US20130190676A1

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Publication number: US20130190676A1
Application number: US13/791,185
Authority: US
Inventors: Robert Julian Dickinson; Andrew Robert Pacey; Martin Terry Rothman
Original assignee: LimFlow GmbH
Current assignee: Inari Medical Inc
Priority date: 2006-04-20
Filing date: 2013-03-08
Publication date: 2013-07-25
Also published as: US20220125572A1; US20190358020A1; US9326792B2; US20160242896A1; US20170367734A1; US10390933B2; US20150126920A1; US20150250500A1; US9108018B2; US9532803B2; US9782201B2; US11241304B2; US10136987B2; US20150133845A1; US20170105834A1

Abstract

A device includes a first end portion, a second end portion, an intermediate portion between the first end portion and the second end portion, and a graft material coupled to at least the intermediate portion. The first end portion has a first end diameter. The second end portion has a second end diameter larger than the first end diameter. The intermediate portion tapers between the first end portion and the second end portion. A method of diverting fluid flow from a first passage to a second passage comprising deploying the device in a third passage between the first passage and the second passage, expanding the first end portion against sidewalls of the first passage, and expanding the second end portion against sidewalls of the second passage.

Description

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation-in-part of U.S. patent application Ser. No. 12/297,498, filed under §371(c) on Feb. 25, 2009 as a U.S. national stage of PCT Patent App. No. PCT/GB2007/001430, filed on Apr. 20, 2007, the contents of which are incorporated herein by reference in their entirety, which claims priority to GB 0607761.4, filed Apr. 20, 2006.

BACKGROUND

The present application relates to devices and methods and for use in percutaneous interventional surgery. In particular, the present application relates to devices and methods for providing or maintaining fluid flow through passages such as heart cavities and blood vessels.

Minimally invasive percutaneous surgery, commonly known as “key-hole” surgery, is a well-known surgical technique wherein surgical devices are inserted into a patient's body through a small aperture cut. For example, it is often preferable to use key-hole surgery in cardiovascular procedures, so as to avoid the substantial discomfort, need for general anesthesia, trauma, high risk of infection, and long recovery time typically associated with conventional surgery.

Key-hole surgery is often used in the treatment of coronary heart disease, in which a coronary artery is partially occluded by a blockage such as an atheroma. For example, in balloon angioplasty, a balloon catheter including a flexible, hollow tube is inserted into an artery, usually near the patient's groin, and is guided through the body to the patient's heart. The heart and the cardiac arteries may be visualised using X-ray fluoroscopy, and the tip of the catheter may be fluorescent so that its position can be determined. The catheter carries an inflatable balloon near its distal tip. The balloon is positioned in or near to the blockage, and then the balloon is inflated so as to widen or dilate the occluded blood vessel to restore blood flow through the coronary artery to the cardiac tissue.

A tubular supporting device (e.g., stent) may be deployed at the site of the blockage to prevent future occlusion (restenosis) or collapse of the blood vessel. The stent may, for example, be an expandable metal mesh tube which is carried on the balloon of the balloon catheter. While on the catheter, the tube has a relatively small diameter in comparison to the diameter of the blood vessel. The stent expands when the balloon is inflated, so that the stent pushes against the wall of the blood vessel. The stent is arranged to retain its expanded shape when it reaches its expanded position, for example by plastic deformation or by means of a mechanical locking mechanism, so as to form a resilient scaffold or support in the blood vessel. The support structure (e.g., stent) supports and dilates the wall of the blood vessel to maintain a pathway for blood to flow through the vessel. Self-expanding stents are also available, which are held in a collapsed state by a suitably adapted catheter for transport through the artery and which adopt an expanded state when deployed at the site of the blockage. The catheter may, for example, include a retaining sleeve which retains the stent in a compressed or unexpanded state. Upon removal or withdrawal of the sleeve from the stent, the stent expands to support and dilate the wall of the blood vessel.

In acute cases of coronary heart disease, where a coronary artery is severely or completely occluded, angioplasty may not be suitable. Instead, coronary bypass surgery may be required. Bypass surgery is an open-chest or open-heart procedure, and typically involves grafting a piece of healthy blood vessel onto the coronary artery so as to bypass the blockage and restore blood flow to the coronary tissue. The healthy blood vessel is usually a vein harvested from the patient's leg or arm during the course of the bypass operation. To perform the procedure, the patient's heart must be exposed by opening the chest, separating the breastbone, and cutting the pericardium surrounding the heart, resulting in significant surgical trauma.

Certain patients are unsuitable as candidates for conventional coronary bypass surgery, due low expectation of recovery or high risk from the significant trauma due to surgery, high risk of infection, absence of healthy vessels to use as bypass grafts, significant co-morbidities, and expected long and complicated recovery time associated with open-chest surgery. For example, factors such as diabetes, age, obesity, and smoking may exclude patients who are in need of treatment.

SUMMARY

Certain embodiments described herein can provide fluid flow in passages such as coronary and/or peripheral blood vessels by creating a bypass using minimally invasive surgical techniques.

In some implementations, a method of diverting fluid flow from a first passage to a second passage comprises deploying a device in a third passage between the first passage and the second passage. The device comprises a first end portion, a second portion, an intermediate portion, and a graft material. The first end portion has a first end diameter. The second end portion has a second end diameter larger than the first end diameter. The intermediate portion is between the first end portion and the second end portion. The intermediate portion tapers between the first end portion and the second end portion. The graft material is coupled to at least the intermediate portion. The method further comprises expanding the first end portion against sidewalls of the first passage and expanding the second end portion against sidewalls of the second passage.

The first passage may be an artery and the second passage may be a vein. The first passage may be a coronary artery and the second passage may be a coronary vein. The method may further comprise dilating the third passage. The first passage may be a peripheral artery and the second passage may be a peripheral vein. The method may further comprise dilating the third passage. Dilating the third passage may comprise expanding the intermediate portion. The first passage may be substantially parallel to the second passage. The intermediate portion may be conformable to an “S” shape. Expanding the first end portion and the second end portion may comprise allowing self-expansion of the first end portion and the second end portion. Expanding the first end portion and the second end portion may comprise balloon expanding at least one of the first end portion and the second end portion. Expanding one of the first end portion and the second end portion may comprise allowing self-expansion of the one of the first end portion and the second end portion and expanding the other of the first end portion and the second end portion may comprise balloon expanding the other of the first end portion and the second end portion. The method may further comprise expanding the intermediate portion.

In some implementations, a device comprises a first end portion, a second end portion, an intermediate portion, and a graft material. The first end portion has a first end diameter. The second end portion has a second end diameter smaller than the first end diameter. The intermediate portion is between the first end portion and the second end portion. The intermediate portion tapers between the first end portion and the second end portion. The graft material is coupled to at least the intermediate portion.

In some implementations, a device comprises a first end portion, a second end portion, an intermediate portion, and a graft material. The first end portion comprises a first material. The second end portion comprises a second material different than the first material. The intermediate portion is between the first end portion and the second end portion. The graft material is coupled to at least the intermediate portion.

The first material may comprise nitinol and the second material may comprise chromium cobalt. The first material may comprise nitinol and the second material may comprise stainless steel. The first end portion may comprise cut struts and the second end portion may comprise filaments. The first end portion may comprise cut struts and the second end portion may comprise cut struts. The first material may comprise an alloy and the first end portion may comprise struts or filaments having a first thickness, and the second material may comprise the alloy and the second end potion may comprise struts or filaments having a second thickness different than the first thickness. The intermediate portion may comprise a third material. The third material may comprise nitinol. The intermediate portion may comprise filaments. The intermediate portion may comprise cut struts. At least one of the first end portion and the second end portion may be substantially cylindrical. At least one of the first end portion, the second end portion, the intermediate portion, and the graft material may comprise a bioabsorbable material. At least some of the graft material may be outside the intermediate portion. At least some of the graft material may be inside the intermediate portion. At least some of the graft material may be embedded within the intermediate portion. The graft material may be coupled to at least one of the first end portion and the second end portion. The device may be capable of maintaining fluid flow between a first passage in which the first end portion is anchored and a second passage in which the second end portion is anchored. The first passage may be substantially parallel to the second passage. The intermediate portion may be conformable to an “S” shape.

