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Stent-based venous valves

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Publication number
WO2002076349A1
WO2002076349A1 PCT/US2002/008610 US0208610W WO2002076349A1 WO 2002076349 A1 WO2002076349 A1 WO 2002076349A1 US 0208610 W US0208610 W US 0208610W WO 2002076349 A1 WO2002076349 A1 WO 2002076349A1
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WO
Grant status
Application
Patent type
Prior art keywords
stent
valve
venous
deformed
flaps
Prior art date
Application number
PCT/US2002/008610
Other languages
French (fr)
Inventor
Thomas W. Duerig
Andreas Melzer
Original Assignee
Cordis Corporation
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date

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Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02Prostheses implantable into the body
    • A61F2/24Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices
    • A61F2/2475Venous valves
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02Prostheses implantable into the body
    • A61F2/24Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices
    • A61F2/2412Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices with soft flexible valve members, e.g. tissue valves shaped like natural valves
    • A61F2/2418Scaffolds therefor, e.g. support stents
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/848Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents having means for fixation to the vessel wall, e.g. barbs
    • A61F2002/8486Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents having means for fixation to the vessel wall, e.g. barbs provided on at least one of the ends
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2220/00Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2220/0008Fixation appliances for connecting prostheses to the body
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2220/00Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2220/0008Fixation appliances for connecting prostheses to the body
    • A61F2220/0016Fixation appliances for connecting prostheses to the body with sharp anchoring protrusions, e.g. barbs, pins, spikes
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2220/00Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2220/0025Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
    • A61F2220/005Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements using adhesives
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2220/00Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2220/0025Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
    • A61F2220/0066Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements stapled
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2230/00Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2230/0002Two-dimensional shapes, e.g. cross-sections
    • A61F2230/0028Shapes in the form of latin or greek characters
    • A61F2230/0054V-shaped
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2230/00Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2230/0063Three-dimensional shapes
    • A61F2230/0067Three-dimensional shapes conical
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2250/00Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0058Additional features; Implant or prostheses properties not otherwise provided for
    • A61F2250/0096Markers and sensors for detecting a position or changes of a position of an implant, e.g. RF sensors, ultrasound markers
    • A61F2250/0098Markers and sensors for detecting a position or changes of a position of an implant, e.g. RF sensors, ultrasound markers radio-opaque, e.g. radio-opaque markers

Abstract

An artificial venous valve which incorporates a stent having one or more of the elements comprising its frame deformed inwardly towards its center and a biocompatible fabric attached to the one or more elements is utilized to replace or supplement incompetent or damaged venous valves. The elements are deformed and the fabric attached in such a way as to form valve flaps, which when there is no pressure differential on opposite sides of the flaps, substantially occludes the lumen of the vessel into which the artificial valve has been deployed. When there is a pressure differential, albeit slight, due to the pumping of the heart, the flaps easily open and allow blood to flow therethrough while substantially preventing backflow.

Description

STENT-BASED VENOUS VALVES

BACKGROUND OF THE INVENTION

1. Field of the Invention

The present invention relates to medical devices, and more particularly to stent-based venous valves.

2. Discussion of the Related Art

The vertebrate circulatory system comprises three major types of blood vessels; namely, arteries, capillaries and veins. Arteries carry oxygen-rich blood from the heart to the other organs and veins carry oxygen-depleted blood from the organs back to the heart. The pulmonary vein is an exception in that it carries oxygen-rich blood from the lungs to the heart. When an artery enters an organ, it divides into a multiplicity of smaller branches called arterioles. Metarterioles are small vessels that link arterioles to venules, which are the multiplicity of smaller vessels that branch from veins. Capillaries branch off from and are connected to metarterioles. Capillaries also interconnect with one another forming long and intricate capillary networks. After blood supplied by arteries courses through an organ via a capillary network, blood enters the venules which eventually merge into veins and is transported back to the heart.

