A cable includes a sheath, and a coating film covering a circumference of the sheath, the coating film adhering to the sheath. The coating film is formed from a rubber composition including a rubber component and fine particles. A static friction coefficient on a surface of the coating film is 0.5 or less. When the coating film is subjected to a testing such that a long fiber non-woven fabric including cotton linters including an alcohol for disinfection with a length of 50 mm along a wiping direction is brought contiguous to the surface of the coating film at a shearing stress of 2×10.sup.−3 MPa to 4×10.sup.−3 MPa, followed by wiping off the surface of the coating film at a speed of 80 times/min to 120 times/min and 20,000 repetitions thereof for a wiping direction length of 150 mm, a difference (an absolute value of a difference) between the static friction coefficients of the coating film before and after the testing is not greater than 0.1.

Tubing, such as medical tubing for administration of intravenous fluid, can include an outer layer on an inner layer, and, optionally additional layers, in which at least the outer layer and the inner layer are made of a same polymeric material but the outer and inner layers have differing amounts or differing types of a plasticizer such that a hardness of the outer layer is greater than a hardness of the inner layer.

Implantable medical devices are provided. In one embodiment, a device includes a body having an external surface defining an outer profile of the device. The body includes a porous matrix including a series of interconnected macropores defined by a plurality of interconnected struts each including a hollow interior. A filler material substantially fills at least a portion of the series of interconnected macropores. The external surface of the body includes a plurality of openings communicating with the hollow interior of at least a portion of the plurality of interconnected struts. In a further aspect of this embodiment, the external surface includes exposed areas of the filler material and porous matrix in addition to the exposed openings. In another aspect, the porous matrix is formed from a bioresorbable ceramic and the filler material is a biologically stable polymeric material. Still, other aspects related to this and other embodiments are also disclosed.

Hemostatic devices for promoting blood clotting can include a substrate (e.g., gauze, textile, sponge, sponge matrix, one or more fibers, etc.), a hemostatic material disposed thereon such as kaolin clay, and a binder material such as crosslinked calcium alginate with a high guluronate monomer molar percentage disposed on the substrate to substantially retain the hemostatic material. When the device is used to treat a bleeding wound, at least a portion of the clay material comes into contact with blood to accelerate clotting. Moreover, when exposed to blood, the binder has low solubility and retains a majority of the clay material on the gauze. A bandage that can be applied to a bleeding wound to promote blood clotting includes a flexible substrate and a gauze substrate mounted thereon.

A cable includes a sheath, and a coating film covering a circumference of the sheath, the coating film adhering to the sheath. The coating film is formed from a rubber composition including a rubber component and fine particles. A static friction coefficient on a surface of the coating film is 0.5 or less. When the coating film is subjected to a testing such that a long fiber non-woven fabric including cotton linters including an alcohol for disinfection with a length of 50 mm along a wiping direction is brought contiguous to the surface of the coating film at a shearing stress of 210.sup.3 MPa to 410.sup.3 MPa, followed by wiping off the surface of the coating film at a speed of 80 times/min to 120 times/min and 20,000 repetitions thereof for a wiping direction length of 150 mm, a difference (an absolute value of a difference) between the static friction coefficients of the coating film before and after the testing is not greater than 0.1.

Iron-based biodegradable metals and the method of fabricating are disclosed. The iron-based biodegradable metals, which have an accelerated degradation rate and a yield strength similar to stainless steel, comprises a composite structure of multiple iron layers separated by thin alloying metallic layers. The composite structure are built layer by layer using additive manufacturing technologies. The iron-based biodegradable metals can be fabricated into a small diameter tube for laser cutting into implantable bare metal stents or drug eluting stents with biodegradable polymer coating. The iron-based biodegradable metals can be fabricated and/or machined into orthopedic implants.

Disclosed herein are embodiments of a conductive polymer doped with silica nanoparticles. In several embodiments, a coated electrode comprising a coating of the conductive polymer on a conductive surface of the electrode is provided. In some embodiments, the silica nanoparticles of the conductive polymer are mesoporous and are loaded with a pharmaceutical agent. Methods of using the conductive polymer doped with silica nanoparticles are also provided, including methods of recording or stimulating a bioelectric signal and methods of administering a pharmaceutical agent to a subject.

A coating film is provided in a cable, a medical hollow tube, a molded article and a hollow tube. The coating film is formed from a rubber composition including a rubber component and fine particles. A static friction coefficient on a surface of the coating film is 0.5 or less. When the coating film is subjected to a testing such that a long fiber non-woven fabric including cotton linters including an alcohol for disinfection with a length of 50 mm along a wiping direction is brought contiguous to the surface of the coating film at a shearing stress of 210.sup.3 MPa to 410.sup.3 MPa, followed by wiping off the surface of the coating film at a speed of 80 times/min to 120 times/min and 20,000 repetitions thereof for a wiping direction length of 150 mm, a difference (an absolute value of a difference) between the static friction coefficients of the coating film before and after the testing is not greater than 0.1.

A coating for an electrosurgical electrode to reduce the potential for sticking of tissue. The coating is an elastomer containing a plurality of diamond particles having an average diameter of between diameter of 0.5 and 500 nanometers and that comprise between 0.1 and 25 percent by weight of the coating. The coating may be formed by reducing a silicone dispersion with xylene, adding the plurality of diamond particles, and agglomerating the plurality of diamond particles through sonification and then applied to the device. The coasting may also be formed by reducing a silicone dispersion with xylene, adding the plurality of diamond particles, and agglomerating the plurality of diamond particles through sonification, and then applied to the device by plasma enhanced vapor deposition.

A cable includes a sheath, and a coating film covering a circumference of the sheath, the coating film adhering to the sheath. The coating film is formed from a rubber composition including a rubber component and fine particles. A static friction coefficient on a surface of the coating film is 0.5 or less. When the coating film is subjected to a testing such that a long fiber non-woven fabric including cotton linters including an alcohol for disinfection with a length of 50 mm along a wiping direction is brought contiguous to the surface of the coating film at a shearing stress of 210.sup.3 MPa to 410.sup.3 MPa, followed by wiping off the surface of the coating film at a speed of 80 times/min to 120 times/min and 20,000 repetitions thereof for a wiping direction length of 150 mm, a difference (an absolute value of a difference) between the static friction coefficients of the coating film before and after the testing is not greater than 0.1.