In some implementations, a device comprises a support structure and a graft material. The support structure comprises a first end portion, a second end portion, and an intermediate portion between the first end portion and the second end portion. At least one of the first end portion, the second end portion, and the intermediate portion comprise cut struts and at least one of the first end portion, the second end portion, and the intermediate portion comprise filaments. The graft material is coupled to at least the intermediate portion.

The first end portion and the second end portion comprise cut struts and the intermediate portion may comprise filaments. At least some of the graft material may be outside the intermediate portion. At least some of the graft material may be inside the intermediate portion. At least some of the graft material may be embedded within the intermediate portion. The graft material may be coupled to at least one of the first end portion and the second end portion. The device may be capable of maintaining fluid flow between a first passage in which the first end portion is anchored and a second passage in which the second end portion is anchored. The first passage may be substantially parallel to the second passage. The intermediate portion may be conformable to an “S” shape.

The device may have a diameter between about 1 mm and about 12 mm (e.g., between 2 mm and 6 mm). The device may have a diameter between about 1 mm and about 10 mm (e.g., between 4 mm and 8 mm). The device may have a diameter between about 6 mm and about 25 mm (e.g., between 12 mm and 15 mm). The device may have a diameter between about 20 mm and about 50 mm (e.g., between 35 mm and 40 mm). The device may have a length between about 25 mm and about 150 mm (e.g., between 70 mm and 110 mm). The device may include filaments having a diameter between about 0.001 inches and about 0.01 inches (e.g., between 0.003 inches and 0.006 inches). The device may include struts having a diameter between about 0.001 inches and about 0.01 inches (e.g., between 0.003 inches and 0.006 inches).

In some embodiments, a device for providing or maintaining fluid flow through at least one passage in a human or animal body includes two end portions for anchoring the device in position and an intermediate portion that allows movement of the end portions relative to each another. The end portions and the intermediate portion together define a pathway for fluid flow through the device.

By allowing the two end portions to move relative to each other, the device can respond to movement of the passage or passages in which the device is used. The intermediate portion may be flexible to allow relative movement of the end portions. In some embodiments, the device has varying or differential flexibility along the length of the device or along a length of a portion of the device. Device flexibility can reduce the likelihood of device failure due to fatigue, for example because the magnitude of stresses within the intermediate portion may be relatively low in comparison to stresses on a support structure (e.g., stent) with uniform flexibility along its entire length.

The device may be configured to provide or maintain fluid flow through a single passageway, for example an occluded blood vessel. The intermediate portion may be capable of maintaining fluid flow between proximal and distal portions of the occluded blood vessel. The intermediate portion can pass through a further passage, for example outside the blood vessel, extending between the proximal and distal portions of the blood vessel. The device may be configured for use as a bypass between proximal and distal portions of a single blood vessel, for example an artery or a vein.

The device may be configured to provide fluid flow from an occluded blood passage to another passage. The passages can be interconnected by the intermediate portion passing through a further passage extending between the two passages. The device may be configured for use as a shunt between two passages, for example between an artery and a vein.

In embodiments in which the end portions can move relative to one another by virtue of the intermediate portion, the device may be suitable for use in applications where the end portions are anchored in separate passages that move relative to one another. A pathway for fluid communication to be maintained through the device irrespective of the relative movement of the end portions, and the likelihood of fatigue failure of the device due to cyclic movement of the end portions may be low in comparison to a support structure (e.g., stent) lacking such an intermediate portion.

One or both of the end portions may be diametrically expandable to anchor the device in position. An expanded end portion may, for example, be expandable to meet with and press against the inner sidewalls of a passage to inhibit or prevent substantial sliding or rotation of the end portion within the passage, and/or to dilate the passage. The intermediate portion may be diametrically expandable, for example to dilate the fluid flow pathway.

The device may be in the form of a tube defining a lumen configured to act as a fluid flow pathway. In some embodiments, the tube may be fluid-tight, so as to confine the fluid flow within the lumen of the tube. The tube may include, but is not limited to, a polymeric material, for example a biocompatible polymer such as polytetrafluoroethylene (PTFE) or polyurethane such as polycarbonate aromatic biodurable thermoplastic polyurethane elastomer (e.g., ChronoFlex C® 80A and 55D medical grade, available from AdvanSource Biomaterials of Wilmington, Mass.).

The device may include a supporting structure that supports the end portions. The supporting structure may support the intermediate portion, in which case the supporting structure may be flexible within the intermediate portion to allow movement of the end portions relative to each other.

When a supporting structure is provided, the supporting structure or a portion thereof may be embedded within a wall of the tube. Alternatively or in addition, the structure or a portion of the structure may be located on the outside of the tube or within the lumen of the tube.

The supporting structure may include at least one mesh. For example, a single mesh may extend along the entire length of the device. In another example, each end of the device includes a mesh, in which case the meshes may stop short of the intermediate portion or may extend into the intermediate portion. When a mesh is present in the intermediate portion, the mesh may have a higher density or smaller window size (e.g., a smaller spacing between filaments and/or struts of the mesh) in the end portions than in the intermediate portion so that the device is relatively more flexible in the intermediate portion than in the end portions. The device may be relatively more flexible in the intermediate portion than in the end portions by way of absence of a mesh, or even when including a mesh with substantially uniform or uniform density or window size (e.g., due to factors other than mesh density or window size), or by including a mesh having a non-uniform density.

At least one mesh may include biocompatible metal wire. For example, the metal wire may be stainless steel. Alternatively, or in addition, at least one mesh may include a shape memory material, for example nitinol and/or chromium cobalt. When a shape memory material is used, at least a portion of the device may be self-expanding.

One or both end portions may include anchoring protuberances or barbs capable of and/or configured to dig into or grasp the inside sidewalls of a passage, for example to prevent or reduce slippage or other movement of the or each end portion relative to the passage.

The two end portions may have different diameters, so that the device can be made to fit securely within a passage having variable diameter, or with one end portion in a first passage and the other end portion in a second passage, when the passages have different diameters. The device can be configured for a particular application and/or for a particular patient.

In some embodiments, a method of diverting fluid flow from a first passage to a second passage (e.g., adjacent to the first passage) includes forming a third passage between the first and second passages, providing a device having two end portions and an intermediate portion, deforming the intermediate portion of the device to permit insertion of the device in the passages, and expanding the end portions against the walls of the first and second passages so as to anchor the device in the passages. The intermediate portion of the device may be flexed to permit insertion of the device in the passages. The two end portions and the intermediate portion may be configured to maintain or provide fluid flow through the device.

One or more end portions of the device may be expanded by a balloon catheter. Alternatively, or in addition, at least one end portion may be self-expanding, in which case the method may include providing the device in a retaining sleeve, and removing the retaining sleeve to enable the at least one end portion to expand.

The method may further include expanding the intermediate portion to dilate the third passage, thereby forming a larger pathway for fluid flow from the first passage to the second passage.

The methods described herein may be used in many surgical procedures, and can be performed by minimally invasive (key-hole) techniques. The methods may be particularly suitable for the treatment of coronary heart disease, for example by providing a shunt or bypass to divert arterial blood from an occluded coronary artery to a coronary vein (e.g., adjacent to the coronary artery) and/or by traversing an occlusion in a coronary artery by exiting the artery proximal to the occlusion, extending through subintimal tissue, external tissue, and/or a portion of a proximate vessel, and reentering the coronary artery distal to the occlusion, for peripheral vascular disease such as critical limb ischemia, for example by providing a shunt or bypass to divert arterial blood from an occluded peripheral artery to a peripheral vein and/or by traversing an occlusion in a peripheral vessel by exiting the vessel proximal to the occlusion, extending through subintimal tissue, external tissue, and/or a portion of a proximate vessel, and reentering the vessel distal to the occlusion, and/or for non-occluded vessels, for example by creating a shunt between a healthy artery and a healthy vein that can be used for dialysis access.

In some embodiments, a method of treating coronary heart disease includes diverting arterial blood from a coronary artery to a coronary vein by the methods described herein. In some embodiments, a method of treating critical limb ischemia includes diverting arterial blood from a peripheral artery to a peripheral vein by the methods described herein.

For purposes of summarizing the invention and the advantages that may be achieved, certain objects and advantages are described herein. Not necessarily all such objects or advantages need to be achieved in accordance with any particular embodiment. In some embodiments, the invention may be embodied or carried out in a manner that can achieve or optimize one advantage or a group of advantages without necessarily achieving other objects or advantages.