Given the nature of the circulatory system, it is easy to understand that blood pressure in arteries is much greater than in veins. To compensate for the much lower blood pressure, veins comprise low flow resistance tissues and venous valves. The primary benefit of venous valves is their ability to limit the backflow of blood traveling through the venous portion of the circulatory system. Numerous venous valves are located throughout the veins, thereby ensuring that the blood travels through the veins and towards the heart.

The normally low blood pressure in the venous portion of the circulatory system is supplemented by the contraction of skeletal muscles. Essentially, the contraction of the muscles compresses and drives the blood through the veins. The venous valves check the backflow of blood through the veins, thereby ensuring that blood is driven back to the heart. The backflow checking function performed by the venous valves also minimizes the effect of a sudden increase in blood pressure caused, for example, by heavy exertion. In addition, venous valves also evenly distribute blood in the veins by segregating portions of blood flowing through the venous portion of the circulatory system. Any damage to the venous valves disrupts the normal flow of blood.

Venous valves are particularly important in the lower extremities. The venous system in the lower extremities generally consists of deep veins and superficial veins, which lie just below the skin surface. The deep and superficial veins are interconnected by perforating veins. Blood generally flows upwards through the legs towards the heart and from the superficial to deep veins. The venous valves are situated in the deep, superficial and perforating veins to ensure the normal direction of blood flow.

Venous valves can become incompetent or damaged by disease, for example, phlebitis, injury or the result of an inherited malformation.

Incompetent or damaged venous valves usually leak blood. The backflow of blood passing through leaking venous valves may cause numerous problems. As described above, blood normally flows upwards from the lower extremities, and from the superficial to deep veins. Leaking venous valves allow for blood regurgitation reflux causing blood to improperly flow back down through the veins. Blood can then stagnate in sections of certain veins, and in particular, the veins in the lower extremities. This stagnation of blood raises blood pressure and dilates the veins and venous valves. The dilation of one vein may in turn disrupt the proper functioning of other venous valves in a cascading manner. The dilation of these valves may lead to chronic venous insufficiency. Chronic venous insufficiency is a severe form of venous disease and is a pathological condition of the skin and subcutaneous tissues that results from venous hypertension and prolonged stasis of venous blood due to valvular incompetence both of a primary nature and of a secondary nature following past illnesses of the venous subsystem. Chronic venous insufficiency progresses through various stages of symptom severity which in order of severity include venous flare, edema, hyper-pigmentation i.e. discoloration of the skin, eczema, induration i.e. thickening of the skin, and ulcers. If neglected, chronic valve insufficiency may necessitate amputation of the neglected limb.

Numerous therapies have been advanced to treat symptoms and to correct incompetent valves. Less invasive procedures include compression, elevation and wound care. Compression involves the use of elastic stockings to compress the affected area. Compression is a conservative therapy and is typically effective in a majority of cases. However, the elastic stockings are uncomfortable and expensive. Continuous elevation is frequently used to treat venous ulcers. Elevation of the affected limb improves venous return, reduces the discomfort of ulcers, and encourages healing. Elevation, however, is contraindicated in patients with cardiopulmonary insufficiency. Wound care involves the use of antibiotics and antiseptics. Topical antibiotics and antiseptics are frequently utilized to treat ulcers. Zinc paste bandages have been a primary dressing for over a century. However, these treatments tend to be somewhat expensive and are not curative. Other procedures involve surgical intervention to repair, reconstruct or replace the incompetent or damaged venous valves.

Surgical procedures for incompetent or damaged venous valves include valvuloplasty, transplantation, and transposition of veins. Valvuloplasty involves the surgical reconstruction of the valve. Essentially, valvuloplasty is a procedure to surgically modify the venous valves to "tighten" them. Transposition of veins involves surgically bypassing sections of veins possessing the incompetent or damaged valves with veins possessing viable valves. Transplantation involves surgically transplanting one or more of a patient's viable valves for the incompetent or damaged valve. A more detailed discussion of these surgical procedures is given in "Reconstruction of Venous Valves", R. Gottlub and R. Moy, Venous Valves, 1986, Part V, section 3.

