surface should also be strong. It is preferred that the material used to define the structured surface be the same as the material used for the substrate (e.g., cobalt-chrome). However, the material used to define the structured surface can be different and include any one or more of, for example, titanium, CoCr, stainless steel, and tantalum, or alloys) thereof. The structured surface can be manufactured in various forms, including, but not limited to, sintered, flame sprayed, acid etched, grit blasted, cast-in, forged-in, laser textured, or micromachined form. For the manufacturing operation, it is an advantage to employ a partially sintered (porous) structure obtained by forming a layer of a mixture that contains a plurality of particles and a binder, and optionally a sacrificial filler.
For non-interconnecting (nonporous) structures, the surface roughness (Ra or RZ) of the structured surface can range from approximately 100 to approximately 40,000 ,/inch, preferably from approximately 3,000 to approximately 30,000 ,/inch. When the structured surface is defined by a porous layer, the layer can have a thickness from approximately 0.010 to 0.080 inch deep, preferably from approximately 0.010 to 0.060 inch deep. In the case of porous structures, the pore sizes can be from approximately 50 to approximately 500 microns, preferably from approximately 200 to 450 microns.
The particular material used for the coating should be biocompatible and provide a suitable surface for tissue in-growth and/or on-growth. It is preferred that the coating be titanium. However, the coating can include one or more of, for example, titanium, tantalum, calcium phosphate, hydroxyapatite, and tissue in-growth andlor on-growth promoting proteins, or alloys thereof.
When the thickness of the coating is excessively thin, parts of the structured surface may not be covered. On the other hand, when the thickness of the coating is excessively high, the strength of the coating may go down due to residual, thermal induced stress. For the specific embodiment of pure titanium on a structured surface defined by a sintered plurality of particles with interconnected porosity, in the deepest region (e.g., bottom of the lowest pore), the minimum coating thickness can be approximately 1 micron. In the outermost region (e.g., top of the highest particle), the maximum coating thickness can be approximately 20 microns.
However, the particular materials selected for coating and substrate are not essential to the invention, as long as they provide the described functions. Normally, those who make or use the invention will select the best commercially available materials based upon the economics of cost and availability, the expected specific application requirements of the final product, and the demands of the overall manufacturing process.
The disclosed embodiments show a continuous coating deposited in one or more zones across at least a portion of a structured surface as the structure for performing the function of facilitating tissue in-growth and/or on-growth. However, the structure for promoting tissue in-growth and/or on-growth can be any other structure capable of performing the function of achieving tissue adhesion, including, by way of example, a pattern such as an array of dots, or lines, or any other geometric pattern.
While not being limited to any particular performance indicator or diagnostic identifier, preferred embodiments of the invention can be identified one at a time by testing S for the presence of high adhesion between the coating and the structured surface. The test for the presence of high adhesion can be carried out without undue experimentation by the use of simple and conventional tribological and mechanical experiments. Among the other ways in which to seek embodiments having the attribute of high adhesion guidance toward the next preferred embodiment can be based on the presence of high coating coverage of undercut surfaces (e.g., hidden interconnected pores). The test for the presence of high coating coverage of undercut surfaces can be carried out without undue experimentation by the use of simple and conventional optical and/or electron microscope imaging techniques.
Practical Applications of the Invention A practical application of the invention that has value within the technological arts is I S the fabrication of an implant for the replacement of a knee joint or a hip joint. Further, the invention is useful in conjunction with other implants (such as pins used for the purpose of joining bones), or the like. There are virtually innumerable uses for the invention, all of which need not be detailed here.
Advantages of the Invention An implant, representing an embodiment of the invention, can be cost effective and advantageous for at least the following reasons. The implants are simple and economical to implement. The implants have increased strength due to the structured surface being defined by a high strength material and better biocompatibility due to the use of materials for the coating that are more biocompatible than the substrate. A single implant can posses different surface areas that are individually optimized with i} some areas bearing tissue in-growth and/or on-growth composite coating, ii) some areas exhibiting the properties of the substrate material(s), and iii) some areas bearing hard surfaces foamed by treatments, such as, for example, ion bombardment.
All the disclosed embodiments of the invention described herein can be realized and practiced without undue experimentation. Although the best mode of carrying out the invention contemplated by the inventors is disclosed above, practice of the invention is not WO 99/58167 PCT/US99/0845. 6 limited thereto. Accordingly, it will be appreciated by those skilled in the art that the invention may be practiced otherwise than as specifically described herein.
For example, the individual components need not be formed in the disclosed shapes, or assembled in the disclosed configuration, but could be provided in virtually any shape, S and assembled in virtually any configuration. Further, the individual components need not be fabricated from the disclosed materials, but could be fabricated from virtually any suitable materials. Further, although the implant described herein is a physically separate module, it will be manifest that the implant may be integrated into additional apparatus with which it is associated. Furthermore, all the disclosed elements and features of each disclosed embodiment can be combined with, or substituted for, the disclosed elements and features of every other disclosed embodiment except where such elements or features are mutually exclusive.
It will be manifest that various additions, modifications and rearrangements of the features of the invention may be made without deviating from the spirit and scope of the underlying inventive concept. It is intended that the scope of the invention as defined by the appended claims and their equivalents cover all such additions, modifications, and rearrangements. The appended claims are not to be interpreted as including means-plus-function limitations, unless such a limitation is explicitly recited in a given claim using the phrase "means-for." Expedient embodiments of the invention are differentiated by the appended subclaims.
Claims (75)
1. An implant, comprising:
a substrate;
a structured surface formed on at least a portion of said substrate; and a biocompatible coating deposited on at least a fraction of said structured surface.
a substrate;
a structured surface formed on at least a portion of said substrate; and a biocompatible coating deposited on at least a fraction of said structured surface.
2. The implant of claim 1, wherein said biocompatible coating is more biocompatible than said structured surface.
3. The implant of claim 1, wherein said biocompatible coating is more biocompatible than said substrate.
4. The implant of claim 1, wherein said biocompatible coating is softer than said structured surface.
5. The implant of claim 1, wherein said biocompatible coating is softer than said substrate.
6. The implant of claim 1, wherein said coating is formed by a thin film technique.
7. The implant of claim 6, wherein said thin film technique includes at least one deposition process selected from the group consisting of physical vapor deposition and chemical vapor deposition.
8. The implant of claim 1, wherein said structured surface includes a plurality of undercuts and said biocompatible material coats said plurality of undercuts in said structured surface.
9. The implant of claim 8, wherein said structured surface is porous and said biocompatible material coats interconnected pores beneath said structured surface.
10. The implant of claim 1, wherein said substrate includes at least one material selected from the group consisting of carbon-composite, stainless steel, cobalt-chromium, titanium alloy, tantalum, and ceramic.
11. The implant of claim 1, wherein said structured surface is defined by a material that includes a plurality of particles that are sintered together to form a continuous porous phase.
12. The implant of claim 1, wherein said structured surface is prepared by at least one method selected from the group consisting of sintering, flame spraying, acid etching, grit blasting, casting-in, forging-in, laser texturing, and micromachining.