All of these embodiments are intended to be within the scope of the invention herein disclosed. These and other embodiments will be apparent from the following detailed description having reference to the attached figures, the invention not being limited to any particular disclosed embodiment(s). Optional and/or preferred features described with reference to some embodiments may be combined with and incorporated into other embodiments.

BRIEF DESCRIPTION OF THE DRAWINGS

These and other features, aspects, and advantages of the present disclosure are described with reference to the drawings of certain embodiments, which are intended to illustrate certain embodiments and not to limit the invention, in which like reference numerals are used for like features, and in which:

FIG. 1 is a side perspective view of an example embodiment of a device for providing fluid flow;

FIG. 2 shows the device ofFIG. 1 in use as a shunt between two blood vessels;

FIG. 3 is a side perspective view of another example embodiment of a device for providing fluid flow; and

FIG. 4 is a side perspective view of still another example embodiment of a device for providing fluid flow.

FIG. 5 is a side perspective view of yet another example embodiment of a device for providing fluid flow.

FIG. 6 is a side perspective view of yet still another example embodiment of a device for providing fluid flow.

DETAILED DESCRIPTION

Although certain embodiments and examples are described below, the invention extends beyond the specifically disclosed embodiments and/or uses and obvious modifications and equivalents thereof. The scope of the invention herein disclosed should not be limited by any particular embodiments described below.

The present application describes devices and methods usable in minimally invasive surgical procedures, which can reduce performance of conventional surgery to treat conditions such as coronary heart disease and critical limb ischemia. For example, patients who might otherwise be unable to receive surgery such as coronary bypass surgery or peripheral arterial bypass surgery can be treated, and the amount of surgical trauma, the risk of infection, and/or the time to recovery may be reduced or significantly reduced in comparison to conventional surgery.

Some methods and devices for performing procedures such as coronary bypass and peripheral arterial bypass by minimally invasive surgical techniques are described in International Patent Application No. PCT/GB05/003480 (Publication No. WO 2006/027599), entitled “Minimally Invasive Surgical Apparatus and Methods,” the contents of which are hereby incorporated into this specification by reference in their entirety, in particular techniques for effectively bypassing an occlusion in an artery by percutaneous surgery. These techniques include creating a channel or passage between a first passage, such as an artery upstream of an occlusion, a vein, or a heart chamber, and a second passage, such as an artery, vein, or heart chamber, proximate to the first passage to interconnect the first and second passages by a third passage. Fluid such as blood may be diverted from the first passage into the second passage by way of the interconnecting third passage. In embodiments in which the first passage includes an artery and the second passage includes a vein, the arterial blood can perfuse into tissue in a retrograde manner (retroperfusion).

The interconnecting passage between the first and second passages can be created by, for example, deploying a needle outwards from a first catheter located within the first passage, so that the needle traverses the interstitial tissue or septum between the first and second passages. A second catheter may be located in the second passage, so as to provide a target device which receives a signal, for example an ultrasound signal, transmitted from the first catheter. By monitoring the received signal, the position of the first catheter with respect to the second catheter can be determined so as to ensure that the needle is deployed in the correct position and orientation to create a passage for fluid flow between the first and second passages.

In order to provide or maintain the flow of blood thorough the interconnecting passage or channel, a structure including a lumen may be inserted in the passage to support the interstitial tissue and/or to inhibit or prevent the passage from closing. The tube may, for example, include a stent expanded in the channel using a balloon catheter or self-expansion, as described herein. A catheter to deliver the structure, for example a balloon catheter or catheter that allows self-expansion, may be guided to the channel by a guide wire deployed in the passage by the first catheter.

Passages such as arteries, veins, and heart chambers can pulsate as the heart beats, for example due to movement of heart walls, peripheral limbs, and/or fluctuations in pressure within the passages themselves. This pulsation can cause movement of the passages relative to each another, which can impose stress on a structure within an interconnecting passage therebetween. This stress may be large in comparison to stress experienced by a structure within a single passage. Stress can lead to premature failure of the structure, for example by fatigue failure of the stent struts. Failure of the structure may result in injury to the interstitial tissue and/or occlusion of the interconnecting passage, which could lead to significant complications or complete failure of the therapy.

FIG. 1 illustrates a device or implant or prosthetic10 for providing or maintaining fluid flow through at least one passage. Thedevice10 includes a first orproximal end portion12, a second ordistal end portion14, and anintermediate portion16 between theproximal end portion12 and thedistal end portion14. The device includes a bore orlumen20 for passage of fluid through thedevice10. Thedevice10, for example at least theintermediate portion16 of thedevice10, includes aflexible polymer tube18. Theflexible polymer tube18 may at least partially define thelumen20.

Thedevice10 includes a support structure (e.g., at least one stent) including amesh22 and amesh24. In some embodiments, at least a portion of themesh22 is embedded in the outside wall of thetube18 proximate to theproximal end portion12 of thedevice10. In some embodiments, at least a portion of themesh24, for example a wire or a strut, is embedded in the outside wall of thetube18 proximate to thedistal end portion14 of thedevice10. The

meshes

22,24 may include biocompatible metal such as stainless steel and/or shape memory material such as nitinol or chromium cobalt.

The wire meshes22,24 can stiffen the

end portions

12,14, respectively. In some embodiments in which theintermediate portion16 does not include a mesh, theintermediate portion16 may be relatively flexible in comparison to the

end portions

12,14, and/or the

end portions

12,14 may have a relatively high radial stiffness.

In some embodiments, the

end portions

12,14 of thedevice10 are diametrically expandable. For example, the wire meshes22,24 may have a smaller diameter after formation or manufacture than the passages, for example blood vessels, into which thedevice10 will be deployed. When thedevice10 is in position in the passages, the

end portions

12,14 can be expanded or deformed outwardly so that the respective diameters of the

end portions

12,14 increase, for example to abut the interior sidewalls of the passages. The

end portions

12,14 are configured to maintain the expanded diameter indefinitely, for example by plastic deformation of the material (e.g., wires, struts) of the

meshes

22,24 and/or by provision of a locking mechanism arranged to mechanically lock the

meshes

22,24 in the expanded position. Theintermediate portion16 of thedevice10 may be diametrically expandable, for example by way of plastic deformation of thetube18.

FIG. 2 shows thedevice10 ofFIG. 1 deployed to provide a fluid flow path between afirst passage26 and asecond passage28. The

passages

26,28 may include coronary blood vessels, for example acoronary artery26 and acoronary vein28, or vice versa. The

passages

26,28 may include peripheral blood vessels (e.g., blood vessels in limbs), for example a femoral or otherperipheral artery26 and a femoral or otherperipheral vein28, or vice versa. The

end portions

12,14 and theintermediate portion16 of thedevice10 have been expanded to meet with and push against the inner walls of the

passages

26,28. Thedistal end portion14 of thedevice10 is located within thesecond passage28, and theproximal end portion12 of thedevice10 is located within thefirst passage26. Theintermediate portion16 extends through an opening or interconnectingpassage30 surgically formed between the

12,14 of thedevice10 are resilient, and impart an outward radial force on the inner walls of the

passages

26,28. By virtue of the radial stiffness of the

end portions

12,14 of thedevice10, the

end portions

12,14 are held or anchored in place within the

respective passages

26,28. Slippage of thedevice10 within the

passages

26,28 is thereby prevented or reduced. In this way, the

end portions

12,14 of thedevice10 can anchor or fix thedevice10 in position, in use, while providing or maintaining fluid flow through thelumen20 of the tube18 (FIG. 1). In this way, thedevice10 can act as a shunt between thefirst passage26 and thesecond passage28.

Theintermediate portion16 of thedevice10 may be flexible, for example allowing theintermediate portion16 to form an ‘S’ shape formed by the combination of thefirst passage26, thesecond passage28, and the interconnecting passage30 (FIG. 2). The flexibleintermediate portion16 can allow the

end portions

12,14 of thedevice10 to move with respect to one another in response to relative movement of the

passages

26,28.

In embodiments in which theintermediate portion16 does not include a wire mesh but includes the flexible polymer material of thetube18, theintermediate portion16 may not be susceptible to damage due to mesh fatigue, for example upon cyclic or other stress imparted by relative movement of the

passages

26,28.

