Abstract: An implant (500, 600) includes first and second arms (14a, 14b) hinged to a base (12) at spaced-apart locations. An actuator (18, 22a, 22b, 602, 604, 606) is deployed to rotate the arms from an initial position in opposing angular motion towards a final position. A rigid bridging element (28) bridges between the arms so that deployment of the arms towards the final position displaces the bridging element away from the base. Engagement between the bridging element and at least one of the arms is via a double pin-in-slot engagement in which two non-collinear pins (30, 40) are engaged in respective non-parallel slots (32, 42).

Abstract: An implant (500, 600) includes first and second arms (14a, 14b) hinged to a base (12) at spaced-apart locations. An actuator (18, 22a, 22b, 602, 604, 606) is deployed to rotate the arms from an initial position in opposing angular motion towards a final position. A rigid bridging element (28) bridges between the arms so that deployment of the arms towards the final position displaces the bridging element away from the base. Engagement between the bridging element and at least one of the arms is via a double pin-in-slot engagement in which two non-collinear pins (30, 40) are engaged in respective non-parallel slots (32, 42).

Abstract: An implant (500, 600) includes first and second arms (14a, 14b) hinged to a base (12) at spaced-apart locations. An actuator (18, 22a, 22b, 602, 604, 606) is deployed to rotate the arms from an initial position in opposing angular motion towards a final position. A rigid bridging element (28) bridges between the arms so that deployment of the arms towards the final position displaces the bridging element away from the base. Engagement between the bridging element and at least one of the arms is via a double pin-in-slot engagement in which two non-collinear pins (30, 40) are engaged in respective non-parallel slots (32, 42).

Abstract: An implant (500, 600) includes first and second arms (14a, 14b) hinged to a base (12) at spaced-apart locations. An actuator (18, 22a, 22b, 602, 604, 606) is deployed to rotate the arms from an initial position in opposing angular motion towards a final position. A rigid bridging element (28) bridges between the arms so that deployment of the arms towards the final position displaces the bridging element away from the base. Engagement between the bridging element and at least one of the arms is via a double pin-in-slot engagement in which two non-collinear pins (30, 40) are engaged in respective non-parallel slots (32, 42).

Abstract: An implant (500, 600) includes first and second arms (14a, 14b) hinged to a base (12) at spaced-apart locations. An actuator (18, 22a, 22b, 602, 604, 606) is deployed to rotate the arms from an initial position in opposing angular motion towards a final position. A rigid bridging element (28) bridges between the arms so that deployment of the arms towards the final position displaces the bridging element away from the base. Engagement between the bridging element and at least one of the arms is via a double pin-in-slot engagement in which two non-collinear pins (30, 40) are engaged in respective non-parallel slots (32, 42).

Abstract: A prosthetic device for use as an artificial meniscus is disclosed. The prosthetic device restores shock absorption, stability, and function to the knee joint after removal of the damaged natural meniscus. In some embodiments, the prosthetic device includes an anti-migration feature. The anti-migration feature is a bridge for engagement with a femur notch in some instances. Generally, the anti-migration feature allows the artificial meniscus to be implanted into the patient's knee and maintain its position within the knee without penetrating the adjacent bone. The bridge is reinforced with fibers in some instances.

Abstract: Devices, apparatus, and systems for replacing at least some of the functionality of the natural hip joint and associated methods of implantation are disclosed. In one aspect a prosthetic acetabular cup system is provided. The system includes a metal shell comprising an outer surface for securely engaging a prepared portion of an acetabulum and an opposing inner surface. In some instances, portions of the inner and outer surfaces define an anchoring section that is deformable between an insertion configuration—where the anchoring section projects inwardly from the inner surface—and an anchoring configuration—where the anchoring section projects outwardly from the outer surface to define an anchoring protrusion for engaging the prepared portion of the acetabulum. In some embodiments, the system also includes a pliable articulating component having an outer surface including at least one engagement feature sized and shaped to engage with the metal shell.

Abstract: Methods of manufacturing prosthetic devices for use as an artificial meniscus are disclosed. In some embodiments, the methods include injection molding a resilient core material, tensioning reinforcing fibers around the injection molded core, and injection molding an outer layer to embed the reinforcing fibers within the prosthetic device. In some instances the core material is a polycarbonate polyurethane and the reinforcing fibers are made of ultra-high molecular weight polyethylene (UHMWPE) having a lower melting temperature than the polyurethane. In one particular embodiment, the core material is Bionate 80A and the reinforcing fibers are made of Dyneema. In other embodiments, methods for manufacturing a reinforced material for use in prosthetic devices is disclosed.

Abstract: Methods of manufacturing prosthetic devices for use as an artificial meniscus are disclosed. In some embodiments, the methods include injection molding a resilient core material, tensioning reinforcing fibers around the injection molded core, and injection molding an outer layer to embed the reinforcing fibers within the prosthetic device. In some instances the core material is a polycarbonate polyurethane and the reinforcing fibers are made of ultra-high molecular weight polyethylene (UHMWPE) having a lower melting temperature than the polyurethane. In one particular embodiment, the core material is Bionate 80A and the reinforcing fibers are made of Dyneema. In other embodiments, methods for manufacturing a reinforced material for use in prosthetic devices is disclosed.

Abstract: A prosthetic device for use as an artificial meniscus is disclosed. The prosthetic device restores shock absorption, stability, and function to the knee joint after removal of the damaged natural meniscus. In some embodiments, the prosthetic device includes an anti-migration feature. The anti-migration feature is a bridge for engagement with a femur notch in some instances. Generally, the anti-migration feature allows the artificial meniscus to be implanted into the patient's knee and maintain its position within the knee without penetrating the adjacent bone. The bridge is reinforced with fibers in some instances.