13. The implant of claim 1, wherein said biocompatible coating includes at least one material selected from the group consisting of titanium, tantalum, carbon, calcium phosphate, zirconium, niobium, hafnium, hydroxyapatite, and tissue in-growth and/or on-growth facilitating proteins.
14. The implant of claim 1, wherein said biocompatible coating includes multi-layers.
15. The implant of claim 1, wherein said biocompatible coating includes nano-layers.
16. The implant of claim 1, wherein said implant is an orthopedic prosthesis.
17. A method for orthopedic surgery which comprises surgically positioning said implant of claim 1 within a vertebrate in need thereof.
18. An osteoconductive process, comprising contacting a bone under in vivo conditions with said implant of claim 1.
19. A composition for an implant, comprising:
a biocompatible material coated on a structured surface defined by a substrate.
a biocompatible material coated on a structured surface defined by a substrate.
20. The composition of claim 19, wherein said biocompatible coating is more biocompatible than said structured surface.
21. The composition of claim 19, wherein said biocompatible coating is more biocompatible than said substrate.
22. The composition of claim 19, wherein said biocompatible coating is softer than said structured surface.
23. The composition of claim 19, wherein said biocompatible coating is softer than said substrate.
24. The composition of claim 19, wherein said coating is formed by a thin film technique.
25. The composition of claim 24, wherein said thin film technique includes at least one deposition process selected from the group consisting of physical vapor deposition and chemical vapor deposition.
26. The composition of claim 19, wherein said structured surface includes a plurality of undercuts and said biocompatible material coats said plurality of undercuts in said structured surface.
27. The composition of claim 26, wherein said structured surface is porous and said biocompatible material coats interconnected pores beneath said structured surface.
28. The composition of claim 19, wherein said substrate includes at least one material selected from the group consisting of carbon-composite, stainless steel, cobalt-chromium, titanium alloy, tantalum, and ceramic.
29. The composition of claim 19, wherein said structured surface is defined by a material that includes a plurality of particles that are sintered together to form a continuous porous phase.
30. The composition of claim 19, wherein said structured surface is prepared by at least one method selected from the group consisting of sintering, flame spraying, acid etching, grit blasting, casting-in, forging-in, laser texturing, and micromachining.
31. The composition of claim 19, wherein said biocompatible coating includes at least one material selected from the group consisting of titanium, tantalum, carbon, calcium phosphate, zirconium, niobium, hafnium, hydroxyapatite, and tissue in-growth and/or on-growth facilitating proteins.
32 The composition of claim 19, wherein said biocompatible coating includes multi-layers.
33. The composition of claim 19, wherein said biocompatible coating includes nano-layers.
34. An osteoconductive process, comprising contacting a bone under in vivo conditions with said composition of claim 19.
35. An orthopedic implant, comprising said composition of claim 19.
36. A method for orthopedic surgery which comprises positioning said composition of claim 19 within a vertebrate in need thereof.
37. An implant, comprising:
a substrate;
a structured surface formed on a portion of said substrate; and a biocompatible coating deposited on at least a fraction of said structured surface, wherein said portion of said substrate is to be fixed with tissue in-growth and/or on-growth for stability.
a substrate;
a structured surface formed on a portion of said substrate; and a biocompatible coating deposited on at least a fraction of said structured surface, wherein said portion of said substrate is to be fixed with tissue in-growth and/or on-growth for stability.
38. The implant of claim 37, wherein said biocompatible coating is more biocompatible than said structured surface.
39. The implant of claim 37, wherein said biocompatible coating is more biocompatible than said substrate.
40. The implant of claim 37, wherein said biocompatible coating is softer than said structured surface.
41. The implant of claim 37, wherein said biocompatible coating is softer than said substrate.
42. The implant of claim 37, wherein said coating is formed by a thin film technique.
43. The implant of claim 42, wherein said thin film technique includes at least one deposition process selected from the group consisting of physical vapor deposition and chemical vapor deposition.
44. The implant of claim 37, wherein said structured surface includes a plurality of undercuts and said biocompatible material coats said plurality of undercuts in said structured surface.
45. The implant of claim 44, wherein said structured surface is porous and said biocompatible material coats interconnected pores beneath said structured surface.
46. The implant of claim 37, wherein said substrate includes at least one material selected from the group consisting of carbon-composite, stainless steel, cobalt-chromium, titanium alloy, tantalum, and ceramic.
47. The implant of claim 37, wherein said structured surface is defined by a material that includes a plurality of particles that are sintered together to form a continuous porous phase.
48. The implant of claim 37, wherein said structured surface is prepared by at least one method selected from the group consisting of sintering, flame spraying, acid etching, grit blasting, casting-in, forging-in, laser texturing, and micromachining.
49. The implant of claim 37, wherein said biocompatible coating includes at least one material selected from the group consisting of titanium, tantalum, carbon, calcium phosphate, zirconium, niobium, hafnium, hydroxyapatite, and tissue in-growth and/or on-growth facilitating proteins.
50. The implant of claim 37, wherein said biocompatible coating includes multi-layers.
51. The implant of claim 37, wherein said biocompatible coating includes nano-layers.
52. The implant of claim 37, wherein said implant is an orthopedic prosthesis.
53. A method for orthopedic surgery which comprises surgically positioning said implant of claim 37 within a vertebrate in need thereof.
54. An osteoconductive process, comprising contacting a bone under in vivo conditions with said implant of claim 37.
55. A method of forming a composite coating, comprising:
depositing a biocompatible coating on a structured surface that composes at least a portion of a surface area of a substrate.
depositing a biocompatible coating on a structured surface that composes at least a portion of a surface area of a substrate.
56. The method of forming a composite coating according to claim 55, further comprising:
covering said portion of said surface area of said substrate with a mixture including a plurality of particles, said plurality of particles including a first material; and sintering said plurality of particles to produce a porous structure, wherein said biocompatible coating includes a second material that is different from said first material.
covering said portion of said surface area of said substrate with a mixture including a plurality of particles, said plurality of particles including a first material; and sintering said plurality of particles to produce a porous structure, wherein said biocompatible coating includes a second material that is different from said first material.
57. The method of claim 55, wherein depositing said biocompatible coating includes depositing a coating that is more biocompatible than said structured surface.
58. The method of claim 55, wherein depositing said biocompatible coating includes depositing a coating that is more biocompatible than said substrate.
59. The method of claim 55, wherein depositing said biocompatible coating includes depositing a coating that is softer than said structured surface.
60. The method of claim 55, wherein depositing said biocompatible coating includes depositing a coating that is softer than said substrate.
61. The method of claim 55, wherein said depositing said biocompatible coating includes forming said biocompatible coating with a thin film technique.
62. The method of claim 61, wherein said thin film technique includes at least one deposition process selected from the group consisting of physical vapor deposition and chemical vapor deposition.
63. The method of claim 55, further comprising, before the step of depositing, forming a plurality of undercuts in said structured surface, and, wherein depositing said biocompatible coating includes coating said plurality of undercuts in said structured surface.
