The present invention aims to provide a method for producing a porous substrate containing a bioabsorbable polymer and heparin in a simple manner without use of a surfactant, a porous substrate containing a bioabsorbable polymer and heparin, and an artificial blood vessel. The present invention provides a method for producing a porous substrate containing a bioabsorbable polymer and heparin, including: a solution preparing step of preparing a heparin-bioabsorbable polymer solution having heparin uniformly dispersed therein and a bioabsorbable polymer dissolved therein, using the bioabsorbable polymer, the heparin, a solvent 1 that is a poor solvent having a lower solvency for the bioabsorbable polymer, a solvent 2 that is a good solvent having a higher solvency for the bioabsorbable polymer and is incompatible with the solvent 1, and a common solvent 3 compatible with the solvent 1 and the solvent 2; a precipitating step of cooling the heparin-bioabsorbable polymer solution to precipitate a porous body containing the bioabsorbable polymer and the heparin; and a freeze-drying step of freeze-drying the porous body containing the bioabsorbable polymer and the heparin to provide a porous substrate containing the heparin.

A crystallized bioabsorbable polymer scaffold comprises a polymer composition of poly (L-lactide-co-tri-methylene-carbonate) or poly (D-lactide-co-tri-methylene-carbonate) or poly (L-lactide-co-ε-caprolactone) or poly (D-lactide-co-ε-caprolactone) in the form of block copolymers of blocky copolymers, wherein the scaffold is cold-bendable.

A composite lumen includes an extruded tube of a composite including a poly(glycerol sebacate) (PGS) matrix mixed with a PGS thermoset filler. The composite lumen also includes an overbraid structure overlying an outer surface of the extruded tube. A method of forming a composite lumen includes extruding a PGS tube of a composite including a PGS matrix mixed with a PGS thermoset filler. The method also includes applying an overbraid structure over an outer surface of the extruded tube.

Methods for preparing oriented polymer tubes, such as biodegradable polymer tubes suitable for in vivo use, are provided herein. The disclosed methods provide alternatives to the typical extrusion/expansion methods by which oriented polymeric tubes for such uses are commonly produced. Advantageously, the disclosed methods can provide more homogeneous molecular orientation of crystallizable polymers within the tube walls, which can endow such polymeric tubes with enhanced strength (e.g., resistance to compression) and toughness.

Biodegradable self-expanding polymer stent has an outer diameter of 0.25-40 mm, length of 5-250 mm, and closed-cell wall structure formed by struts, where ratio of inner diameter values before crimping and after crimping is in a range of 3 to 5, and made of a copolymer obtained from L-lactide, D-lactide, D,L-lactide, meso-lactide, glycolide, ε-caprolactone, trimethylene carbonate, p-dioxanone and compounds comprising functional groups capable of photopolymerization; supramolecular structure of the copolymer is oriented substantially circularly in a transversal cross section of the stent. Method of manufacturing includes extruding a tube of a polymer material; annealing the extruded polymer tube; laser cutting the extruded polymer tube to form a stent workpiece; heating the stent to above glass transition temperature of the polymer, crimping the stent workpiece uniformly over the entire outer surface thereof, and quenching at about minus 20 degrees Celsius; placing the quenched stent on a delivery means.

A prosthetic tissue valve and a method of treating the prosthetic tissue valve are provided. The method includes: decreasing a temperature of a chamber carrying the prosthetic tissue valve from a first preset temperature to a second preset temperature in a first cooling rate; decreasing the temperature of the chamber carrying the prosthetic tissue valve from the second preset temperature to a third preset temperature in a second cooling rate; and performing a drying process to the prosthetic tissue valve. The second preset temperature is a critical crystallization temperature and is greater than a crystallization temperature of the prosthetic tissue valve. The third preset temperature is lower than the crystallization temperature of the prosthetic tissue valve, and the second cooling rate is greater than the first cooling rate.

A personalized naturally designed mitral valve prosthesis and a method for manufacturing the such to precisely fit a specific patient for which the valve prosthesis is made for, is provided. The method includes measuring size and shape of a mitral valve of the specific patient by using imaging means, building a 3D model of the personalized mitral valve prosthesis, optimizing the 3D model using FEM method and fabricating the personalized mitral valve prosthesis by cutting and connecting the annular ring, leaflets and chords to form a personalized prosthesis mitral valve.

The present invention relates generally to a method that is used to create three-dimensional synthetic vascular networks. Micromachining and molding techniques are used to create a template in a shape that mimics a biological network. Cellular material can be seeded around the template or a space created by the template and grown into an engineered tissue-construct.

Provided herein is a cell macroencapsulation device composed of hydrogel in a 3D conformation that optimizes encapsulated cell viability and function when transplanted into a vascularized tissue space. The hydrogel macroencapsulation device is intended to reduce or eliminate immune response to the cell graft, while allowing exchange of encapsulated cell-secreted products, such as insulin. Also described herein is an injection-mold and fabrication process to generate the hydrogel macroencapsulation devices for use in the clinic.

A composite implant device for use in a medical application, comprising a synthetically-derived mesh that mimics particular critical aspects of a biologically-derived mesh. The composite implant device can be used for the reinforcement and reconstruction of tissues within the body and can be comprised of a majority of synthetic components and minority of naturally-derived components which mimic the structure and function of a naturally-derived mesh.