The above-described surgical procedures provide somewhat limited results. The leaflets of venous valves are generally thin, and once the valve becomes incompetent or destroyed, any repair provides only marginal relief. Venous valves may also be damaged when the valve is being reconstructed, * transpositioned, or transplanted. The endothelium tissue layer of the vein may also be damaged during handling. This reduces the viability of the vein graft after implant. Another disadvantage with transplantation procedures is the need to use the patient's own vein segment in order to avoid the complications posed by rejection. In addition, the use of a patient's own vein segment predisposes that the incompetence or damage did not arise from inherited factors or diseases which will affect the transplanted valve.

Another surgical procedure involves the removal of the valve. In this procedure, the incompetent or damaged valve is completely removed. While this procedure removes any potential impediment to normal blood flow, it does not solve the backflow problem. As an alternative to surgical intervention, drug therapy to correct venous valvular incompetence has been utilized. Currently, however, there are no effective drug therapies available.

Other means and methods for treating and/or correcting damaged or incompetent valves include utilizing xenograft valve transplantation (monocusp bovine pericardium), prosthetic/bioprosthetic heart valves and vascular grafts, and artificial venous valves. The use of xenograft valve transplantation is still in the experimental stages. In addition, after a given amount of time, it has been found that luminal deposits of fibrous material develops. Prosthetic heart valves are usually made from porcine valves and porcine heart valves have a geometry unsuitable as a replacement for venous valves. These types of valves are also generally larger than venous valves, and include vaive leaflets generally thicker and stiffer than the leaflets of venous valves. The thicker heart valve leaflets require a greater opening pressure. The greater required opening pressure makes such valves unsuitable for the venous system. Artificial venous valves are known in the art. For example, U.S. Patent No.

5,358,518 to Camilli discloses an artificial venous valve. The device comprises a hollow elongated support and a plate mounted therein. The plate is moveably mounted such that when in a first position, blood flows through the valve and when in a second position, blood cannot flow through the valve. A pressure differential drives the plate. Although the device is made from biocompatible materials, the use of non-physiological materials in this type of pivoting plate arrangement increases the risk of hemolysis and/or thrombosis. SUMMARY OF THE INVENTION

The stent-based venous valve of the present invention provides a means for overcoming the difficulties associated with the treatments and devices as briefly described above. In accordance with one aspect, the present invention is directed to an artificial venous valve. The artificial venous valve comprises a stent formed from a lattice of interconnected elements and having a substantially cylindrical configuration with first and second open ends. One or more of the elements are deformed inwardly out of the circumferential plane. The artificial venous valve also comprises a biocompatible material attached to the one or more elements thereby forming one or more valve flaps.

In accordance with another aspect, the present invention is directed to an artificial venous valve. The artificial venous valve comprises a self- expanding stent formed from a lattice of interconnected elements and having a substantially cylindrical configuration with first and second open ends and a compressed diameter for insertion into a vessel and an expanded diameter for deployment into the vessel. The one or more of the elements are deformed out of the circumferential plane at a first angle when the self-expanding stent is at its compressed diameter and at a second angle when the self-expanding stent is at its expanded diameter. The second angle is greater than the first angle. The artificial venous valve also comprises a biocompatible material attached to the one or more elements thereby forming one or more valve flaps.

The stent-based venous valve of the present invention utilizes a modified self-expanding stent to create an effective artificial venous valve. One or more elements comprising the framework of the self-expanding stent are deformed out of the circumferential plane and towards the center of the stent and a lightweight, biocompatible fabric is attached thereto. The attachment of the fabric to the elements creates flaps which function to regulate the flow of blood in the veins into which it is positioned. The slightly higher blood pressure upstream of the stent easily opens the flaps and allows the blood to flow through. In the absence of a pressure differential, the flaps return to their normally closed position, thereby substantially preventing the backflow of blood. The stent-based venous valve of the present invention may be percutaneously delivered to the venous sub-system by releasing it from a catheter to assist or replace deteriorating natural venous valves by allowing flow towards the heart and preventing backflow. Since the venous valve is percutaneously delivered, the whole procedure is minimally invasive. The stent-based venous valve creates very little resistance in the vessel and offers minimal complication risks. In addition, since the stent-based venous valve utilizes modified existing technology, physicians will be more comfortable performing the valve replacement procedure. The stent-based venous valve of the present invention may be more cost effectively manufactured by utilizing existing manufacturing techniques that are currently used for the manufacture of stents with only slight modification. Accordingly, high quality, reliable venous valves may be easily manufactured at relatively low cost.

