Various aspects of the present disclosure provide compositions including a water-insoluble therapeutic agent and a gallate-containing compound. Other aspects provide methods of using such compositions.

Provided is a biodegradable polymer coating stent effective in delaying the damage of physical properties (particularly radial force) of a core structure. The stent includes a core structure of a bioabsorbable material (e.g., Mg), a first coating layer of a first polymer with biodegradability, and a second coating layer of a second polymer with biodegradability, wherein the first coating layer covers the whole surface of the core structure; the second coating layer covers a part or the whole surface of the first coating layer; the first polymer has a glass transition point of lower than 37° C.; and the second polymer has a glass transition point of 47° C. or higher.

A balloon catheter is disclosed capable of effectively delivering a drug to living body tissue and a manufacturing method of the balloon catheter, and a treatment method. The balloon catheter has a balloon at a distal portion of a catheter shaft, and is provided on a surface of the balloon with elongate bodies which are crystals of a water-insoluble drug extending in a longitudinal direction. The surface of the balloon is provided with crystal conjugates formed of a plurality of elongate bodies united to one another while being in a tilted state.

This document provides methods and materials for treating a mammal (e.g., a human) having one or more stenotic blood vessels. For example, amnion coated balloons that can be used in balloon angioplasty are provided.

A medical device may comprise a body including a mixture of polyvinylpyrrolidone (“PVP”) and mitomycin. The medical device may be in any size or shape such that the medical device may be inserted into living tissue, including, but not limited to, a lacrimal punctal plug and a stent. The mixture of PVP and mitomycin may be coated on a portion of the medical device, contained within a cavity on the medical device, disposed on the surface of the medical device or configured as part of the medical device such that the mixture of PVP and mitomycin can be delivered to tissue.

Provided are a method of manufacturing a stent for drug release that may be coated with a drug by forming a 3D nanostructured film on the surface of a stent and a stent for drug release manufactured thereby, more particularly, a method of manufacturing a stent for drug release including: (a) preparing a stent, (b) forming a 3D nanostructured film on a surface of the stent; and (c) surface-treating the 3D nanostructured film, and a stent for drug release manufactured thereby.

Various aspects of the present invention provide compositions and implantable devices including a water-insoluble therapeutic agent solubilized in a matrix of a gallate-containing compound. Other aspects provide methods of manufacturing and using such compositions and devices.

The present disclosure provides for a medical device or a substrate coated with polydopamine which is further linked to ligands such as antibodies and/or antibody fragments. The polydopamine coating and the ligands may be linked through a linker such as an organic polymer.

A balloon catheter system for infusion of micelles at high pressure. The system includes a catheter with a drug eluting balloon with a perforated wall with numerous pores, a reservoir of nanoparticles in an aqueous solution disposed within the balloon or in fluid communication with the balloon. The particles may comprise drug loaded micelles, where the micelles are provided in the size range of 40 to 250 nm generally (0.040 μm to 0.250 μm), and the pores of the balloon wall are configured to allow passage of the micelles with a minimum of disruption, The pores are conical, with the diameter of the pore at the inside of the balloon wall smaller than the diameter of the pores at the outside of the balloon wall.

The invention provides liquid injectable copolymers of TMC and HTMC that are degradable in vivo. Degradation can be tailored by adjusting the amount of HTMC in the copolymer, the initial molecular weight of the copolymer, and the characteristics of the initiator used in its preparation. Specifically, the degradation rate increases as the amount of HTMC incorporated into the copolymer increases, as the molecular weight of the copolymer decreases, and as the hydrophobicity of the initiator decreases. Moreover, the degradation yields products such as glycerol and carbon dioxide that are non-toxic in vivo, and which will not cause a substantive change in tissue pH upon implantation in vivo. The copolymers may be used in applications such as drug delivery and as coatings.