64. The method of claim 63, wherein forming a plurality of undercuts includes forming interconnected pores beneath said structured surface, and, wherein depositing said biocompatible coating includes coating said interconnected pores.
65. The method of claim 55, further comprising, before the step of depositing, providing said substrate from at least one material selected from the group consisting of carbon-composite, stainless steel, cobalt-chromium, titanium alloy, tantalum, and ceramic.
66. The method of claim 55, further comprising, before the step of depositing, providing said structured surface from a material that includes a plurality of particles that are sintered together to form a continuous porous phase.
67. The method of claim 55, further comprising, before the step of depositing, preparing said structured surface by at least one method selected from the group consisting of sintering, flame spraying, acid etching, grit blasting, casting-in, forging-in, laser texturing, and micromachining.
68. The method of claim 55, wherein depositing said biocompatible coating includes depositing at least one material selected from the group consisting of titanium, tantalum, carbon, calcium phosphate, zirconium, niobium, hafnium, hydroxyapatite, and tissue in-growth and/or on-growth facilitating proteins.
69. The method of claim 55, wherein depositing said biocompatible coating include depositing multi-layers.
70. The method of claim 69, wherein depositing said biocompatible coating includes depositing nano-layers.
71. A method for orthopedic surgery which comprises surgically positioning an implant that includes the composite coating made by the method of claim 55 within a vertebrate in need thereof.
72. An osteoconductive process, comprising contacting a bone under in vivo conditions with an implant including a composite coating made by the method of claim 55.
73. An implant including a composite coating made by the method of claim SS.
74. An orthopedic prosthesis including a composite coating made by the method of claim 55.
75. The method of claim 55, further comprising, after the step of depositing, treating another portion of said surface area with ion bombardment.
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US09/079,502 | 1998-05-14 | ||
US09/079,502 US6261322B1 (en) | 1998-05-14 | 1998-05-14 | Implant with composite coating |
PCT/US1999/008456 WO1999058167A1 (en) | 1998-05-14 | 1999-04-16 | Implant with composite coating |
Publications (1)
Publication Number | Publication Date |
---|---|
CA2354065A1 true CA2354065A1 (en) | 1999-11-18 |
Family
ID=22150964
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA002354065A Abandoned CA2354065A1 (en) | 1998-05-14 | 1999-04-16 | Implant with composite coating |
Country Status (7)
Country | Link |
---|---|
US (5) | US6261322B1 (en) |
EP (1) | EP1093384B1 (en) |
AT (1) | ATE415983T1 (en) |
AU (1) | AU3650199A (en) |
CA (1) | CA2354065A1 (en) |
DE (1) | DE69940020D1 (en) |
WO (1) | WO1999058167A1 (en) |
Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20150069111A1 (en) * | 2012-06-18 | 2015-03-12 | DePuy Synthes Products, LLC | Dual modulus hip stem and method of making the same |
Families Citing this family (161)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8617242B2 (en) * | 2001-05-25 | 2013-12-31 | Conformis, Inc. | Implant device and method for manufacture |
US8556983B2 (en) | 2001-05-25 | 2013-10-15 | Conformis, Inc. | Patient-adapted and improved orthopedic implants, designs and related tools |
US8735773B2 (en) | 2007-02-14 | 2014-05-27 | Conformis, Inc. | Implant device and method for manufacture |
US6261322B1 (en) * | 1998-05-14 | 2001-07-17 | Hayes Medical, Inc. | Implant with composite coating |
US6827742B2 (en) * | 1998-05-14 | 2004-12-07 | Daniel E. E. Hayes, Jr. | Bimetal acetabular component construct for hip joint prosthesis |
US7653923B2 (en) | 2000-02-18 | 2010-01-26 | Prime Research Alliance E, Inc. | Scheduling and presenting IPG ads in conjunction with programming ads in a television environment |
DE19951477A1 (en) | 1999-10-26 | 2001-05-03 | Biotronik Mess & Therapieg | Stent |
EP1244606B1 (en) * | 1999-12-21 | 2005-04-27 | CeramTec AG Innovative Ceramic Engineering | Coating aluminium oxide ceramics with hydroxyl apatite |
US8632583B2 (en) | 2011-05-09 | 2014-01-21 | Palmaz Scientific, Inc. | Implantable medical device having enhanced endothelial migration features and methods of making the same |
DE60111253T2 (en) * | 2000-07-20 | 2006-04-20 | Hayes Medical, Inc., El Dorado Hills | RAIL INSERT FROM A BIMETAL FOR APPLICATION IN A KNEE PROSTHESIS |
US20020106611A1 (en) * | 2001-01-19 | 2002-08-08 | Sutapa Bhaduri | Metal part having a dense core and porous periphery, biocompatible prosthesis and microwave sintering |
US6599322B1 (en) * | 2001-01-25 | 2003-07-29 | Tecomet, Inc. | Method for producing undercut micro recesses in a surface, a surgical implant made thereby, and method for fixing an implant to bone |
US7018418B2 (en) * | 2001-01-25 | 2006-03-28 | Tecomet, Inc. | Textured surface having undercut micro recesses in a surface |
US6620332B2 (en) | 2001-01-25 | 2003-09-16 | Tecomet, Inc. | Method for making a mesh-and-plate surgical implant |
US7597715B2 (en) | 2005-04-21 | 2009-10-06 | Biomet Manufacturing Corp. | Method and apparatus for use of porous implants |
US8123814B2 (en) | 2001-02-23 | 2012-02-28 | Biomet Manufacturing Corp. | Method and appartus for acetabular reconstruction |
US6949251B2 (en) * | 2001-03-02 | 2005-09-27 | Stryker Corporation | Porous β-tricalcium phosphate granules for regeneration of bone tissue |
WO2002083194A1 (en) * | 2001-04-12 | 2002-10-24 | Therics, Inc. | Method and apparatus for engineered regenerative biostructures |
US20050177237A1 (en) * | 2001-04-12 | 2005-08-11 | Ben Shappley | Spinal cage insert, filler piece and method of manufacturing |
