A total hip surface replacement implant, comprising a femur component and an acetabular cup component, wherein the femur component is in a half-spherical shell shape and is formed by polyether ether ketone (PEEK) or derivatives thereof; the shape of the acetabular cup component matches that of the femur component, and the acetabular cup component is tightly attached to an outer surface of the half-spherical shell of the femur component; the acetabular cup component is formed by ultrahigh molecular weight polyethylene; or the femur component can be formed by ultrahigh molecular weight polyethylene, and meanwhile the acetabular cup component is formed by polyether ether ketone (PEEK) or derivatives thereof. The total hip surface replacement implant employs friction combination between organic polymers so as to reduce material toxicity against a living body; the rigidity of the organic polymers more matches that of a natural bone of a human body, thereby reducing implant wearing in a usage process; and by means of an optimization design of a positioning column on a femur condyle, the clinic problems of early neck-of-femur fracture and medium-and-long term bone resorption are avoided.

In the present disclosure, an artificial joint shell includes a base and a coating film. The base has a cup shape and includes an outer surface including a first region and a second region adjacent to the first region. The coating film contains a calcium phosphate-based material and an antimicrobial material and is disposed across the first region and the second region of the outer surface of the base. A surface of the coating film in the first region has a larger surface roughness than a surface of the coating film in the second region.

In the present disclosure, an artificial joint shell includes a base and a coating film. The base has a cup shape and includes an outer surface including a first region and a second region adjacent to the first region. The coating film contains a calcium phosphate-based material and an antimicrobial material and is disposed across the first region and the second region of the outer surface of the base. A surface of the coating film in the first region has a larger surface roughness than a surface of the coating film in the second region.

Described herein are hydrogels attached to a base with the strength and fatigue comparable to that of cartilage on bone and methods of forming them. The methods and apparatuses described herein may achieve an attachment strength between a hydrogel and a substrate equivalent to the osteochondral junction. In some examples the hydrogel may be a triple-network hydrogel (such as BC-PVA-PAMPS) that is attached to a porous substrate (e.g., a titanium base) with the shear strength and fatigue strength equivalent to that of the osteochondral junction.

Described herein are hydrogels attached to a base with the strength and fatigue comparable to that of cartilage on bone and methods of forming them. The methods and apparatuses described herein may achieve an attachment strength between a hydrogel and a substrate equivalent to the osteochondral junction. In some examples the hydrogel may be a triple-network hydrogel (such as BC-PVA-PAMPS) that is attached to a porous substrate (e.g., a titanium base) with the shear strength and fatigue strength equivalent to that of the osteochondral junction.

A biocompatible Mg—P coating on the surface of a zinc-based biomedical material, and a preparation method and use thereof are disclosed. In the method, zinc and a zinc alloy are first subjected to surface pretreatment and then soaked in a phosphate solution at a constant temperature to form the Mg—P coating through chemical liquid deposition (CLD). The control on the composition, thickness and surface morphology of the coating is realized by using the CLD method. The biocompatible Mg—P coating has a thickness of 0.5 μm to 50 μm, is dense and uniform, and comprises a main component of zinc-magnesium-phosphate and a small amount of zinc phosphate.

A biocompatible Mg—P coating on the surface of a zinc-based biomedical material, and a preparation method and use thereof are disclosed. In the method, zinc and a zinc alloy are first subjected to surface pretreatment and then soaked in a phosphate solution at a constant temperature to form the Mg—P coating through chemical liquid deposition (CLD). The control on the composition, thickness and surface morphology of the coating is realized by using the CLD method. The biocompatible Mg—P coating has a thickness of 0.5 μm to 50 μm, is dense and uniform, and comprises a main component of zinc-magnesium-phosphate and a small amount of zinc phosphate.

The invention relates to a biodegradable implant comprising a surface coated magnesium alloy or zinc alloy product, whereby the coating layer comprises oxides and/or phosphates of from rare-earth elements, Mg, Ca, Zn, Zr, Cu, Fe, Sr, Li, Mn or Ag wherein the coating is preferably generated by plasma electrolytically oxidation (PEO). The invention further comprises a method for preparing the coated magnesium or zinc alloy product of the implant.

The invention relates to a biodegradable implant comprising a surface coated magnesium alloy or zinc alloy product, whereby the coating layer comprises oxides and/or phosphates of from rare-earth elements, Mg, Ca, Zn, Zr, Cu, Fe, Sr, Li, Mn or Ag wherein the coating is preferably generated by plasma electrolytically oxidation (PEO). The invention further comprises a method for preparing the coated magnesium or zinc alloy product of the implant.

The present invention relates to a material for bone implants, comprising: a surface of oxidic ceramic materials, titanium or polyether ether ketone (PEEK) or other polymer or composite materials, a matrix of collagen or gelatin, which is covalently bound to said surface, and calcium phosphate embedded into said matrix. The present invention further relates to a method for producing the material according to the invention, to bone implants comprising the material according to the invention, and to its use as a bone implant material.