A method of treating an aneurysm, including determining a diameter associated with a vessel having the aneurysm; selecting one of a plurality of braided implants for treating the vessel, wherein each braided implant comprises a porosity substantially consistent over up to a 1 mm diameter range, each braided implant configured to provide consistent porosity over different diameter ranges; and treating the vessel with the one of the plurality of braided implants.

Systems and methods for deploying a stent within the frontal sinus. The stent includes flexible foam and film layers arranged in a stacked configuration and furled within a cartridge prior to deployment. The cartridge is removably coupled to an applicator device including an actuator. The film layer may include a polymer having a resilience sufficient to unfurl the stent and maintain patency of the frontal sinus opening. The flexible foam layer may have porosity of greater than 80%, and an active agent may be within the flexible foam layer. The flexible foam layer may be bioresorbable and the flexible film layer biocompatible and non-biodegradable. The stent may include first and second body portions with the first body portion independently unfurling from the second body portion to retain the stent within the frontal sinus. Contouring of the first and second body portions may facilitate ease with removal of the stent.

Systems and methods for deploying a stent within the frontal sinus. The stent includes flexible foam and film layers arranged in a stacked configuration and furled within a cartridge prior to deployment. The cartridge is removably coupled to an applicator device including an actuator. The film layer may include a polymer having a resilience sufficient to unfurl the stent and maintain patency of the frontal sinus opening. The flexible foam layer may have porosity of greater than 80%, and an active agent may be within the flexible foam layer. The flexible foam layer may be bioresorbable and the flexible film layer biocompatible and non-biodegradable. The stent may include first and second body portions with the first body portion independently unfurling from the second body portion to retain the stent within the frontal sinus. Contouring of the first and second body portions may facilitate ease with removal of the stent.

A device and a method for treatment of a urethra that is constricted due to benign prostatic hyperplasia (BPH) are provided, including a delivery tool (101) advanced to a location in an area of the urethra that is to be treated. The delivery tool (101) includes an expandable element (400) that expands within the urethra such as to enlarge the urethra, a tissue cutter (412) that forms a cut in the urethra, subsequently to the expandable element expanding to dilate the urethra, and an implant (410) that maintain the urethra in a dilated state. The implant (410) includes a shape-memory material and is shaped to define two end sections and a middle section (1202) disposed between the two end sections. The shape memory-material is shape set such that in an unconstrained configuration of the implant (410), the middle section (1202) is substantially straight. Other embodiments are also described.

The acute and chronic devices and methods described herein include a body lumen fluid flow modulator including an upstream flow accelerator and a downstream flow decelerator. The fluid flow modulator preferably includes one or more openings that define a gap/entrainment region that provides a pathway through which additional fluid from a branch lumen(s) is entrained into the fluid stream flowing from the upstream flow accelerator to the downstream flow decelerator. Delivery devices including a sheath and inner assembly also are provided for delivering the flow modulator to the body lumen. The delivery device may maintain the flow modulator in its collapsed, delivery state upon retraction of the sheath for ease of readjustment within the body lumen prior to full deployment of the flow modulator within the body lumen.

A tack device for holding plaque against blood vessel walls in treating atherosclerotic occlusive disease can be formed as a thin, annular band of durable, flexible material. The tack device may also have a plurality of barbs or anchoring points on its outer annular periphery. The annular band can have a length in the axial direction of the blood vessel walls that is about equal to or less than its diameter as installed in the blood vessel. A preferred method is to perform angioplasty with a drug eluting balloon as a first step, and if there is any dissection to the blood vessel caused by the balloon angioplasty, one or more tack devices may be installed to tack down the dissected area of the blood vessel surface.

A method of making a self-expanding stent entails applying a bend stress sufficient to over-bend a portion of a wire by an amount in a range from about 85% to about 105%, where the wire comprises a Ni—Ti alloy and includes from about 40% to about 46% cold work. The bend stress is then released, thereby forming a bend having a predetermined bend angle in the wire. The application and release of the bend stress are repeated on successive portions of the wire in order to create a series of bends along a length of the wire in a predetermined bend pattern. The wire comprising the predetermined bend pattern is then positioned about a mandrel in an expanded stent geometry and heat set. Thus, a self-expanding stent is formed.

A method of making a self-expanding stent entails applying a bend stress sufficient to over-bend a portion of a wire by an amount in a range from about 85% to about 105%, where the wire comprises a Ni—Ti alloy and includes from about 40% to about 46% cold work. The bend stress is then released, thereby forming a bend having a predetermined bend angle in the wire. The application and release of the bend stress are repeated on successive portions of the wire in order to create a series of bends along a length of the wire in a predetermined bend pattern. The wire comprising the predetermined bend pattern is then positioned about a mandrel in an expanded stent geometry and heat set. Thus, a self-expanding stent is formed.

A synthetic heart valve is made from a valve graft of synthetic material and more particularly expanded polytetrafluoroethylene (ePTFE). The valve graft has an upper portion defined by a first thickness and a lower portion defined by a second thickness which is greater than the first thickness. The valve graft is formed into a cylindrical sleeve having a diameter and a folded region. A flexible stent overlays the cylindrical sleeve, wherein a series of leaflets are formed in the lower portion of the sleeve, the leaflets defining a semicircular perimeter. The leaflets are sutured to the cylindrical sleeve and the cylindrical sleeve is sutured to the flexible stent, the stent having a plurality of bent cylindrical wire segments that are welded together and in which the sleeve is sutured to the wire, including the welded areas of the stent. The formed valve can be implanted using a balloon catheter.

A synthetic heart valve is made from a valve graft of synthetic material and more particularly expanded polytetrafluoroethylene (ePTFE). The valve graft has an upper portion defined by a first thickness and a lower portion defined by a second thickness which is greater than the first thickness. The valve graft is formed into a cylindrical sleeve having a diameter and a folded region. A flexible stent overlays the cylindrical sleeve, wherein a series of leaflets are formed in the lower portion of the sleeve, the leaflets defining a semicircular perimeter. The leaflets are sutured to the cylindrical sleeve and the cylindrical sleeve is sutured to the flexible stent, the stent having a plurality of bent cylindrical wire segments that are welded together and in which the sleeve is sutured to the wire, including the welded areas of the stent. The formed valve can be implanted using a balloon catheter.