EP1389978B1 (en) * | 2001-05-01 | 2009-01-07 | Amedica Corporation | Radiolucent bone graft |
US7695521B2 (en) | 2001-05-01 | 2010-04-13 | Amedica Corporation | Hip prosthesis with monoblock ceramic acetabular cup |
US7776085B2 (en) * | 2001-05-01 | 2010-08-17 | Amedica Corporation | Knee prosthesis with ceramic tibial component |
US20050177238A1 (en) * | 2001-05-01 | 2005-08-11 | Khandkar Ashok C. | Radiolucent bone graft |
EP1408874B1 (en) * | 2001-06-14 | 2012-08-08 | Amedica Corporation | Metal-ceramic composite articulation |
SE519531C2 (en) * | 2001-07-04 | 2003-03-11 | Nobel Biocare Ab | Implants including pore arrangements coated with calcium phosphate |
WO2003034951A1 (en) * | 2001-10-20 | 2003-05-01 | Osseobiotek Ltd | Implant and method of manufacturing thereof |
CA2466947C (en) | 2001-11-19 | 2012-05-22 | Scil Technology Gmbh | A homogeneously coated device having osteoinductive and osteoconductive properties |
ATE317070T1 (en) * | 2001-11-23 | 2006-02-15 | Univ Duisburg Essen | IMPLANT |
EP1358859A1 (en) * | 2002-04-29 | 2003-11-05 | Politecnico Di Milano | Bone prostheses having multilayer interface |
US20040000540A1 (en) * | 2002-05-23 | 2004-01-01 | Soboyejo Winston O. | Laser texturing of surfaces for biomedical implants |
US20040002766A1 (en) * | 2002-06-27 | 2004-01-01 | Gordon Hunter | Prosthetic devices having diffusion-hardened surfaces and bioceramic coatings |
DK1539261T3 (en) * | 2002-09-10 | 2006-08-07 | Scil Technology Gmbh | Metal implant coated under reduced oxygen concentration with osteoinductive protein |
US20040053197A1 (en) * | 2002-09-16 | 2004-03-18 | Zoran Minevski | Biocompatible implants |
EP1551569B1 (en) | 2002-09-26 | 2017-05-10 | Advanced Bio Prosthetic Surfaces, Ltd. | Implantable materials having engineered surfaces and method of making same |
US8268340B2 (en) | 2002-09-26 | 2012-09-18 | Advanced Bio Prosthetic Surfaces, Ltd. | Implantable materials having engineered surfaces and method of making same |
US8679517B2 (en) | 2002-09-26 | 2014-03-25 | Palmaz Scientific, Inc. | Implantable materials having engineered surfaces made by vacuum deposition and method of making same |
CA2448592C (en) | 2002-11-08 | 2011-01-11 | Howmedica Osteonics Corp. | Laser-produced porous surface |
US20060147332A1 (en) * | 2004-12-30 | 2006-07-06 | Howmedica Osteonics Corp. | Laser-produced porous structure |
JP2006510452A (en) * | 2002-12-17 | 2006-03-30 | アメディカ コーポレイション | Total disc implant |
US20040148033A1 (en) * | 2003-01-24 | 2004-07-29 | Schroeder David Wayne | Wear surface for metal-on-metal articulation |
US20040167632A1 (en) * | 2003-02-24 | 2004-08-26 | Depuy Products, Inc. | Metallic implants having roughened surfaces and methods for producing the same |
US20050155679A1 (en) * | 2003-04-09 | 2005-07-21 | Coastcast Corporation | CoCr alloys and methods for making same |
US7938861B2 (en) * | 2003-04-15 | 2011-05-10 | Depuy Products, Inc. | Implantable orthopaedic device and method for making the same |
US7520947B2 (en) | 2003-05-23 | 2009-04-21 | Ati Properties, Inc. | Cobalt alloys, methods of making cobalt alloys, and implants and articles of manufacture made therefrom |
US20050211680A1 (en) * | 2003-05-23 | 2005-09-29 | Mingwei Li | Systems and methods for laser texturing of surfaces of a substrate |
US7270679B2 (en) * | 2003-05-30 | 2007-09-18 | Warsaw Orthopedic, Inc. | Implants based on engineered metal matrix composite materials having enhanced imaging and wear resistance |
US7067169B2 (en) * | 2003-06-04 | 2006-06-27 | Chemat Technology Inc. | Coated implants and methods of coating |
US20040267376A1 (en) * | 2003-06-25 | 2004-12-30 | Kabushiki Kaisha Kobe Seiko Sho (Kobe Steel, Ltd) | Ceramic member for medical implant and its production method |
US8062365B2 (en) * | 2003-08-04 | 2011-11-22 | Warsaw Orthopedic, Inc. | Bone supporting devices with bio-absorbable end members |
US20050085922A1 (en) * | 2003-10-17 | 2005-04-21 | Shappley Ben R. | Shaped filler for implantation into a bone void and methods of manufacture and use thereof |
US7001672B2 (en) * | 2003-12-03 | 2006-02-21 | Medicine Lodge, Inc. | Laser based metal deposition of implant structures |
US20050165472A1 (en) * | 2004-01-22 | 2005-07-28 | Glocker David A. | Radiopaque coating for biomedical devices |
US20070106374A1 (en) * | 2004-01-22 | 2007-05-10 | Isoflux, Inc. | Radiopaque coating for biomedical devices |
US8002822B2 (en) | 2004-01-22 | 2011-08-23 | Isoflux, Inc. | Radiopaque coating for biomedical devices |
US7393589B2 (en) * | 2004-01-30 | 2008-07-01 | Ionbond, Inc. | Dual layer diffusion bonded chemical vapor coating for medical implants |
US20050196519A1 (en) * | 2004-03-08 | 2005-09-08 | Depuy Products, Inc. | Apparatus for producing a biomimetic coating on a medical implant |
US7744635B2 (en) * | 2004-06-09 | 2010-06-29 | Spinal Generations, Llc | Spinal fixation system |
WO2006004645A2 (en) * | 2004-06-28 | 2006-01-12 | Isoflux, Inc. | Porous coatings for biomedical implants |
CA2573329A1 (en) * | 2004-07-13 | 2006-02-16 | Isoflux, Inc. | Porous coatings on electrodes for biomedical implants |
GB0422666D0 (en) * | 2004-10-12 | 2004-11-10 | Benoist Girard Sas | Prosthetic acetabular cups |
US7862835B2 (en) * | 2004-10-27 | 2011-01-04 | Boston Scientific Scimed, Inc. | Method of manufacturing a medical device having a porous coating thereon |
CH697330B1 (en) | 2004-12-28 | 2008-08-29 | Synthes Gmbh | Intervertebral prosthesis. |
US20060184251A1 (en) * | 2005-01-07 | 2006-08-17 | Zongtao Zhang | Coated medical devices and methods of making and using |
US20060230288A1 (en) * | 2005-03-29 | 2006-10-12 | International Business Machines Corporation | Source code classification method for malicious code detection |
US8266780B2 (en) * | 2005-04-21 | 2012-09-18 | Biomet Manufacturing Corp. | Method and apparatus for use of porous implants |