Theintermediate portion16 of thedevice10 has sufficient resilience to maintain dilatation of the interconnectingpassage30, so that the interconnectingpassage30 remains open to provide or maintain a path for blood flow from theartery26 to thevein28 by way of thelumen20 of the tube18 (FIG. 1). Blood flow from theartery26 to thevein28, by way of the interconnectingpassage30, may thereby be provided or maintained through thelumen20 of thetube18. Thedevice10 at least partially supports theartery26, thevein28, and the interconnectingpassage30 to provide a pathway for fluid communication through thedevice10.

Theproximal end portion12 and thedistal end portion14 of thedevice10 are arranged so that, when thedevice10 is deployed with thedistal end portion14 in avein28 and theproximal end portion12 in anartery26, for example as shown inFIG. 2, the diameter of the expandeddistal end portion14 is sufficient to hold thedistal end portion14 within thevein28, and the diameter of the expandedproximal end portion12 is sufficient to hold theproximal end portion12 within theartery26. The diameter of theproximal end portion12 may therefore differ from the diameter of thedistal end portion14. By selecting appropriate diameters for the

end portions

12,14 and theintermediate portion16, thedevice10 can be tailored to a certain anatomy and/or the anatomy of an individual patient.

An example procedure for positioning thedevice10 ofFIG. 1 to provide a shunt between anoccluded artery26 and a vein28 (e.g., acoronary artery26 and acoronary vein28, or aperipheral artery26 and a peripheral vein28) to achieve reteroperfusion of arterial blood, for example as shown inFIG. 2, will now be described.

A catheter may be inserted into the patient's arterial system by way of a small aperture cut, usually in the patient's groin area. The catheter is fed to theartery26 and guided to a position upstream of the site of the occlusion, for example at a site proximate and parallel or substantially parallel to avein28. A hollow needle is deployed from the catheter, through the wall of theartery26, through theinterstitial tissue32 that separates theartery26 andvein28, and through the wall of thevein28. The path of the needle creates an interconnecting passage oropening30, which allows blood to flow between theartery26 and thevein28. Deployment of the needle may be guided by a transmitter (e.g., a directional ultrasound transmitter) coupled to a catheter in theartery26 and a receiver (e.g., an omnidirectional ultrasound receiver) coupled to a catheter in thevein28, or vice versa, for example as described in International Patent Application No. PCT/GB05/003480. Other methods of forming theopening30 are also possible (e.g., with or without guidance, from vein to artery, etc.).

Before the needle is withdrawn from thepassage30, a guide wire is inserted through the hollow needle and into thevein28. The needle is then retracted, leaving the guide wire in place in theartery26, thepassage30, and thevein28. The catheter carrying the needle can then be withdrawn from the patient's body. The guide wire can be used to guide further catheters to the interconnectingpassage30 between theartery26 and thevein28.

A catheter carrying thedevice10 in a non-expanded state is advanced towards the interconnectingpassage30, guided by the guide wire, for example by a rapid exchange lumen or through thelumen20. The catheter may include, for example, a balloon catheter configured to expand at least a portion of thedevice10 and/or a catheter configured to allow self-expansion of at least a portion of thedevice10. Thedistal end portion14 of thedevice10 is passed through the interconnectingpassage30 and into thevein28, leaving theproximal end portion12 in theartery26. Theintermediate portion16 of thedevice10 is at least partially in thepassage30, and is at least partially within theartery26 and thevein28. Theintermediate portion16 flexes to adopt a curved or “S”-shaped formation, depending on the anatomy of the site. Adoption of such curvature may conform the shape of anintermediate portion16 extending through the interconnectingpassage30, and optionally into at least one of the

passages

26,28, to the shape of at least the interconnectingpassage30.

Thedistal end portion14 of thedevice10 is expanded, for example upon inflation of a balloon or by self-expansion, so as to increase the diameter of thedistal end portion14 and anchor thedistal end portion14 against the inner wall of thevein28. The catheter may be adapted to expand theintermediate portion16 of thedevice10, for example by inflation of a balloon, so that the interconnectingpassage30 can be widened or dilated to obtain blood flow (e.g., sufficient blood flow) from theartery26 to thevein28. Theproximal end portion12 of thedevice10 is expanded, for example upon inflation of a balloon or by self-expansion, so as to increase the diameter of theproximal end portion12 and anchor theproximal end portion12 against the inner wall of theartery26.

After the

end portions

12,14 of thedevice10 are expanded, for example due to self-expansion and/or balloon expansion, and with or without improving expansion after deployment, the catheter and the guide wire are withdrawn from the patient's body. In this way, thedevice10 is anchored or fixed in position within thevein28, theartery26, and the interconnectingpassage30 as shown inFIG. 2.

The catheter may be adapted to selectively expand theproximal end portion12, thedistal end portion14, and/or theintermediate portion16 of thedevice10 individually or in combination, for example by the provision of two or more separately inflatable balloons or balloon portions, a single balloon configured to expand all of the portions of thedevice10 simultaneously, or a single balloon configured to expand one or more selected portions of thedevice10. For example, the

end portions

12,14 may be self-expanding, and theintermediate portion16 may be expanded by a balloon to dilate thepassage30. In some embodiments including balloon expansion, all or selected parts of thedevice10 may be expanded, for example, simultaneously by a balloon across the entire length of thedevice10 or by a plurality of balloons longitudinally spaced to selectively inflate selected parts of thedevice10, and/or sequentially by a balloon or plurality of balloons. In some embodiments including at least partial self-expansion, all or selected parts of thedevice10 may be expanded, for example, by proximal retraction of a sheath over or around thedevice10, which can lead to deployment of thedevice10 from distal to proximal as the sheath is proximally retracted. Deployment of thedevice10 proximal to distal and deployment of thedevice10 intermediate first then the ends are also possible.

Other steps may be included in the procedure. For example, before thedevice10 is deployed, a balloon catheter may be guided to the interconnectingpassage30 and positioned so that an inflatable balloon portion of the catheter lies in the interconnectingpassage30. Upon inflation of the balloon, the balloon pushes against the walls of the interconnectingpassage30 to widen or dilate the interconnectingpassage30 to ease subsequent insertion of thedevice10.

FIG. 3 illustrates anotherdevice34 for providing fluid flow through at least one passage. Thedevice34 includes amesh36 and apolymer tube18. Themesh36 is shown as being on the outside of thepolymer tube18, but as described herein could also or alternatively be on an inside of the polymer tube and/or within thepolymer tube18. As described with respect to thedevice10, thedevice34 includes aproximal end portion12, adistal end portion14, and anintermediate portion16. In the embodiment illustrated inFIG. 3, themesh36 extends along the entire length of thedevice34, including along theintermediate portion16.

In some embodiments, the spacing of filaments or struts of themesh36 varies along the length of thedevice34. For example, winding density of a woven or layered filamentary mesh may be varied and/or a window size pattern of a cut mesh may be varied.

In some embodiments, the spacing may be relatively small in theproximal end portion12 and thedistal end portions14, and the spacing may be relatively large in theintermediate portion16. In other words, the density or window size of themesh36 may be relatively low in theintermediate portion16, and the density or window size of themesh36 may be relatively high in the

end portions

12,14. In certain such embodiments, theintermediate portion16 may be flexible in comparison to the

end portions

12,14. The relatively

rigid end portions

12,14 may engage and anchor in passages. Although themesh36 in theintermediate portion16 may be subject to stress such as cyclic stress, in use, the relatively high flexibility of theintermediate portion16 due to the low density or window size allows the impact of the stress to be low because theintermediate portion16 can flex in response to the stress. The risk of fatigue failure of thedevice34, and particularly the filaments or struts38 of themesh36, may therefore be reduced in comparison to a device having uniform flexibility along its entire length.

In some embodiments, the spacing may be relatively large in theproximal end portion12 and thedistal end portions14, and the spacing may be relatively small in theintermediate portion16. In other words, the density of themesh36 may be relatively high (or the window size of themesh36 may be relatively low) in theintermediate portion16, and the density of themesh36 may be relatively low (or the window size of themesh36 may be relatively high) in the

end portions

12,14. In certain such embodiments, theintermediate portion16 may have radial strength sufficient to inhibit or prevent collapse of thepassage30, yet still, flexible enough to flex in response to stress such as cyclic stress. The

end portions

12,14 may engage and anchor in passages.