BRIEF DESCRIPTION OF THE DRAWINGS

The foregoing and other features and advantages of the invention will be apparent from the following, more particular description of preferred embodiments of the invention, as illustrated in the accompanying drawings. Figure 1 is a perspective view of a stent in a compressed state in accordance with the present invention.

Figure 2 is a sectional, flat view of the stent illustrated in Figure 1.

Figure 3 is an enlarged view of the section of the stent illustrated in Figure 2. Figure 4 is a perspective view of the stent illustrated in Figure 1 in its expanded state.

Figure 5 is a perspective view of the stent-based venous valve in accordance with the present invention.

Figure 6 is an end view of the stent-based venous valve in accordance with the present invention.

Figure 7 is an end view of the stent-based venous valve having a single valve flap in accordance with the present invention. Figure 8 is an end view of the stent-based venous valve having two valve flaps in accordance with the present invention.

Figure 9 is an enlarged perspective view of the end of the stent-based venous valve having a tab in accordance with the present invention. Figure 10 is an enlarged perspective end view of the stent-based venous valve having a radiopaque marker in accordance with the present invention.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS The stent-based venous valve of the present invention comprises a self- expanding stent in which one or more of its elements are deformed inwardly towards its center, and a biocompatible fabric which is attached to the one or more deformed elements. With no pressure differential between the upstream and downstream ends of the venous valve, the fabric covered elements substantially occlude the lumen. When there is a pressure differential, albeit slight, due to the pumping of the heart, the fabric covered elements open easily and allow blood to flow therethrough with substantially no backflow. Given the design of the circulatory system, the pressure in the upstream portion of the venous system should always be higher than the pressure downstream. The venous valve is percutaneously delivered to the venous system by releasing it from a delivery catheter and functions to assist or replace incompetent or damaged natural venous valves by allowing normal blood flow and preventing or reducing backflow. Although any self-expanding stent may be utilized in constructing the venous valve, for ease of explanation, the exemplary embodiments described below will be with reference to one particular self- expanding stent design as set forth herein.

Referring to Figures 1-3, there is illustrated an exemplary stent 100 in accordance with the present invention. Figures 1-3 illustrate the stent 100 in its unexpanded or compressed state. In a preferred embodiment, the stent 100 comprises a superelastic alloy such as Nitinol. More preferably, the stent 100 is formed from an alloy comprising from about 50.5 to 60.0 percent Ni by atomic weight and the remainder Ti. Even more preferably, the stent 100 is formed from an alloy comprising about 55 percent Ni and about 45 percent Ti. The stent 100 is preferably designed such that it is superelastic at body temperature, and preferably has an Af temperature in the range from about 24° C to about 37° C. The superelastic design of the stent 100 makes it crush recoverable and thus suitable as a stent or frame for any number of vascular devices for different applications.

The stent 100 comprises a tubular configuration having front and back open ends 102, 104 and defining a longitudinal axis 103 extending therebetween. The stent 100 has a first diameter for insertion into a patient and navigation through the vessels and a second diameter for deployment into the target area of a vessel with the second diameter being greater than the first diameter. The stent 100 comprises a plurality of adjacent hoops 106(a)-(d) extending between the front and back ends 102, 104. The hoops 106(a)-(d) include a plurality of longitudinally arranged struts 108 and a plurality of loops 110 connecting adjacent struts 108. Adjacent struts 108 are connected at opposite ends so as to form a substantially S or Z shape pattern. The plurality of loops 110 have a substantially semi-circular configuration and are substantially symmetric about their centers 112.