US8021432B2 (en) | 2005-12-05 | 2011-09-20 | Biomet Manufacturing Corp. | Apparatus for use of porous implants |
US8066778B2 (en) * | 2005-04-21 | 2011-11-29 | Biomet Manufacturing Corp. | Porous metal cup with cobalt bearing surface |
US8292967B2 (en) * | 2005-04-21 | 2012-10-23 | Biomet Manufacturing Corp. | Method and apparatus for use of porous implants |
US8414907B2 (en) * | 2005-04-28 | 2013-04-09 | Warsaw Orthopedic, Inc. | Coatings on medical implants to guide soft tissue healing |
US9119901B2 (en) * | 2005-04-28 | 2015-09-01 | Warsaw Orthopedic, Inc. | Surface treatments for promoting selective tissue attachment to medical impants |
US7901462B2 (en) * | 2005-06-23 | 2011-03-08 | Depuy Products, Inc. | Implants with textured surface and methods for producing the same |
US9763788B2 (en) | 2005-09-09 | 2017-09-19 | Board Of Trustees Of The University Of Arkansas | Bone regeneration using biodegradable polymeric nanocomposite materials and applications of the same |
US8936805B2 (en) | 2005-09-09 | 2015-01-20 | Board Of Trustees Of The University Of Arkansas | Bone regeneration using biodegradable polymeric nanocomposite materials and applications of the same |
US8518123B2 (en) * | 2005-09-09 | 2013-08-27 | Board Of Trustees Of The University Of Arkansas | System and method for tissue generation and bone regeneration |
US20070078521A1 (en) * | 2005-09-30 | 2007-04-05 | Depuy Products, Inc. | Aluminum oxide coated implants and components |
ES2726355T3 (en) | 2005-11-14 | 2019-10-03 | Biomet 3I Llc | Deposition of discrete nanoparticles on an implant surface |
US8728387B2 (en) | 2005-12-06 | 2014-05-20 | Howmedica Osteonics Corp. | Laser-produced porous surface |
US8070821B2 (en) * | 2005-12-27 | 2011-12-06 | Howmedica Osteonics Corp. | Hybrid femoral implant |
CA2572095C (en) * | 2005-12-30 | 2009-12-08 | Howmedica Osteonics Corp. | Laser-produced implants |
US20080299337A1 (en) * | 2006-02-09 | 2008-12-04 | Isoflux, Inc. | Method for the formation of surfaces on the inside of medical devices |
EP1826293A1 (en) * | 2006-02-09 | 2007-08-29 | Isoflux, Inc. | Formation of nanoscale surfaces for the attachment of biological materials |
US8252058B2 (en) * | 2006-02-16 | 2012-08-28 | Amedica Corporation | Spinal implant with elliptical articulatory interface |
US7635447B2 (en) * | 2006-02-17 | 2009-12-22 | Biomet Manufacturing Corp. | Method and apparatus for forming porous metal implants |
US20070198093A1 (en) * | 2006-02-17 | 2007-08-23 | Amedica Corporation | Spinal implant with offset keels |
US20070288021A1 (en) * | 2006-06-07 | 2007-12-13 | Howmedica Osteonics Corp. | Flexible joint implant |
WO2008016713A2 (en) * | 2006-08-02 | 2008-02-07 | Inframat Corporation | Lumen-supporting devices and methods of making and using |
US20080069854A1 (en) * | 2006-08-02 | 2008-03-20 | Inframat Corporation | Medical devices and methods of making and using |
US8147861B2 (en) | 2006-08-15 | 2012-04-03 | Howmedica Osteonics Corp. | Antimicrobial implant |
NZ550531A (en) * | 2006-10-12 | 2009-05-31 | Canterprise Ltd | A method of producing an implant with an improved bone growth surface |
ES2729425T3 (en) | 2006-10-24 | 2019-11-04 | Biomet 3I Llc | Deposition of discrete nanoparticles on a nanostructured surface of an implant |
NL1032851C2 (en) * | 2006-11-10 | 2008-05-14 | Fondel Finance B V | Kit and method for fixing a prosthesis or part thereof and / or filling bony defects. |
US20080131604A1 (en) * | 2006-11-30 | 2008-06-05 | Shuangbiao Liu | Textured coating on a component surface |
US20080150028A1 (en) * | 2006-12-21 | 2008-06-26 | Advanced Micro Devices, Inc. | Zero interface polysilicon to polysilicon gate for semiconductor device |
CN101657564A (en) | 2007-02-12 | 2010-02-24 | 莲花应用技术有限责任公司 | Prepare matrix material with ald |
WO2008109016A1 (en) * | 2007-03-05 | 2008-09-12 | Signal Medical Corporation | Metal/alloy coated ceramic |
US8066770B2 (en) * | 2007-05-31 | 2011-11-29 | Depuy Products, Inc. | Sintered coatings for implantable prostheses |
EP2170222B1 (en) * | 2007-06-11 | 2022-02-23 | Smith & Nephew, Inc. | Ceramic layered medical implant |
US20090010990A1 (en) * | 2007-06-20 | 2009-01-08 | Little Marisa A | Process for depositing calcium phosphate therapeutic coatings with controlled release rates and a prosthesis coated via the process |
EP2014319A1 (en) | 2007-07-09 | 2009-01-14 | Astra Tech AB | A bone tissue implant comprising strontium ions |
EP2014259A1 (en) * | 2007-07-09 | 2009-01-14 | Astra Tech AB | A bone tissue implant comprising lithium ions |
EP2022447A1 (en) | 2007-07-09 | 2009-02-11 | Astra Tech AB | Nanosurface |
WO2009014718A1 (en) | 2007-07-24 | 2009-01-29 | Porex Corporation | Porous laser sintered articles |
CN101842062B (en) * | 2007-09-25 | 2013-04-03 | 拜欧米特制造公司 | Cementless tibial tray |
WO2009040124A1 (en) * | 2007-09-26 | 2009-04-02 | Straumann Holding Ag | Dental implant system |
WO2009097218A1 (en) | 2008-01-28 | 2009-08-06 | Biomet 3I, Llc | Implant surface with increased hydrophilicity |
GB0809721D0 (en) * | 2008-05-28 | 2008-07-02 | Univ Bath | Improvements in or relating to joints and/or implants |
US20110059149A1 (en) * | 2008-06-16 | 2011-03-10 | Little Marisa A | Process for depositing calcium phosphate therapeutic coatings with different release rates and a prosthesis coated via the process |
US8414671B2 (en) * | 2008-10-06 | 2013-04-09 | Augustine Biomedical And Design, Llc | Personal air filtration device for use with bedding structure |
GB0821927D0 (en) * | 2008-12-01 | 2009-01-07 | Ucl Business Plc | Article and method of surface treatment of an article |
EP2199423B1 (en) * | 2008-12-16 | 2013-04-17 | Sulzer Metco AG | Thermally injected surface layer and orthopaedic implant |
US8696759B2 (en) * | 2009-04-15 | 2014-04-15 | DePuy Synthes Products, LLC | Methods and devices for implants with calcium phosphate |
US9399086B2 (en) * | 2009-07-24 | 2016-07-26 | Warsaw Orthopedic, Inc | Implantable medical devices |