FIG. 4 illustrates another device or implant or prosthetic40 for providing fluid flow through at least one passage. As described with respect to thedevice10, thedevice40 includes aproximal end portion12, adistal end portion14, and anintermediate portion16. Thedevice40 includes apolymer tube18 and a support structure including afirst mesh42 and asecond mesh44. Thefirst mesh42 extends from theproximal end portion12 toward (e.g., into) theintermediate portion16 and optionally into thedistal end portion14. Thesecond mesh44 extends from thedistal end portion14 toward (e.g., into) theintermediate portion16 and optionally into theproximal end portion12. The

meshes

42,44 thereby overlap each other at least in theintermediate portion16. Both meshes42,44 may be on the outside of thetube18, on the inside of thetube18, or embedded within thetube18, or one mesh may be on the outside of thetube18, on the inside of thetube18, or embedded within thetube18 while the other mesh is differently on the outside of thetube18, on the inside of thetube18, or embedded within the tube18 (e.g., one mesh inside thetube18 and one mesh outside the tube18). The

meshes

42,44 may be formed, for example, by winding wire in a lattice configuration around or inside thepolymer tube18, by placing a cut tube around or inside thepolymer tube18, by being embedded in thepolymer tube18, combinations thereof, and the like.

In some embodiments, the density of the

meshes

42,44 is relatively high (or the window size of the

meshes

42,44 is relatively low) in their

respective end portions

12,14 and decreases in density (or increases in window size) towards theintermediate portion16. The total winding density (e.g., the winding density of both

meshes

42,44, taken together) may be lower in theintermediate portion16 than in the

end portions

12,14, or the total window size (e.g., the window size of both

meshes

42,44, taken together) may be higher in theintermediate portion16 than in the

end portions

12,14. In certain such embodiments, theintermediate portion16 is relatively flexible in comparison to the

end portions

12,14. In some embodiments, the

meshes

42,44 do not extend into the intermediate portion, and absence of a mesh could cause theintermediate portion16 to be relatively flexible in comparison to the

end portions

12,14. In some embodiments, as window size increases (e.g., longitudinally along a tapered portion of the device40), the density decreases, the mesh coverage decreases, and/or the porosity increases because the width of the struts and/or filaments remains substantially constant or constant or does not increase in the same proportion as the window size, which could provide a change in flexibility along a longitudinal length.

The first and

second meshes

42,44 may include different materials, which can allow optimization of the properties of each of the respective distal and

proximal end portions

12,14 of thedevice40 for a particular application of thedevice40. For example, thesecond mesh44 at thedistal end portion14 of thedevice40 may include a relatively flexible metallic alloy for ease of insertion through an interconnecting passage between two blood vessels, while thefirst mesh42 at theproximal end portion12 of thedevice40 may include a relatively inelastic metallic alloy to provide a high degree of resilience at theproximal end portion14 to anchor thedevice40 firmly in position. The first and

second meshes

42,44 could include the same material composition (e.g., both including nitinol) but different wire diameters (gauge) or strut thicknesses.

FIG. 5 illustrates another device or implant or prosthetic50 for providing fluid flow through at least one passage. Thedevice50 includes a support structure (e.g., stent)56 and agraft58. As described with respect to thedevice10, thedevice50 includes aproximal end portion12, adistal end portion14, and anintermediate portion16. Theproximal end portion12 includes a cylindrical or substantially cylindrical portion and thedistal end portion14 includes a cylindrical or substantially cylindrical portion. The diameter of theproximal end portion12 is smaller than the diameter of thedistal end portion14. In some embodiments, the diameter of theproximal end portion12 is larger than the diameter of thedistal end portion14. Theintermediate portion16 has a tapered or frustoconical shape between theproximal end portion12 and thedistal end portion14. Thestent56 may include filaments (e.g., woven, layered), a cut tube or sheet, and/or combinations thereof.

Parameters of thestent56 may be uniform or substantially uniform across a portion and/or across multiple portions, or may vary within a portion and/or across multiple portions. For example, thestent56 at theproximal end portion12 may include a cut tube or sheet, thestent56 at thedistal end portion12 may include a cut tube or sheet, and thestent56 at theintermediate portion16 may include filaments (e.g., woven or layered). Certain such embodiments may provide good anchoring by theproximal end portion12 and thedistal end portion14 and good flexibility (e.g., adaptability to third passage sizes and dynamic stresses) of theintermediate portion16.

Thestent56 may include different materials in different portions. For example, thestent56 at theproximal end portion12 may include chromium cobalt and/or tantalum, thestent56 at thedistal end portion14 may include nitinol, and thestent56 at theintermediate portion16 may include nitinol. Certain such embodiments may provide good anchoring and/or wall apposition by thedevice50 in each deployment areas (e.g., theproximal end portion12 engaging sidewalls of an artery, thedistal end portion14 engaging sidewalls of a vein, and theintermediate portion16 engaging sidewalls of the passage between the artery and the vein).

Combinations of support structure materials and types are also possible. For example, thestent56 at the proximal portion may include a cut tube or sheet including chromium cobalt and/or tantalum, thestent56 at thedistal end portion14 may include a cut tube or sheet including nitinol, and thestent56 at theintermediate portion16 may include filaments including nitinol.

In embodiments in which thestent56 includes at least one portion including a cut tube or sheet, the cut pattern may be the same. For example, the cut pattern may be the same in theproximal end portion12 and thedistal end portion14, but proportional to the change in diameter. In some embodiments, the window size or strut density is uniform or substantially uniform within a

portion

12,14,16, within two or more of the

portions

12,14,16, and/or from one end of thestent56 to the other end of thestent56. In embodiments in which thestent56 includes at least one portion including filaments, the winding may be the same. For example, the winding may be the same in theproximal end portion12 and thedistal end portion14, but changed due to the change in diameter. In some embodiments, the winding density or porosity is uniform or substantially uniform within a

portion

12,14,16, within two or more of the

portions

12,14,16, and/or from one end of thestent56 to the other end of thestent56. In embodiments in which thestent56 includes at least one portion including a cut tube or sheet and at least one portion including filaments, the cut pattern and winding may be configured to result in a uniform or substantially uniform density. Non-uniformity is also possible, for example as described herein.

Thegraft58 may include materials and attachment to thestent56 as described with respect to thetube18. Thegraft58 generally forms a fluid-tight passage for at least a portion of thedevice50. Although illustrated as only being around theintermediate portion16, thegraft58 may extend the entire length of thedevice50, or may partially overlap into at least one of the

cylindrical end portions

12,14.

FIG. 6 illustrates anotherdevice60 for providing fluid flow through at least one passage. Thedevice60 includes a support structure (e.g., stent) and agraft68. As described with respect to thedevice10, thedevice60 includes aproximal end portion12, adistal end portion14, and anintermediate portion16. Theproximal end portion12 includes a tapered or frustoconical portion and thedistal end portion14 includes a tapered or frustoconical portion. The diameter of the proximal end of theproximal end portion12 is smaller than the diameter of the distal end of thedistal end portion14. In some embodiments, the diameter of the proximal end of theproximal end portion12 is larger than the diameter of the distal end of thedistal end portion14. Theintermediate portion16 has a tapered or frustoconical shape between theproximal end portion12 and thedistal end portion14. In some embodiments, the angle of inclination of the

portions

12,14,16 is the same or substantially the same (e.g., as illustrated inFIG. 6). In some embodiments, the angle of inclination of at least one portion is sharper or narrower than at least one other portion. The frustoconicalproximal end portion12 anddistal end portion14 may allow better anchoring in a body passage, for example because arteries tend to taper with distance from the heart and veins tend to taper with distance towards the heart, and the

end portions

12,14 can be configured to at least partially correspond to such anatomical taper.

As described above with respect to thesupport structure56, thesupport structure66 may include filaments (e.g., woven, layered), a cut tube or sheet, the same materials, different materials, and combinations thereof.

Thegraft68 may include materials and attachment to thestent66 as described with respect to thetube18. Thegraft68 generally forms a fluid-tight passage for at least a portion of thedevice60. Although illustrated as only being around theintermediate portion16, thegraft68 may extend the entire length of thedevice60, or may partially overlap into at least one of the

frustoconical end portions

12,14.

In some embodiments, a combination of thedevice50 and thedevice60 are possible. For example, theproximal end portion12 can be cylindrical or substantially cylindrical (e.g., as in the device50), thedistal end portion14 can be tapered or frustoconical (e.g., as in the device60), with theproximal end portion12 having a larger diameter than the distal end of thedistal end portion14. For another example, theproximal end portion12 can be tapered or frustoconical (e.g., as in the device60), thedistal end portion14 can be cylindrical or substantially cylindrical (e.g., as in the device50), with the proximal end of theproximal end portion12 having a larger diameter than thedistal end portion14. In each example, theintermediate portion16 can have a tapered or frustoconical shape between theproximal end portion12 and thedistal end portion14.

