Provided is yarn for a cell culture scaffold. The yarn for a cell culture scaffold according to an exemplary embodiment of the present invention includes slitting yarn produced by cutting a compressed nanofiber web to a predetermined width. Accordingly, by creating microenvironments suitable for migration, proliferation and differentiation of cells, cell viability may be enhanced and cells may be three-dimensionally proliferated. In addition, a scaffold according to the present invention has a mechanical strength sufficient for prevention of disruption of the scaffold which occurs during cell culture, such that cells may be stably proliferated. Further, the scaffold according to the present invention uses slitting yarn formed of the compressed nanofiber web, thereby having pores with various sizes, and therefore cell proliferation and cell viability may be enhanced by creation of an extracellular matrix-like environment.

The present application provides a suture structure for medical surgery and a process for making the same. The suture structure includes: a thread head core, a winding yarn and a suture connection yarn. In particular, the thread head core is formed by bundling a plurality of thread core yarns; a connection section is provided at a first end of the suture connection yarn; the connection section is attached to the thread head core along a length direction of the thread head core; a second end of the suture connection yarn extends out from the thread head core at the middle of the thread head core; the thread head core and the connection section are wound along the length direction of the thread head core to form a thread rod; and the core yarn, the winding yarn and the suture connection yarn are made of thermoplastic resin fibers.

Nerve scaffolds are described that include a tubular outer housing fabricated from a biocompatible polymer, within which are disposed a plurality of carbon nanofiber yarns. The carbon nanofiber yarns, which can be separated by distances roughly corresponding to an average nerve fiber diameter, provide surfaces on which nerve fibers can regrow. Because the proximate carbon nanofiber yarns can support individual nerve fibers, a nerve can be regenerated with a reduced likelihood of undesirable outcomes, such as nerve pain or reduced nerve function.

Nerve scaffolds are described that include a tubular outer housing fabricated from a biocompatible polymer, within which are disposed a plurality of carbon nanofiber yarns. The carbon nanofiber yarns, which can be separated by distances roughly corresponding to an average nerve fiber diameter, provide surfaces on which nerve fibers can regrow. Because the proximate carbon nanofiber yarns can support individual nerve fibers, a nerve can be regenerated with a reduced likelihood of undesirable outcomes, such as nerve pain or reduced nerve function.

Resorbable implants comprising poly(butylene succinate) and copolymers thereof have been developed. The implants implants are preferably sterilized, and contain less than 20 endotoxin units per device as determined by the limulus amebocyte lysate (LAL) assay, and are particularly suitable for use in procedures where prolonged strength retention is necessary, and can include one or more bioactive agents. The implants may be made from fibers and meshes of poly(butylene succinate) and copolymers thereof, or by 3d printing, and the fibers may be oriented. Coverings and receptacles made from forms of poly(butylene succinate) and copolymers thereof have also been developed for use with cardiac rhythm management devices and other implantable devices. These coverings and receptacles may be used to hold, or partially/fully cover, devices such as pacemakers and neurostimulators. The coverings and receptacles are made from meshes, webs, lattices, non-wovens, films, fibers, and foams, and contain antibiotics such as rifampin and minocycline.

Resorbable implants comprising poly(butylene succinate) and copolymers thereof have been developed. The implants implants are preferably sterilized, and contain less than 20 endotoxin units per device as determined by the limulus amebocyte lysate (LAL) assay, and are particularly suitable for use in procedures where prolonged strength retention is necessary, and can include one or more bioactive agents. The implants may be made from fibers and meshes of poly(butylene succinate) and copolymers thereof, or by 3d printing, and the fibers may be oriented. Coverings and receptacles made from forms of poly(butylene succinate) and copolymers thereof have also been developed for use with cardiac rhythm management devices and other implantable devices. These coverings and receptacles may be used to hold, or partially/fully cover, devices such as pacemakers and neurostimulators. The coverings and receptacles are made from meshes, webs, lattices, non-wovens, films, fibers, and foams, and contain antibiotics such as rifampin and minocycline.

Resorbable implants comprising poly(butylene succinate) and copolymers thereof have been developed. The implants implants are preferably sterilized, and contain less than 20 endotoxin units per device as determined by the limulus amebocyte lysate (LAL) assay, and are particularly suitable for use in procedures where prolonged strength retention is necessary, and can include one or more bioactive agents. The implants may be made from fibers and meshes of poly(butylene succinate) and copolymers thereof, or by 3d printing, and the fibers may be oriented. Coverings and receptacles made from forms of poly(butylene succinate) and copolymers thereof have also been developed for use with cardiac rhythm management devices and other implantable devices. These coverings and receptacles may be used to hold, or partially/fully cover, devices such as pacemakers and neurostimulators. The coverings and receptacles are made from meshes, webs, lattices, non-wovens, films, fibers, and foams, and contain antibiotics such as rifampin and minocycline.

Resorbable implants comprising poly(butylene succinate) and copolymers thereof have been developed. The implants implants are preferably sterilized, and contain less than 20 endotoxin units per device as determined by the limulus amebocyte lysate (LAL) assay, and are particularly suitable for use in procedures where prolonged strength retention is necessary, and can include one or more bioactive agents. The implants may be made from fibers and meshes of poly(butylene succinate) and copolymers thereof, or by 3d printing, and the fibers may be oriented. Coverings and receptacles made from forms of poly(butylene succinate) and copolymers thereof have also been developed for use with cardiac rhythm management devices and other implantable devices. These coverings and receptacles may be used to hold, or partially/fully cover, devices such as pacemakers and neurostimulators. The coverings and receptacles are made from meshes, webs, lattices, non-wovens, films, fibers, and foams, and contain antibiotics such as rifampin and minocycline.

A piezoelectric base material includes an elongated inner conductor, and a piezoelectric layer covering a periphery of the inner conductor. The piezoelectric layer includes a piezoelectric yarn wound around the inner conductor, and an adhering section that maintains a state in which the piezoelectric yarn is wound around the periphery of the inner conductor. The piezoelectric yarn includes an optically active polypeptide fiber that is a fiber including an optically active polypeptide. The piezoelectric layer has an elastic modulus Y of from 1.0 GPa to 8.0 GPa as measured by a microhardness measurement in accordance with JIS Z 2255.

A biocompatible yarn comprising a conductive elastomeric filament, the conductive elastomeric filament comprising a elastomeric polymer and conductive filler.