US9173748B2 (en) * | 2009-08-07 | 2015-11-03 | Ebi, Llc | Toroid-shaped spinal disc |
US20110035010A1 (en) * | 2009-08-07 | 2011-02-10 | Ebi, Llc | Toroid-shaped spinal disc |
US8124187B2 (en) * | 2009-09-08 | 2012-02-28 | Viper Technologies | Methods of forming porous coatings on substrates |
US20110089041A1 (en) * | 2009-10-19 | 2011-04-21 | Biomet Manufacturing Corp. | Methods of depositing discrete hydroxyapatite regions on medical implants |
US20110143127A1 (en) * | 2009-12-11 | 2011-06-16 | Biomet Manufacturing Corp. | Methods for coating implants |
EP2512383B1 (en) | 2009-12-14 | 2016-04-13 | Ascension Orthopedics, Inc. | Humeral head resurfacing implant |
US8641418B2 (en) | 2010-03-29 | 2014-02-04 | Biomet 3I, Llc | Titanium nano-scale etching on an implant surface |
US8388887B2 (en) | 2010-04-12 | 2013-03-05 | Biomet Manufacturing Corp. | Methods for making textured ceramic implants |
WO2011130506A1 (en) * | 2010-04-15 | 2011-10-20 | Synthes Usa, Llc | Coating for a cocrmo substrate |
CA2798710C (en) | 2010-05-11 | 2019-08-27 | Venkat R. Garigapati | Organophosphorous, multivalent metal compounds, & polymer adhesive interpenetrating network compositions & methods |
EP2389901B8 (en) * | 2010-05-24 | 2013-05-15 | Episurf IP Management AB | An implant for cartilage repair |
CN103052410B (en) * | 2010-07-09 | 2015-04-22 | 欧瑞康贸易股份公司(特吕巴赫) | Antibacterial medicinal product and method for producing same |
US8727203B2 (en) | 2010-09-16 | 2014-05-20 | Howmedica Osteonics Corp. | Methods for manufacturing porous orthopaedic implants |
WO2012088490A1 (en) * | 2010-12-23 | 2012-06-28 | Orchid Orthopedics Solutions, Llc | Orthopedic implant and method of making same |
DE102011010899A1 (en) * | 2011-02-04 | 2012-08-09 | Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. | Method of creating a three-dimensional structure and three-dimensional structure |
US8728563B2 (en) | 2011-05-03 | 2014-05-20 | Palmaz Scientific, Inc. | Endoluminal implantable surfaces, stents, and grafts and method of making same |
WO2012158527A2 (en) | 2011-05-13 | 2012-11-22 | Howmedica Osteonics | Organophosphorous & multivalent metal compound compositions & methods |
US9351834B2 (en) | 2011-09-12 | 2016-05-31 | Biomet Manufacturing, Llc | Negative-positive pressurizable implant |
US9408686B1 (en) | 2012-01-20 | 2016-08-09 | Conformis, Inc. | Devices, systems and methods for manufacturing orthopedic implants |
US9364896B2 (en) | 2012-02-07 | 2016-06-14 | Medical Modeling Inc. | Fabrication of hybrid solid-porous medical implantable devices with electron beam melting technology |
EP2828100B1 (en) | 2012-03-20 | 2018-05-16 | Biomet 3i, LLC | Surface treatment for an implant surface |
US9180010B2 (en) | 2012-04-06 | 2015-11-10 | Howmedica Osteonics Corp. | Surface modified unit cell lattice structures for optimized secure freeform fabrication |
US9135374B2 (en) | 2012-04-06 | 2015-09-15 | Howmedica Osteonics Corp. | Surface modified unit cell lattice structures for optimized secure freeform fabrication |
FR2991573A1 (en) * | 2012-06-08 | 2013-12-13 | Tornier Sa | FEMORAL KNEE PROSTHESIS COMPONENT, METHOD FOR MANUFACTURING SUCH COMPONENT, AND PROSTHETIC COMPRISING SUCH COMPONENT |
US9636229B2 (en) | 2012-09-20 | 2017-05-02 | Conformis, Inc. | Solid freeform fabrication of implant components |
IN2015DN02636A (en) | 2012-09-21 | 2015-09-18 | Conformis Inc | |
US9370605B2 (en) | 2013-03-04 | 2016-06-21 | Howmedica Osteonics Corp. | Cobalt chrome coated titanium implant |
US9271839B2 (en) | 2013-03-14 | 2016-03-01 | DePuy Synthes Products, Inc. | Femoral component for an implantable hip prosthesis |
ITMI20132154A1 (en) * | 2013-12-20 | 2015-06-21 | Adler Ortho S R L | FEMORAL COMPONENT FOR KNEE PROSTHESIS. |
JP6573908B2 (en) | 2014-05-12 | 2019-09-11 | インテグラ・ライフサイエンシーズ・コーポレイションIntegra LifeSciences Corporation | Total joint replacement prosthesis |
US10687956B2 (en) | 2014-06-17 | 2020-06-23 | Titan Spine, Inc. | Corpectomy implants with roughened bioactive lateral surfaces |
EP3034033A1 (en) | 2014-12-16 | 2016-06-22 | Nobel Biocare Services AG | Dental implant |
TWI726940B (en) | 2015-11-20 | 2021-05-11 | 美商泰坦脊柱股份有限公司 | Processes for additively manufacturing orthopedic implants |
CN105559947A (en) * | 2015-12-15 | 2016-05-11 | 广州中国科学院先进技术研究所 | Preparation method of porous implant filled with O-intersecting lines units |
EP3493768A1 (en) | 2016-08-03 | 2019-06-12 | Titan Spine, Inc. | Implant surfaces that enhance osteoinduction |
CN106264802A (en) * | 2016-08-05 | 2017-01-04 | 北京爱康宜诚医疗器材有限公司 | Knee-joint prosthesis |
US11039938B2 (en) | 2017-07-26 | 2021-06-22 | Optimotion Implants LLC | Modular knee prothesis |
US11406502B2 (en) | 2017-03-02 | 2022-08-09 | Optimotion Implants LLC | Orthopedic implants and methods |
US10905436B2 (en) | 2017-03-02 | 2021-02-02 | Optimotion Implants, Llc | Knee arthroplasty systems and methods |
US10638970B2 (en) | 2017-03-08 | 2020-05-05 | Strive Orthopedics, Inc | Method for identifying human joint characteristics |
US10537658B2 (en) | 2017-03-28 | 2020-01-21 | DePuy Synthes Products, Inc. | Orthopedic implant having a crystalline gallium-containing hydroxyapatite coating and methods for making the same |
US10537661B2 (en) | 2017-03-28 | 2020-01-21 | DePuy Synthes Products, Inc. | Orthopedic implant having a crystalline calcium phosphate coating and methods for making the same |
US11298747B2 (en) | 2017-05-18 | 2022-04-12 | Howmedica Osteonics Corp. | High fatigue strength porous structure |
CN108103428B (en) * | 2017-11-14 | 2019-11-01 | 上海交通大学 | A kind of surface treatment method of medical metal material |
US10973658B2 (en) | 2017-11-27 | 2021-04-13 | Titan Spine, Inc. | Rotating implant and associated instrumentation |
US11135070B2 (en) | 2018-02-14 | 2021-10-05 | Titan Spine, Inc. | Modular adjustable corpectomy cage |