An example deployment device for the implantable devices described herein is described in U.S. patent application Ser. No. 12/545,982, filed Aug. 24, 2009, and U.S. patent application Ser. No. 13/486,249, filed Jun. 1, 2012, the entire contents of each of which is hereby incorporated by reference. The device generally includes a handle at the proximal end with a trigger actuatable by a user and a combination of tubular member at the distal end configured to be pushed and/or pulled upon actuation of the trigger to release the device. Other delivery devices are also possible. The delivery device may include a portion slidable over a guide wire (e.g., a guide wire that has been navigated between the artery and the vein via a tissue traversing needle) and/or may be trackable through a lumen of a catheter.

Although certain embodiments and examples are shown or described herein in detail, various combinations, sub-combinations, modifications, variations, substitutions, and omissions of the specific features and aspects of those embodiments are possible, some of which will now be described by way of example only.

The device, for example a stent of the device, a mesh of the device, a support structure of the device, etc., may be self-expanding. For example, a mesh may include a shape-memory material, such as nitinol, which is capable of returning to a pre-set shape after undergoing deformation. In some embodiments, the stent may be manufactured to a shape that is desired in the expanded configuration, and is compressible to fit inside a sleeve for transport on a catheter to a vascular site. To deploy and expand the stent, the sleeve is drawn back from the stent to allow the shape memory material to return to the pre-set shape, which can anchor the stent in the passages, and which may dilate the passages if the stent has sufficient radial strength. The use of a balloon catheter is not required to expand a fully self-expanding stent, but may be used, for example, to improve or optimize the deployment.

A device may include one or more self-expanding portions, and one or more portions which are expandable by deformation, for example using a balloon catheter. For example, in the embodiment shown inFIG. 4, thefirst mesh42 may include stainless steel expandable by a balloon catheter, and thesecond mesh44 may include nitinol for self-expansion upon deployment.

With respect to any of the embodiments described herein, thepolymer tube18, including the

grafts

58,68, may include any suitable compliant or flexible polymer, such as PTFE, silicone, polyethylene terephthalate (PET), polyurethane such as polycarbonate aromatic biodurable thermoplastic polyurethane elastomer (e.g., ChronoFlex C® 80A and 55D medical grade, available from AdvanSource Biomaterials of Wilmington, Mass.), combinations thereof, and the like. Thepolymer tube18 may include biodegradable, bioabsorbable, or biocompatible polymer (e.g., polylactic acid (PLA), polyglycolic acid (PGA), polyglycolic-lactic acid (PLGA), polycaprolactone (PCL), polyorthoesters, polyanhydrides, combinations thereof, etc. The polymer may be in tube form before interaction with a support structure (e.g., stent), or may be formed on, in, and/or around a support structure (e.g., stent). For example, the polymer may include spun fibers, a dip-coating, combinations thereof, and the like. In some embodiments, for example when the device is to be deployed within a single blood vessel, the device may omit the tube. In certain such embodiments, the intermediate portion of the stent may include a mesh with a low winding density or high window size, while the end portions of the stent include a mesh with a higher winding density or lower window size, the mesh being generally tubular to define a pathway for fluid flow through the center of the mesh. In some embodiments, thepolymer tube18 includes a lip (e.g., comprising the same or different material), which can help form a fluid-tight seal between thepolymer tube18 and the body passages. The seal may be angled, for example to account for angled positioning of thepolymer tube18 between body passages. In some embodiments, thepolymer tube18 may extend longitudinally beyond the support structure in at least one direction, and the part extending beyond is not supported by the support structure.

The mesh may include any suitable material, such as nickel, titanium, chromium, cobalt, tantalum, platinum, tungsten, iron, manganese, molybdenum, combinations thereof (e.g., nitinol, chromium cobalt, stainless steel), and the like. The mesh may include biodegradable, bioabsorbable, or biocompatible polymer (e.g., polylactic acid (PLA), polyglycolic acid (PGA), polyglycolic-lactic acid (PLGA), polycaprolactone (PCL), polyorthoesters, polyanhydrides, combinations thereof, etc.) and/or glass, and may lack metal. Different materials may be used for portions of the mesh or within the same mesh, for example as previously described with reference toFIG. 4. For example, themesh24 at thedistal end portion14 and themesh22 at theproximal end portion12 of thedevice10 may include different materials. For another example, themesh22, and/or themesh24, may include a metallic alloy (e.g., comprising cobalt, chromium, nickel, titanium, combinations thereof, and the like) in combination with a different type of metallic alloy (e.g., a shape memory alloy in combination with a non-shape memory alloy, a first shape memory alloy in combination with a second shape memory alloy different than the first shape memory alloy, a clad material (e.g., comprising a core including a radiopaque material such as titanium, tantalum, rhenium, bismuth, silver, gold, platinum, iridium, tungsten, etc.)) and/or a non-metallic material such as a polymer (e.g., polyester fiber), carbon, and/or bioabsorbable glass fiber. In some embodiments, at least one

mesh

22,24 comprises nitinol and stainless steel. The ninitol may allow some self-expansion (e.g., partial and/or full self-expansion), and the mesh could then be further expanded, for example using a balloon.

Although generally illustrated inFIGS. 1,3, and4 as a woven filament mesh, any other structure that can provide the desired degree of resilience may be used. For example, layers of filaments wound in opposite directions may be fused at the filament ends to provide an expandable structure. For another example, a metal sheet may be cut (e.g., laser cut, chemically etched, plasma cut, etc.) to form perforations and then heat set in a tubular formation or a metal tube (e.g., hypotube) may be cut (e.g., laser cut, chemically etched, plasma cut, etc.) to form perforations. A cut tube (including a cut sheet rolled into a tube) may be heat set to impart an expanded configuration.

Filaments or wires or ribbons that may be woven or braided, or layered or otherwise arranged, are generally elongate and have a circular, oval, square, rectangular, etc. transverse cross-section. Example non-woven filaments can include a first layer of filaments wound in a first direction and a second layer of filaments wound in a second direction, at least some of the filament ends being coupled together (e.g., by being coupled to an expandable ring). Example braid patterns include one-over-one-under-one, a one-over-two-under-two, a two-over-two-under-two, and/or combinations thereof, although other braid patterns are also possible. At filament crossings, filaments may be helically wrapped, cross in sliding relation, and/or combinations thereof. Filaments may be loose (e.g., held together by the weave) and/or include welds, coupling elements such as sleeves, and/or combinations thereof. Ends of filaments can be bent back, crimped (e.g., end crimp with a radiopaque material such as titanium, tantalum, rhenium, bismuth, silver, gold, platinum, iridium, tungsten, etc. that can also act as a radiopaque marker), twisted, ball welded, coupled to a ring, combinations thereof, and the like. Weave ends may include filament ends and/or bent-back filaments, and may include open cells, fixed or unfixed filaments, welds, adhesives, or other means of fusion, radiopaque markers, combinations thereof, and the like. Parameters of the filaments may be uniform or substantially uniform across a portion and/or across multiple portions, or may vary within a portion and/or across multiple portions. For example, theproximal end portion12 may include a first parameter and thedistal end portion14 may include a second parameter different than the first braid pattern. For another example, theproximal end portion12 and thedistal end portion14 may each include a first parameter and theintermediate portion16 may include a second parameter different than the parameter. For yet another example, at least one of theproximal end portion12, thedistal end portion14, and theintermediate portion16 may include both a first parameter and a second parameter different than the first parameter. Filament parameters may include, for example, filament type, filament thickness, filament material, quantity of filaments, weave pattern, layering, wind direction, pitch, angle, crossing type, filament coupling or lack thereof, filament end treatment, weave end treatment, layering end treatment, quantity of layers, presence or absence of welds, radiopacity, braid pattern, density, porosity, filament angle, braid diameter, winding diameter, and shape setting.

