Shapeable porous metal implants and methods for use in various procedures are disclosed. The implants can comprise a shell according to some examples. According to one example, the method can include providing a sheet of highly porous metal material having a porosity of between 55% and 90%, and wrapping the sheet of highly porous metal material around at least a first bone of the patient. Further examples can form the sheet intra-operatively to a desired shape. In an example, the porous metal sheet can be formed of tantalum or tantalum alloys.

An alloprosthetic composite implant comprising includes a structural porous scaffold having a pore density profile corresponding to a density profile of bone to be replaced. A plurality of cells are seeded within pores of the porous scaffold and grown by incubation. The cells may include osteoblasts and/or stem cells to form the structure of the implant, and one or more cartilage layers may be grown on top of the scaffold. The pore density profile of the scaffold may be formed based on one or both of the bone density profile of the bone to be removed, and the bone density profile of the native bone that will be in contact with the alloprosthetic implant. A robot may be employed reo resect the native bone and also to shape the alloprosthetic implant to fit into place in the native bone.

An alloprosthetic composite implant comprising includes a structural porous scaffold having a pore density profile corresponding to a density profile of bone to be replaced. A plurality of cells are seeded within pores of the porous scaffold and grown by incubation. The cells may include osteoblasts and/or stem cells to form the structure of the implant, and one or more cartilage layers may be grown on top of the scaffold. The pore density profile of the scaffold may be formed based on one or both of the bone density profile of the bone to be removed, and the bone density profile of the native bone that will be in contact with the alloprosthetic implant. A robot may be employed reo resect the native bone and also to shape the alloprosthetic implant to fit into place in the native bone.

The present invention relates to a biodegradable alloy of Formula (I): Mg—Zn—X, wherein X represents —Ca—Mn or —Dy—Sr, wherein Zn is about 0.1 wt % to about 3.0 wt %, Dy is about 0.1 wt % to about 0.7 wt %, Sr is about 0.1 wt % to about 0.9 wt %, Ca is about 0.1 wt % to about 1.5 wt %, Mn is about 0.1 wt % to about 0.9 wt % and Mg is balance with impurities. The present invention further relates to a method for producing alloys, wherein the method comprises: (a) placing alloy components in a crucible, wherein the alloy components are placed in the crucible in a multilayer arrangement; (b) melting the alloy components at about 700° C. to about 850° C.; (c) stirring the melt of step (b) at about 400 rpm to about 500 rpm; (d) atomizing the melt of step (c) into millimeter size droplets using jets of inert gas; and (e) cooling and depositing the atomized alloy melt to obtain an ingot.

Disclosed is a biomedical β titanium alloy and a preparation method thereof. Its composition includes: Mo: 9.20-13.50%; Fe: 1.00-3.20%; Zr: 3.50-8.20%; Ta: 0-1.00%; the balance is Ti. The β titanium alloy is suitable for the laser additive manufacturing technology, and the prepared parts have a dense equiaxed grain structure with ultra-low grain size and a small number of columnar grain structures, which produces a fine-grain strengthening effect, and greatly improve the hardness and tribocorrosion performance of the alloy material. Also provided is a method for preparing a non-toxic, low-elasticity, and tribocorrosion resistant biomedical β titanium alloy material. A powder prepared from the above alloy components is subjected to a laser additive manufacturing technology to prepare a corresponding β titanium alloy with high-hardness, good tribocorrosion resistance and extremely low cytotoxicity. Moreover, the prepared material has good weldability and is a special metal alloy powder suitable for laser additive manufacturing.

A medical device comprising a substantially flexible porous structure. The porous structure comprises a plurality of interlocking units. Each of the plurality of interlocking units comprises a body and at least one arm. The plurality of interlocking units is configured to have space between adjacent interlocking units when the porous structure is in a neutral configuration. The plurality of interlocking units is configured to contact the respective body and arm of adjacent interlocking units when a compressive force is applied to the porous structure, thereby restricting compression of the porous structure. The plurality of interlocking units is configured to contact the respective arms of adjacent interlocking units when an extension force is applied to the porous structure, thereby restricting extension of the porous structure.

The present invention addresses the problem of providing a plasma spraying material with which it is possible to form an HAp film that has high hardness and is not susceptible to abrasion, even under conditions involving plasma spraying with low flame energy. In the present invention, an HAp powder having an average particle diameter (D.sub.50) of 15-40 μm and a pore volume of 0.01-0.30 cc/g at a pore diameter of 2000 nm or less as measured through mercury intrusion makes it possible to form an HAp film that has high hardness, is not susceptible to abrasion, and can be subjected to plasma spraying, even under conditions involving plasma spraying with low flame energy.

An implantable, autonomously growing medical device is disclosed. The device may have an outer, braided outer element that holds an inner core. Degradation and/or softening of the inner core permits the outer element to elongate, allowing the device to grow with surrounding tissue. The growth profile of the medical device can be controlled by altering the shape/material/cure conditions of the inner core, as well as the geometry of the out element.

A method of forming a shoulder prosthesis includes resecting an end portion of a humerus to form a resected end of the humerus and a resected portion separated from the humerus, the resected portion having an outer convex surface and an inner surface. The inner surface of the resected portion is processed to include a concave articular surface. The outer convex surface of the resected portion is implanted in the resected end of the humerus. An implant having a convex articular surface is secured to a glenoid. The concave articular surface of the resected portion is articulated with the convex articular surface of the implant.

The present disclosure provides a bone-implantable device and methods of use. The bone-implantable device comprises a body having an exterior surface, wherein a portion of the exterior surface includes a cured osteostimulative material comprising MgO.