SE543241C2 (en) | 2018-04-27 | 2020-10-27 | Episurf Ip Man Ab | An implant for cartilage and/or bone repair |
EP3954400A1 (en) * | 2020-08-10 | 2022-02-16 | Waldemar Link GmbH & Co. KG | Coating of a structured implant surface |
CN112522666B (en) * | 2021-02-05 | 2022-09-20 | 中南大学湘雅医院 | Artificial joint composite coating based on titanium alloy matrix and preparation method thereof |
Family Cites Families (63)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
CA962806A (en) | 1970-06-04 | 1975-02-18 | Ontario Research Foundation | Surgical prosthetic device |
GB1462876A (en) | 1973-05-17 | 1977-01-26 | Thackray C F Ltd | Knee arthroplasty |
US4038703A (en) * | 1975-11-14 | 1977-08-02 | General Atomic Company | Prosthetic devices having a region of controlled porosity |
US4216549A (en) | 1977-06-02 | 1980-08-12 | Purdue Research Foundation | Semi-stable total knee prosthesis |
US4166292A (en) | 1977-09-08 | 1979-09-04 | Carbomedics, Inc. | Stress reinforced artificial joint prostheses |
US4491987A (en) | 1979-09-24 | 1985-01-08 | Clemson University | Method of orthopedic implantation and implant product |
US5192324A (en) * | 1982-02-18 | 1993-03-09 | Howmedica Inc. | Bone prosthesis with porous coating |
US4818559A (en) | 1985-08-08 | 1989-04-04 | Sumitomo Chemical Company, Limited | Method for producing endosseous implants |
US4718905A (en) * | 1986-08-13 | 1988-01-12 | Freeman Jerre M | Haptic element using ion beam implantation for an intraocular lens |
IT1202437B (en) | 1987-01-28 | 1989-02-09 | Cremascoli Spa G | STRUCTURE OF TOTAL ANCHOR PROSTHESIS, INCLUDING A FEMORAL COMPONENT AND AN ACETABULAR COMPONENT, REALIZED, BOTH, PART IN METAL MATERIAL AND PART IN CERAMIC MATERIAL |
US6083570A (en) * | 1987-03-31 | 2000-07-04 | Lemelson; Jerome H. | Synthetic diamond coatings with intermediate amorphous metal bonding layers and methods of applying such coatings |
US5176712A (en) * | 1988-04-12 | 1993-01-05 | Tranquil Prospects Ltd. | Endoprostheses with resorption preventing means |
US4978358A (en) * | 1988-10-06 | 1990-12-18 | Zimmer Inc. | Orthopaedic prosthetic device possessing improved composite stem design |
ATE85507T1 (en) | 1989-03-17 | 1993-02-15 | Thull Roger | ACETABULUM FOR CEMENTLESS IMPLANTATION IN THE ACETABULUM OF THE HIP BONE. |
NZ233403A (en) * | 1989-04-28 | 1992-09-25 | Mcneil Ppc Inc | Simulated capsule-like medicament |
US5545227A (en) * | 1989-12-21 | 1996-08-13 | Smith & Nephew Richards, Inc. | Biocompatible low modulus medical implants |
US5702448A (en) * | 1990-09-17 | 1997-12-30 | Buechel; Frederick F. | Prosthesis with biologically inert wear resistant surface |
CA2031571A1 (en) | 1990-12-05 | 1992-06-06 | The University Of British Columbia | Antibiotic loaded joint prosthesis |
US5198308A (en) | 1990-12-21 | 1993-03-30 | Zimmer, Inc. | Titanium porous surface bonded to a cobalt-based alloy substrate in an orthopaedic implant device |
EP0525210A4 (en) * | 1991-02-20 | 1993-07-28 | Tdk Corporation | Composite bio-implant and production method therefor |
JP2997330B2 (en) | 1991-03-29 | 2000-01-11 | 京セラ株式会社 | Hip prosthesis |
GB9202248D0 (en) | 1992-02-03 | 1992-03-18 | Howmedica | Prosthesis for attachement without bone cement and method of attaching |
US5372130A (en) | 1992-02-26 | 1994-12-13 | Djs&T Limited Partnership | Face mask assembly and method having a fan and replaceable filter |
US5366507A (en) * | 1992-03-06 | 1994-11-22 | Sottosanti John S | Method for use in bone tissue regeneration |
US5344458A (en) | 1992-08-06 | 1994-09-06 | Bonutti Peter M | Arthroplasty component |
US5723011A (en) * | 1992-12-21 | 1998-03-03 | Zimmer, Inc. | Prosthetic implant and method of making same |
US5876454A (en) * | 1993-05-10 | 1999-03-02 | Universite De Montreal | Modified implant with bioactive conjugates on its surface for improved integration |
US5368881A (en) * | 1993-06-10 | 1994-11-29 | Depuy, Inc. | Prosthesis with highly convoluted surface |
US5665118A (en) * | 1994-02-18 | 1997-09-09 | Johnson & Johnson Professional, Inc. | Bone prostheses with direct cast macrotextured surface regions and method for manufacturing the same |
US5443523A (en) | 1994-03-18 | 1995-08-22 | Mikhail; W. E. Michael | Femoral stem cement mantle |
US5593719A (en) * | 1994-03-29 | 1997-01-14 | Southwest Research Institute | Treatments to reduce frictional wear between components made of ultra-high molecular weight polyethylene and metal alloys |
EP0774931B1 (en) * | 1994-08-12 | 2003-06-25 | Diamicron, Inc. | Prosthetic joint with at least one diamond coated interface |
DE4435680A1 (en) * | 1994-10-06 | 1996-04-11 | Merck Patent Gmbh | Porous bone substitute materials |
JP3681396B2 (en) * | 1994-11-30 | 2005-08-10 | インプラント・イノヴェーションズ・インコーポレーテッド | Implant surface preparation |
US5998024A (en) | 1995-02-02 | 1999-12-07 | Rainer H. Frey | Biocompatible material and method of manufacture and use thereof |
US5820707A (en) | 1995-03-17 | 1998-10-13 | Teledyne Industries, Inc. | Composite article, alloy and method |
US5688557A (en) * | 1995-06-07 | 1997-11-18 | Lemelson; Jerome H. | Method of depositing synthetic diamond coatings with intermediates bonding layers |
US5658338A (en) | 1995-09-29 | 1997-08-19 | Tullos; Hugh S. | Prosthetic modular bone fixation mantle and implant system |
AU7456596A (en) | 1995-10-31 | 1997-05-22 | Clarence F. Batchelder | Prosthetic joint and method of manufacture |
KR970025573A (en) | 1995-11-09 | 1997-06-24 | 황성관 | Artificial hip |
US6087553A (en) | 1996-02-26 | 2000-07-11 | Implex Corporation | Implantable metallic open-celled lattice/polyethylene composite material and devices |
GB2312168B (en) | 1996-04-17 | 1999-11-03 | Finsbury | Meniscal knee prosthesis |
EP0803234B1 (en) | 1996-04-23 | 2004-11-17 | Biomet Limited | Methods of manufacturing an acetabular cup |
US5746272A (en) * | 1996-09-30 | 1998-05-05 | Johnson & Johnson Professional, Inc. | Investment casting |