Tubes or sheets may be cut to form strut or cell patterns, struts being the parts of the tube or sheet left after cutting and cells or perforations or windows being the parts cut away. A tube (e.g., hypotube) may be cut directly, or a sheet may be cut and then rolled into a tube. The tube or sheet may be shape set before or after cutting. The tube or sheet may be welded or otherwise coupled to itself, to another tube or sheet, to filaments, to a graft material, etc. Cutting may be by laser, chemical etchant, plasma, combinations thereof, and the like. Example cut patterns include helical spiral, weave-like, coil, individual rings, sequential rings, open cell, closed cell, combinations thereof, and the like. In embodiments including sequential rings, the rings may be coupled using flex connectors, non-flex connectors, and/or combinations thereof. In embodiments including sequential rings, the rings connectors (e.g., flex, non-flex, and/or combinations thereof) may intersect ring peaks, ring valleys, intermediate portions of struts, and/or combinations thereof (e.g., peak-peak, valley-valley, mid-mid, peak-valley, peak-mid, valley-mid, valley-peak, mid-peak, mid-valley). The tube or sheet or sections thereof may be ground and/or polished before or after cutting. Interior ridges may be formed, for example to assist with fluid flow. Parameters of the cut tube or sheet may be uniform or substantially uniform across a portion and/or across multiple portions, or may vary within a portion and/or across multiple portions. For example, theproximal end portion12 may include a first parameter and thedistal end portion14 may include a second parameter different than the first parameter. For another example, theproximal end portion12 and thedistal end portion14 may each include a first parameter and theintermediate portion16 may include a second parameter different than the parameter. For yet another example, at least one of theproximal end portion12, thedistal end portion14, and theintermediate portion16 may include both a first parameter and a second parameter different than the first parameter. Cut tube or sheet parameters may include, for example, radial strut thickness, circumferential strut width, strut shape, cell shape, cut pattern, cut type, material, density, porosity, tube diameter, and shape setting.

In some embodiments, the perforations may provide the mesh with a relatively flexible intermediate portion and relatively stiff end portions. The supporting structure may instead be an open-cell foam disposed within the tube.

Filaments of a stent, stent-graft, or a portion thereof, and/or struts of a cut stent, stent-graft, or a portion thereof, may be surface modified, for example to carry medications such as thrombosis modifiers, fluid flow modifiers, antibiotics, etc. Filaments of a stent, stent-graft, or a portion thereof, and/or struts of a cut stent, stent-graft, or a portion thereof, may be at least partially covered with a coating including medications such as thrombosis modifiers, fluid flow modifiers, antibiotics, etc., for example embedded within a polymer layer or a series of polymer layers, which may be the same as or different than thepolymer tube18.

Thicknesses of filaments and/or struts may be based, for example, on at least one of device or device portion size (e.g., diameter and/or length), porosity, radial strength, material, quantity of filaments and/or struts, cut pattern, weave pattern, layering pattern, and the like. For example, larger filament and/or strut thicknesses (e.g., greater than about 0.006 inches) may be useful for large devices or device portions used to treat large vessels such as coronary vessels, mid-sized filament and/or strut thicknesses (e.g., between about 0.003 inches and about 0.006 inches) may be useful for mid-sized used to treat mid-sized vessels such as peripheral vessels, and small filament and/or strut thicknesses (e.g., less than about 0.003 inches) may be useful for small devices or device portions used to treat small vessels such as veins and neurological vessels.

The porosity of a stent, a stent-graft, or a first end portion, second end portion, intermediate portion, or subportion thereof may be between about 5% and about 95%, between about 5% and about 50%, between about 5% and about 25%, between about 5% and about 10%, between about 10% and about 50%, between about 10% and about 25%, between about 25% and about 50%, between about 50% and about 95%, between about 50% and about 75%, between about 50% and about 60%, between about 60% and about 95%, between about 75% and about 90%, between about 60% and about 75%, and combinations thereof. The density of a stent may be inverse to the porosity of that stent. The porosity of a portion of a stent covered by a graft may be about 0%. The porosity may vary by objectives for certain portions of the stent. For example, the intermediate portion may have a low porosity to increase fluid flow through the device, while end portions may have lower porosity to increase flexibility and wall apposition.

The radial strength or compression resistance of a stent, a stent-graft, or a first end portion, second end portion, intermediate portion, or subportion thereof may be between about 0.1 N/mm and about 0.5 N/mm, between about 0.2 N/mm and about 0.5 N/mm, between about 0.3 N/mm and about 0.5 N/mm, between about 0.1 N/mm and about 0.3 N/mm, between about 0.1 N/mm and about 0.2 N/mm, between about 0.2 N/mm and about 0.5 N/mm, between about 0.2 N/mm and about 0.3 N/mm, or between about 0.3 N/mm and about 0.5 N/mm.

The values of certain parameters of a stent, a stent-graft, or a first end portion, second end portion, intermediate portion, or subportion thereof may be linked (e.g., proportional). For example, a ratio of a thickness of a strut or filament to a diameter of a device portion comprising that strut or filament may be between about 1:10 and about 1:250, between about 1:25 and about 1:175, or between about 1:50 and about 1:100. For another example, a ratio of a length of a device or portion thereof to a diameter of a device or a portion thereof may be between about 1:1 and about 50:1, between about 5:1 and about 25:1, or between about 10:1 and about 20:1.

Portions of the device may include radiopaque material. For example, filaments and/or struts a stent, a stent-graft, or a first end portion, second end portion, intermediate portion, or subportion thereof may comprise (e.g., be at least partially made from) titanium, tantalum, rhenium, bismuth, silver, gold, platinum, iridium, tungsten, combinations thereof, and the like. For another example, filaments and/or struts of a stent, stent-graft, or a portion thereof may comprise (e.g., be at least partially made from) a material having a density greater than about 9 grams per cubic centimeter. Separate radiopaque markers may be attached to certain parts of the device. For example, radiopaque markers can be added to the proximal end of the device or parts thereof (e.g., a proximal part of the intermediate portion, a proximal part of the distal portion), the distal end of the device or parts thereof (e.g., a distal part of the intermediate portion, a distal part of the proximal portion), and/or other parts. A radiopaque marker between ends of a device may be useful, for example, to demarcate transitions between materials, portions, etc. Radiopacity may vary across the length of the device. For example, the proximal portion could have a first radiopacity (e.g., due to distal portion material and/or separate markers) and the distal portion could have a second radiopacity (e.g., due to distal portion material and/or separate markers) different than the first radiopacity.

In some embodiments, the device includes a polymer tube, and no supporting structure is provided. The intermediate portion of such a device may be relatively more flexible than the end portions by, for example, decreasing the wall thickness of the polymer tube within the intermediate portion.

When a mesh or other supporting structure is provided in combination with a polymer tube, the supporting structure may be located around the outside of the tube, in the inner bore of the tube, or embedded within a wall of the tube. More than one supporting structure may be provided, in which case each supporting structure may have a different location with respect to the tube.

One or both of the end portions of the device may include anchoring elements such as hooks, protuberances, or barbs configured to grasp or grip inner sidewalls of a blood vessel. The radial force of the end portions after expansion may be sufficient to grasp or grip inner sidewalls of a blood vessel without anchoring elements.

There need not be a well-defined transition between the intermediate and end portions. For example, mesh type, material, wall thickness, flexibility, etc. may gradually change from an end portion toward an intermediate portion or from an intermediate portion toward an end portion.

The flexibility of the device may increase gradually when moving from an end portion towards the intermediate portion, for example as described with respect to the

devices

34,40. The change in flexibility may be due to change in mesh density (e.g., winding density, window size), tube thickness, or other factors. The flexibility of the device may be uniform or substantially uniform along the entire length of the support structure (e.g., stent), or along certain portions of the support structure (e.g., along an entire end portion, along the entire intermediate portion, along one end portion and the intermediate portion but not the other end portion, etc.).

While the devices described herein may be particularly suitable for use as a transvascular shunt in percutaneous surgery, the devices could be used in many other medical applications. For example, the devices could be used in angioplasty for the treatment of occluded blood vessels with tortuous or kinked paths, or where the vessels may be subject to deflection or deformation at or near the position of the stent. The stent could also be used for the repair of damaged blood vessels, for example in aortic grafting procedures or after perforation during a percutaneous procedure. In certain such cases, the intermediate portion of the device can allow the device to conform to the shape of the blood vessel and to deform in response to movement of the vessel with reduced risk of fatigue failure while remaining fixed or anchored in position by the end portions. For another example, the devices could be used to form a shunt between a healthy artery and a healthy vein for dialysis access and/or access for administration of medications (e.g., intermittent injection of cancer therapy, which can damage vessels).

