An endoscopic submucosal injection material containing: a water-soluble resin having a weight-average molecular weight of 10,000 or more; an organic compound having two or more hydroxyl groups and having a molecular weight of 400 or less; and water is provided, in which the endoscopic submucosal injection material has an electrical conductivity of 500 mS/m or less, and an osmotic pressure ratio of the endoscopic submucosal injection material to physiological saline is 0.7 to 1.5.

Novel formulations for electrospun, electrowoven, and otherwise formed polymer stents and implants are disclosed herein.

Compounds comprising R-G-Cysteic Acid (i.e., R-G-NHCH(CH.sub.2SO.sub.3H)COOH or Arg-Gly-NHCH(CH.sub.2SO.sub.3H)COOH) and derivatives thereof, including pharmaceutically acceptable salts, hydrates, stereoisomers, multimers, cyclic forms, linear forms, drug-conjugates, pro-drugs and their derivatives. Also disclosed are methods for making and using such compounds including methods for inhibiting integrins including but not necessarily limited to .sub.5.sub.1-Integrin, .sub.v.sub.3-Integrin and .sub.v.sub.5-Integrin, inhibiting cellular adhesion to RGD binding sites, preventing or treating viral or other microbial infections, inhibiting angiogenesis in tumors, retinal tissue or other tissues or delivering other diagnostic or therapeutic agents to RGD binding sites in human or animal subjects.

Meshes for use to control the movement of bodily fluids, such as blood, are described herein. The mesh can be partially or completely biodegradable or non-biodegradable. In one embodiment, the mesh is formed from one or more self-assembling peptides. The peptides can be in the form of fibers, such as nanofibers. The peptides can be assembled prior to formation of the mesh or after the mesh has been formed but before it is applied. Alternatively, the mesh can be prepared from unassembled peptides, which assemble at the time of application. The peptides can assemble upon contact with bodily fluids (e.g., blood) or can be contacted with an ionic solution to initiate assembly.

Meshes for use to control the movement of bodily fluids, such as blood, are described herein. The mesh can be partially or completely biodegradable or non-biodegradable. In one embodiment, the mesh is formed from one or more self-assembling peptides. The peptides can be in the form of fibers, such as nanofibers. The peptides can be assembled prior to formation of the mesh or after the mesh has been formed but before it is applied. Alternatively, the mesh can be prepared from unassembled peptides, which assemble at the time of application. The peptides can assemble upon contact with bodily fluids (e.g., blood) or can be contacted with an ionic solution to initiate assembly.

The present invention relates to a method for producing a protein-functionalized film, in which a protein is bound to a copolymer or a polymer having an unhydrolyzed or hydrolyzed thiolactone functionalization is bound to the film by means of the existing functionalization. The present invention also relates to a correspondingly produced film.

Compounds comprising R-G-Cysteic Acid (i.e., R-G-NHCH(CH.sub.2SO.sub.3H)COOH or Arg-Gly-NHCH(CH.sub.2SO.sub.3H)COOH) and derivatives thereof, including pharmaceutically acceptable salts, hydrates, stereoisomers, multimers, cyclic forms, linear forms, drug-conjugates, pro-drugs and their derivatives. Also disclosed are methods for making and using such compounds including methods for inhibiting cellular adhesion to RGD binding sites or delivering other diagnostic or therapeutic agents to RGD binding sites in human or animal subjects.

A laser is used to form openings within a graft material to selectively enhance permeability of a prosthesis for tissue integration therein. A feature of utilizing a laser to create the openings for tissue integration builds from its tunability. More particularly, the laser precisely places openings in any pattern and location, and on any textile that forms the graft material. Further, the power and focus of the laser is precisely adjusted to control the diameter and shape of the openings. All parameters of the openings can be controlled at will, allowing for the opportunity to selectively enhance and optimize the permeability of the graft material in a vessel.

The techniques of this disclosure generally relate to a prosthesis including framed biodegradable yarn graft material having a frame and biodegradable yarns combined with the frame. The biodegradable yarns seal tissue integration openings within the frame. The frame provides long term mechanical strength while the biodegradable yarns provide acute strength and impermeability to prevent endoleaks. As the biodegradable yarns degrade, the drop in textile density creates tissue integration openings, through which tissue grows. The integrate of tissue into the framed biodegradable yarn graft material provides biological fixation of the prosthesis in vessels and prevents endoleaks and migration of the prosthesis.

The techniques of this disclosure generally relate to a variable permeability layered prosthesis including an impermeable outer layer and a permeable inner layer. The impermeable outer layer is well suited to seal a dissection opening of a dissection. The permeable inner layer allows fluid to enter into a dead space between the impermeable outer layer and the permeable inner layer. The fluid in the dead space coagulates in the dead space providing a media for tissue growth into the prosthesis. The ability of tissue to integrate into the prosthesis provides biological fixation of the prosthesis in vessels and prevents endoleaks and migration of the prosthesis.