NL1004207C2 (en) | 1996-10-04 | 1998-04-07 | Accis B V | Joint prosthesis. |
US5981827A (en) * | 1996-11-12 | 1999-11-09 | Regents Of The University Of California | Carbon based prosthetic devices |
EP0944368B1 (en) | 1996-11-21 | 2003-02-05 | Plus Endoprothetik Ag | Artificial acetabular cup |
EP0860213A3 (en) | 1997-01-03 | 2002-10-16 | Therapol SA | Bioactive coating on surfaces |
ES2171010T3 (en) * | 1997-02-04 | 2002-08-16 | Bekaert Sa Nv | COVERING THAT INCLUDES COATS OF DIAMOND TYPE CARBON COMPOSITIONS AND DIAMOND TYPE NANOCOMPOSTS. |
ATE273036T1 (en) * | 1997-03-27 | 2004-08-15 | Smith & Nephew Inc | METHOD FOR PRODUCING CONSTANT THICKNESS OXIDES ON ZIRCONIUM ALLOYS |
MY122234A (en) * | 1997-05-13 | 2006-04-29 | Inst Neue Mat Gemein Gmbh | Nanostructured moulded bodies and layers and method for producing same |
US6008432A (en) * | 1997-10-01 | 1999-12-28 | Osteonics Corp. | Metallic texture coated prosthetic implants |
US5938702A (en) | 1997-10-31 | 1999-08-17 | Sulzer Orthopedics Inc. | Locking mechanism for acetabular cup |
US6045581A (en) | 1997-12-12 | 2000-04-04 | Sulzer Orthopedics Inc. | Implantable prosthesis having textured bearing surfaces |
US6139585A (en) * | 1998-03-11 | 2000-10-31 | Depuy Orthopaedics, Inc. | Bioactive ceramic coating and method |
US6261322B1 (en) * | 1998-05-14 | 2001-07-17 | Hayes Medical, Inc. | Implant with composite coating |
US6827742B2 (en) | 1998-05-14 | 2004-12-07 | Daniel E. E. Hayes, Jr. | Bimetal acetabular component construct for hip joint prosthesis |
AU2695799A (en) | 1998-05-22 | 1999-12-02 | Howmedica Osteonics Corp. | Acetabular cup assembly with selected bearing |
NL1009550C2 (en) | 1998-07-03 | 2000-01-10 | Straten Beheer B V Van | Joint prosthesis, in particular finger joint prosthesis. |
US6096175A (en) * | 1998-07-17 | 2000-08-01 | Micro Therapeutics, Inc. | Thin film stent |
US6280476B1 (en) | 1998-10-16 | 2001-08-28 | Biomet Inc. | Hip joint prosthesis convertible in vivo to a modular prosthesis |
DE50015178D1 (en) | 1999-08-10 | 2008-07-10 | Zimmer Gmbh | Artificial knee joint |
US6368354B2 (en) | 1999-10-07 | 2002-04-09 | Exactech, Inc. | Acetabular bearing assembly for total hip joints |
-
1998
- 1998-05-14 US US09/079,502 patent/US6261322B1/en not_active Expired - Lifetime
-
1999
- 1999-04-16 AU AU36501/99A patent/AU3650199A/en not_active Abandoned
- 1999-04-16 EP EP99918636A patent/EP1093384B1/en not_active Expired - Lifetime
- 1999-04-16 AT AT99918636T patent/ATE415983T1/en not_active IP Right Cessation
- 1999-04-16 WO PCT/US1999/008456 patent/WO1999058167A1/en active Application Filing
- 1999-04-16 DE DE69940020T patent/DE69940020D1/de not_active Expired - Lifetime
- 1999-04-16 CA CA002354065A patent/CA2354065A1/en not_active Abandoned
-
2001
- 2001-07-09 US US09/901,310 patent/US7105030B2/en not_active Expired - Fee Related
-
2006
- 2006-01-10 US US11/329,273 patent/US7445640B2/en not_active Expired - Fee Related
-
2008
- 2008-11-04 US US12/290,876 patent/US8167954B2/en not_active Expired - Lifetime
-
2010
- 2010-12-14 US US12/928,636 patent/US20110295381A1/en not_active Abandoned
Cited By (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20150069111A1 (en) * | 2012-06-18 | 2015-03-12 | DePuy Synthes Products, LLC | Dual modulus hip stem and method of making the same |
US10213310B2 (en) | 2012-06-18 | 2019-02-26 | DePuy Synthes Products, Inc. | Dual modulus hip stem and method of making the same |
US11020232B2 (en) * | 2012-06-18 | 2021-06-01 | DePuy Synthes Products, Inc. | Dual modulus hip stem and method of making the same |
Also Published As
Publication number | Publication date |
---|---|
US7105030B2 (en) | 2006-09-12 |
US20110295381A1 (en) | 2011-12-01 |
US6261322B1 (en) | 2001-07-17 |
US20020016635A1 (en) | 2002-02-07 |
US7445640B2 (en) | 2008-11-04 |
ATE415983T1 (en) | 2008-12-15 |
US20090254191A1 (en) | 2009-10-08 |
WO1999058167A1 (en) | 1999-11-18 |
DE69940020D1 (en) | 2009-01-15 |
EP1093384B1 (en) | 2008-12-03 |
US8167954B2 (en) | 2012-05-01 |
EP1093384A1 (en) | 2001-04-25 |
AU3650199A (en) | 1999-11-29 |
US20060178751A1 (en) | 2006-08-10 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US6261322B1 (en) | Implant with composite coating | |
US7578851B2 (en) | Gradient porous implant | |
JP4339606B2 (en) | Porous metal scaffolding | |
EP1365711B1 (en) | Orthopedic implants having ordered microgeometric surface patterns | |
EP1923079B1 (en) | Articular prothesis with a metallic part coated with wear resistant ceramic | |
de Viteri et al. | Titanium and titanium alloys as biomaterials | |
US6319285B1 (en) | Ceramic acetabular cup with metal coating | |
CA2523167C (en) | Prosthetic acetabular cups | |
US4865608A (en) | Grooved endoprosthesis | |
US20090012611A1 (en) | Plasma sprayed porous coating for medical implants | |
US8932663B2 (en) | Pyrocarbon coated bone implants | |
Lee et al. | Biological performance of calcium phosphate films formed on commercially pure Ti by electron-beam evaporation | |
JP2013059673A (en) | Oxidized zirconium on porous structure for bone implant use | |
JP2012130715A (en) | Open-pore biocompatible surface layer for implant, method for manufacturing the same, and use | |
WO2012110816A1 (en) | Coating method | |
Voinarovych et al. | Fabrication and characterization of Zr microplasma sprayed coatings for medical applications | |
JP3752332B2 (en) | Artificial hip joint | |
Goharian et al. | Vapor deposition process for osseoconductive surface engineering | |
Zhang | Biomedical Coatings Made by Thermal Spraying for Orthopaedic Joint Applications | |
US20230404764A1 (en) | Medical Implant and Related Methods | |
JP3709055B2 (en) | Artificial hip joint | |
CN114672801A (en) | Preparation method of renovation mortar cup coating and renovation mortar cup |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
EEER | Examination request | ||
FZDE | Discontinued |