While the devices described herein may be used in applications in which the fluid that flows through the device is a liquid such as blood, the devices could be used in applications such as tracheal or bronchial surgery where the fluid is a gas, such as air. In some embodiments, the fluid may contain solid matter, for example emboli or, in gastric surgery where the fluid includes food particles.

The ranges disclosed herein also encompass any and all overlap, sub-ranges, and combinations thereof. Language such as “up to,” “at least,” “greater than,” “less than,” “between,” and the like includes the number recited. Numbers preceded by a term such as “about” or “approximately” include the recited numbers. For example, “about 10 mm” includes “10 mm.” Terms or phrases preceded by a term such as “substantially” include the recited term or phrase. For example, “substantially parallel” includes “parallel.”

Example Embodiments

The following example embodiments identify some possible permutations of combinations of features disclosed herein, although other permutations of combinations of features are also possible.

1. A method of diverting fluid flow from a first passage to a second passage, the method comprising:

- deploying a device in a third passage between the first passage and the second passage, the device comprising;
  - a first end portion having a first end diameter;
  - a second end portion having a second end diameter larger than the first end diameter;
  - an intermediate portion between the first end portion and the second end portion, the intermediate portion tapering between the first end portion and the second end portion; and
  - a graft material coupled to at least the intermediate portion; expanding the first end portion against sidewalls of the first passage; and expanding the second end portion against sidewalls of the second passage.

2. The method of Embodiment 1, wherein the first passage is an artery and the second passage is a vein.

3. The method of Embodiment 2, wherein the first passage is a coronary artery and the second passage is a coronary vein.

4. The method of Embodiment 2, wherein the first passage is a peripheral artery and the second passage is a peripheral vein.

5. The method of any one of Embodiments 1-4, further comprising dilating the third passage.

6. The method of Embodiment 5, wherein dilating the third passage comprises expanding the intermediate portion.

7. The method of any one of Embodiments 1-6, wherein the first passage is substantially parallel to the second passage.

8. The method of any one of Embodiments 1-7, wherein the intermediate portion is conformable to an “S” shape.

9. The method of any one of Embodiments 1-8, wherein expanding the first end portion and the second end portion comprises allowing self-expansion of the first end portion and the second end portion.

10. The method of any one of Embodiments 1-9, wherein expanding the first end portion and the second end portion comprises balloon expanding at least one of the first end portion and the second end portion.

11. The method of any one of Embodiments 1-10, wherein expanding one of the first end portion and the second end portion comprises allowing self-expansion of the one of the first end portion and the second end portion and wherein expanding the other of the first end portion and the second end portion comprises balloon expanding the other of the first end portion and the second end portion.

12. The method of any one of Embodiments 1-11, further comprising expanding the intermediate portion.

13. A device comprising:

- a first end portion having a first end diameter;
- a second end portion having a second end diameter smaller than the first end diameter;
- an intermediate portion between the first end portion and the second end portion, the intermediate portion tapering between the first end portion and the second end portion; and
- a graft material coupled to at least the intermediate portion.

14. The device of Embodiment 13, wherein at least one of the first end portion and the second end portion is substantially cylindrical.

15. The device ofEmbodiment 14, wherein the first end portion is substantially cylindrical and the second end portion is substantially cylindrical.

16. The device of any one of Embodiments 13-15, wherein the first end portion tapers between the first end diameter and the intermediate portion, or wherein the second end portion tapers between the second end diameter and the intermediate portion.

17. The device of any one of Embodiments 13-15, wherein the first end portion tapers between the first end diameter and the intermediate portion and the second end portion tapers between the second end diameter and the intermediate portion.

18. The device of any one of Embodiments 13-17, wherein the first end portion comprises a first type of material, the second end portion comprises a second type of material, and the intermediate portion comprises a third type of material.

19. The device ofEmbodiment 18, wherein the first type of material comprises a first cut material, the second type of material comprises a second cut material, and the third type of material comprises filaments.

20. The device of Embodiment 19, wherein the first cut material comprises a chromium cobalt alloy, the second cut material comprises nitinol, and the filaments comprises nitinol.

21. The device ofEmbodiment 18, wherein the first type of material comprises a cut material, the second type of material comprises the cut material, and the third type of material comprises filaments.

22. The device of Embodiment 21, wherein the cut material comprises nitinol and the filaments comprises nitinol.

23. The device of any one of Embodiments 13-22, wherein at least one of the first end portion, the second end portion, the intermediate portion, and the graft material comprises a bioabsorbable material.

24. The device of any one of Embodiments 13-23, wherein at least some of the graft material is outside the intermediate portion, at least some of the graft material is inside the intermediate portion, or at least some of the graft material is embedded within the intermediate portion.

25. The device of any one of Embodiments 13-24, wherein the device is capable of maintaining fluid flow between a first passage in which the first end portion is anchored and a second passage in which the second end portion is anchored.

26. The device of Embodiment 25, wherein the first passage is substantially parallel to the second passage.

27. The device ofEmbodiment 25 or 26, wherein the intermediate portion is conformable to an “S” shape.

28. A device comprising:

- a first end portion comprising a first material;
- a second end portion comprising a second material different than the first material;
- an intermediate portion between the first end portion and the second end portion; and
- a graft material coupled to at least the intermediate portion.

29. The device ofEmbodiment 28, wherein the first material comprises nitinol and the second material comprises chromium cobalt.

30. The device ofEmbodiment 28 or 29, wherein the first material comprises nitinol and the second material comprises stainless steel.

31. The device of any one of Embodiments 28-30, wherein the first end portion comprises cut struts and the second end portion comprises filaments.

32. The device of any one of Embodiments 28-31, wherein the first end portion comprises cut struts and the second end portion comprises cut struts.

33. The device of any one of Embodiments 28-33, wherein the first material comprises an alloy and the first end portion comprises struts or filaments having a first thickness, and wherein the second material comprises the alloy and the second end potion comprises struts or filaments having a second thickness different than the first thickness.

34. The device of any one of Embodiments 28-33, wherein the intermediate portion comprises a third material.

35. The device ofEmbodiment 34, wherein the third material comprises nitinol.

36. The device of any one of Embodiments 28-35, wherein the intermediate portion comprises filaments.

37. The device of any one of Embodiments 28-36, wherein the intermediate portion comprises cut struts.

38. The device of any one of Embodiments 28-37, wherein at least one of the first end portion and the second end portion is substantially cylindrical.

39. The device of any one of Embodiments 28-38, wherein at least one of the first end portion, the second end portion, the intermediate portion, and the graft material comprises a bioabsorbable material.

40. The device of any one of Embodiments 28-39, wherein at least some of the graft material is outside the intermediate portion, at least some of the graft material is inside the intermediate portion, or at least some of the graft material is embedded within the intermediate portion.

41. The device of any one of Embodiments 28-41, wherein the graft material is coupled to at least one of the first end portion and the second end portion.

42. The device of any one of Embodiments 28-42, wherein the device is capable of maintaining fluid flow between a first passage in which the first end portion is anchored and a second passage in which the second end portion is anchored.

43. The device ofEmbodiment 42, wherein the first passage is substantially parallel to the second passage.

44. The device ofEmbodiment 42 or 43, wherein the intermediate portion is conformable to an “S” shape.

45. A device comprising:

- a support structure comprising
  - a first end portion;
  - a second end portion;
  - an intermediate portion between the first end portion and the second end portion, at least one of the first end portion, the second end portion, and the intermediate portion being comprising cut struts and at least one of the first end portion, the second end portion, and the intermediate portion comprising filaments; and a graft material coupled to at least the intermediate portion.

46. The device of Embodiment 45, wherein the first end portion and the second end portion comprise cut struts and the intermediate portion comprises filaments.

47. The device of Embodiment 45 or 46, wherein at least some of the graft material is outside the intermediate portion, at least some of the graft material is inside the intermediate portion, or at least some of the graft material is embedded within the intermediate portion.

48. The device of any one of Embodiments 45-47, wherein the graft material is coupled to at least one of the first end portion and the second end portion.

49. The device of any one of Embodiments 45-48, wherein the device is capable of maintaining fluid flow between a first passage in which the first end portion is anchored and a second passage in which the second end portion is anchored.

50. The device of Embodiment 49, wherein the first passage is substantially parallel to the second passage.

51. The device ofEmbodiment 49 or 50, wherein the intermediate portion is conformable to an “S” shape.