A medical device and a method and process for at least partially forming a medical device, which medical device has improved physical properties. The one or more improved physical properties of the novel metal alloy can be achieved in the medical device without having to increase the bulk, volume and/or weight of the medical device.

An anchor for an embolic coil, and an embolic coil including the same are provided. The anchor for an embolic coil includes a hollow main body and a central shaft arranged in the hollow main body, wherein the hollow main body is made of a braided composite filament including a polymer filament and a first alloy filament, and the central shaft includes a second alloy filament that is a material different from the first alloy filament.

The present invention relates to the preparation methods and applications of biodegradable zinc-copper alloys, which can be applied to medical implant materials. The alloy of present invention is mainly composed of copper (1-10 wt. %), the balance of zinc and trace impurity elements. As-cast alloy ingot is homogenized and then hot processed to refine microstructure. The mechanical properties of the alloys are improved due to the refined microstructure. The alloys are capable of being further fabricated into micro-tubes, wires and plates. There are many advantages of these Zn alloys such as excellent mechanical properties, easy to process, appropriate corrosion resistance, good biocompatibility and so on, which correspondingly can be applied to many kinds of biodegradable medical implant devices. With excellent mechanical properties, good biocompatibility and degrading completely in 6-18 months, the Zn alloys meet the requirements of implant materials for mechanical properties and biosafety.

A method of using an implantable device provides an implantable device including a plurality of arcs. Each arc contains a multiplicity of links. The implantable device further includes a device closure pin, a lock-in unit attached and located between the three arcs, and a quick-release unit attached and located between three arcs. The plurality of arcs, the lock-in unit, and the release unit form a closed contour. The closed contour of the implantable device, in a rigid state is a three-dimensional shape.

An endoluminal prosthesis includes an implantable scaffold and/or stent substrate which is convertible from a compressed first geometric shape to a radially dilated dimensionally stable second tubular second geometric shape, the scaffold and/or stent substrate comprising a bioresorbable zinc alloy, the zinc alloy including at least at least four alloying elements selected from the group consisting of silver (Ag) in an amount of about 1.0 wt. % to about 6.0 wt. %, manganese (Mn) in an amount of about 0.1 wt. to about 2.0 wt. %, zirconium (Zr) in an amount of about 0.05 wt. % to about 1.0 wt. %, copper (Cu) in an amount of about 0.5 wt. % to about 1.2 wt. %, and optionally titanium (Ti) in an amount of 0 to about 0.4 wt. %, with the balance of the alloy being zinc and incidental impurities.

An implantable medical device (IMD) may include an outer housing having a titanium outer surface, the titanium outer surface including a plurality of titanium atoms. A tissue growth-inhibiting layer may extend over the titanium outer surface. In some cases, the tissue growth-inhibiting layer may include a plurality of polyethylene glycol molecules, at least some of the plurality of polyethylene glycol molecules covalently bonded via an ether bond to one of the plurality of titanium atoms.

A patient-specific drill template for spine screw placement includes a hook-shaped main body, and an insertion guiding portion that guides a spine screw to be inserted into a vertebra. The main body includes a tight contact portion and a hook portion, the tight contact portion connecting with insertion guiding portion, the hook portion extending from the tight contact portion, and the main body partially surrounds the vertebra. A method of preparing a patient-specific drill template for spine screw placement includes preparing a three-dimensional computed tomography of a lumbar or thoracic spine in a hospital; transferring the CT data to the manufacturing facility using a network; processing the computed tomography to generate a three-dimensional reconstruction template of the patient-specific drill template in the facility; preparing the patient-specific drill template based on the reconstruction template; packaging the template and sterilizing the patient-specific drill template.

Magnesium alloy containing, in % by mass, 1.0 to 2.0% of Zn, 0.05 to 0.80% by mass of Zr, 0.05 to 0.40% by mass of Mn, and the balance consisting of Mg and unavoidable impurities. The magnesium alloy may further contain, in % by mass, 0.005% or more and less than 0.20% of Ca.

The present invention concerns a process for the production of implants with an ultrahydrophilic surface as well as the implants produced in that way and also processes for the production of loaded, so-called bioactive implant surfaces of metallic or ceramic materials, which are used for implants such as artificial bones, joints, dental implants or also very small implants, for example what are referred to as stents, as well as implants which are further produced in accordance with the processes and which as so-called “delivery devices” allow controlled liberation, for example by way of dissociation, of the bioactive molecules from the implant materials.

A medical device includes a base layer, and a lubrication layer supported on at least a part of the base layer, wherein the lubrication layer contains a block copolymer (A) composed of a first constituting unit derived from a reactive monomer that has an epoxy group and a second constituting unit derived from at least one hydrophilic monomer selected from the group consisting of acrylamide and an acrylamide derivative, and a polymer (B) composed of a constituting unit derived from at least one hydrophilic monomer selected from the group consisting of acrylamide and an acrylamide derivative, wherein the block copolymer (A) is contained in a proportion of 20 to 80% by weight relative to the total weight of the block copolymer (A) and the polymer (B), and wherein the block copolymer (A) is crosslinked or polymerized to form a mesh structure.