Thin-film mesh for medical devices, including stent and scaffold devices, and related methods are provided. Micropatterned thin-film mesh, such as thin-film Nitinol (TFN) mesh, may be fabricated via sputter deposition on a micropatterned wafer. The thin-film mesh may include slits to be expanded into pores, and the expanded thin-film mesh used as a cover for a stent device. The stent device may include two stent modules that may be implanted at a bifurcated aneurysm such that one module passes through a medial surface of the other module. The thin-film mesh may include pores with complex, fractal, or fractal-like shapes. The thin-film mesh may be used as a scaffold for a scaffold device. The thin-film scaffold may be placed in a solution including structural protein such as fibrin, seeded with cells, and placed in the body to replace or repair tissue.

An implantable shunting device configured to shunt blood from the left atrium of the heart to the azygous vein through an aperture in the atrial septal wall is provided. The device comprises a flexible tube configured for radial adjustment between a contracted delivery configuration suitable for delivery in a delivery catheter and a deployed radially expanded configuration, the tube having a through lumen, a distal end configured to anchor within the azygous vein, and a proximal end configured to span an aperture in an atrial septal wall and anchor to the wall to provide fluid communication between the left atrium and the azygous vein. Methods of treating heart disease by implanting a shunting device of the invention are also disclosed.

The techniques of this disclosure generally relate to an assembly including a docking graft. The docking graft includes a main graft defining a main lumen, a first internal lumen within the main lumen, a second internal lumen within the main lumen, and a main docking lumen within the main lumen. The first and second internal lumens are configured to receive first and second bridging stent graft therein. The main docking lumen is configured to receive a tube graft therein. The first internal lumen, the second internal lumen, and the main docking lumen being parallel to one another and extending an entire length of the docking graft when the docking graft is in a relaxed configuration. The docking graft forms the foundation, or anchor device, for attachment of the first bridging stent graft, the second bridging stent graft, and the tube graft within the aorta.

The techniques of this disclosure generally relate to an iliac branch device having an external iliac body, a common iliac branch, and an internal iliac branch. A diameter of the proximal opening of the common iliac branch is greater than a diameter of a distal opening of the external iliac body. The iliac branch device is configured to be deployed without going up and over the aortic bifurcation and without using some form of supra-aortic antegrade access such as through brachial or axillary artery access. This simplifies the procedure and reduces procedure time thus maximizing the success rate of the procedure and allows the procedure to be performed on a broad patient population.

The techniques of this disclosure generally relate to a stent-graft system including a bifurcated stent-graft, a first bifurcating branch device, and a first branch extension. The bifurcated stent-graft includes a body, a first branch limb, and a second branch limb. The first bifurcating branch device includes a body segment coupled to the first branch limb of the bifurcated stent-graft, a first branch limb, and a second branch limb. The first branch extension is within the first branch limb of the first bifurcating branch device and within an external iliac artery. The first bifurcating branch device has a wide patient applicability since the treatment can be extended proximal to the anatomical iliac bifurcation and is not limited by the common iliac artery length. The stent-graft system is suitable to treat a wide range of internal and external iliac artery diameters.

A staged-deployment stent graft assembly. A main stent graft has a sacrificial port extending therefrom. The stent graft has a compressed state and an expanded state. The staged-deployment stent graft assembly also includes an internal stent cuff located within the stent graft. The internal stent cuff has a constricted state and a non-constricted state. The internal stent cuff may be biased to expand from the constricted state to the non-constricted state to close the sacrificial port when the main stent graft is in the expanded state. The assembly also includes a filament structure maintaining the internal stent cuff in the constricted state. The assembly further includes a release configured to manipulate the filament structure to transition the internal stent cuff from the constricted state to the non-constricted state to close the sacrificial port when the main stent graft is in the expanded state.

Devices and associated methods are disclosed for improving the fixation of the stent graft to the wall of the abdominal aortic neck and to increase the tightness of the aneurysmal sac from the main lumen of the abdominal aorta. Particular embodiments are directed to a bifurcated stent graft system for the treatment of the abdominal aortic aneurysm, which includes an aortic bifurcation segment, two iliac segments and an additional inner segment. The aortic bifurcation segment contains a main tubular body with branched legs at the distal end made of biocompatible fabric material attached to and supported by stents. The proximal end of the aortic bifurcation segment is configured to engage with a part of the aorta, without aneurysmal dilatation, proximal to the renal arteries and contains only a metal expandable frame (for example, a stent), without fabric material, but with fixing pins for engagement with the aortic wall proximal to the renal arteries. The part of the aortic bifurcation segment placed in the proximal neck of the abdominal aortic aneurysm is made only of stent/stents, without biocompatible fabric material, but with fixing multidirectional (for example, caudally and cranially) pins on the outer surface for engagement with the aortic wall.

The techniques of this disclosure generally relate to modular stent device and method of deploying the same. The method includes introducing a delivery system including the modular stent device via supra aortic access. The delivery system is advanced into the ascending aorta. Once positioned, the modular stent device is deployed from the delivery system such that an artery leg of the modular stent device engages the brachiocephalic artery and a bypass gate engages the aorta, wherein the artery leg partially collapses the bypass gate. The artery leg has a greater radial force than the bypass gate such that the artery leg remains un-collapsed and opened. Accordingly, blood flow through the artery leg and perfusion of the brachiocephalic artery and preservation of blood flow to cerebral territories including the brain is insured.

A joining arrangement between a main tube and a side arm (5) in a side arm stent graft (1). The side arm (5) is stitched into an aperture (11) in the main tube and is in fluid communication with it. The aperture is triangular, elliptical or rectangular and the side arm is cut off at an angle to leave an end portion having a circumferential length equal to the circumference of the aperture. The side arm can also include a connection socket (76) comprising a first resilient ring (79) around the arm at its end, a second resilient ring (80) spaced apart along the arm from the first ring and a zig zag resilient stent (82) between the first and second rings. The zig-zag resilient stent can be a compression stent. Both the main tube and the side arm are formed from seamless tubular biocompatible graft material.

A stent graft (2) for placement in the thoracic arch of a patient has a first tubular body portion (6) with a first lumen therein for placement in the ascending aorta of a patient and a second tubular body portion (8) to extend along the thoracic arch and down the descending aorta. The second tubular body portion is of a lesser diameter than the first tubular body portion. There is a step portion (10) between the first body portion and the second body portion. The step portion is joined to and continuous with the first portion and the second portion. A first side of each of the first body portion, the step portion and the second body portion are substantially aligned so that there is a step (18) defined on a second side opposite to the first side of the body portion. There is an aperture (30) in the step portion and an internal tube (32) extending from the aperture towards the first body portion. The internal tube is divided along part of its length into at least two smaller internal tubes (34, 36) with the smaller internal tubes opening into the first lumen.