The stent 100 further comprises a plurality of bridges 114, which connect adjacent hoops 106(a)-(d). The details of the bridges 114 are more fully illustrated in Figure 3. Each bridge comprises two ends 116, 118. One end of each bridge 114 is attached to one loop 110 on one hoop 106(a) and the other end of each bridge 114 is attached to one loop 110 on an adjacent hoop 106(b). The bridges 114 connect adjacent hoops 106(a)-(d) together at bridge to loop connection regions 120,122. For example, bridge end 116 is connected to loop 110(a) at bridge to loop connection region 120, and bridge end 118 is connected to loop 110(b) at bridge to loop connection region 122. Each bridge to loop connection region includes a center 124. The bridge to loop connection regions 120, 122, are separated angularly with respect to the longitudinal axis 103 of the stent 100. In other words, and as illustrated in Figure 3, a straight line drawn between the center 124 of each bridge to loop connection region 120, 122 on a bridge 114 would not be parallel to the longitudinal axis 103 of the stent 100. The above-described geometry better distributes strain throughout the stent 100, prevents metal to metal contact where the stent 100 is bent, and minimizes the opening between the features of the stent 100; namely, struts 108, loops 110 and bridges 114. The number of and nature of the design of the struts, loops and bridges are important design factors when determining the working properties and fatigue life properties of the stent. It was previously thought that in order to improve the rigidity of the stent, struts should be large, and thus there should be fewer struts per hoop. However, it is now known that stents having smaller struts and more struts per hoop improve the construction of the stent and provide greater rigidity. Preferably, each hoop has between twenty-four (24) to thirty-six (36) or more struts. It has been determined that a stent having a ratio of number of struts per hoop to strut length which is greater than four hundred has increased rigidity over prior art stents which typically have a ratio of under two hundred. The length of a strut (L) is measured in its compressed state parallel to the longitudinal axis 103 of the stent 100 as illustrated in Figure 3.

Figure 4 illustrates the stent 100 in its expanded state. As may be seen from a comparison between the stent 100 illustrated in Figures 1-3 and the stent 100 illustrated in Figure 4, the geometry of the stent 100 changes quite significantly as it is deployed from its unexpanded state to its expanded state. As a stent undergoes diametric change, the strut angle and strain levels in the loops and bridges are affected. Preferably, all of the stent features will strain in a predictable manner so that the stent is reliable and uniform in strength. In addition, it is preferable to minimize the maximum strain experienced by the struts, loops and bridges since Nitinol properties are more generally limited by strain rather than by stress.

In trying to minimize the maximum strain experienced by the features of the stent, the present invention makes use of structural geometries which distribute strain to areas of the strut which are less susceptible to failure than others. For example, one of the more vulnerable areas of the stent is the inside radius of the connecting loops. In going from its unexpanded state to its expanded state the connecting loops of the stent undergo the most deformation of all the stent features. The inside radius of the loop would normally be the area with the highest level of strain on the stent. This area is also critical in that it is usually the smallest radius on the stent. Stress concentrations are generally minimized by maintaining the largest radii possible. Similarly, it is preferable to minimize local strain concentrations on the bridge and bridge connection points. One way to accomplish this is to utilize the largest possible radii while maintaining feature widths, which are consistent with applied forces. Another consideration is to minimize the maximum open area of the stent. Efficient utilization of the original tube from which the stent is cut, described subsequently, increases the strength of the stent and increases its ability to trap embolic material.

Many of these design objectives are accomplished in a preferred embodiment of the stent of the present invention as illustrated in Figures 1-3. As seen from these figures, the most compact designs, which maintain the largest radii at the loop to bridge connections, are non-symmetric with respect to the centeriine of the loop. That is, loop to bridge connection region centers 124 are off set from the center 112 of the loops 110 to which they are attached. This feature is particularly advantageous for stents having large expansion ratios, which in turn requires them to have extreme bending requirements where large elastic strains are required. Nitinol can withstand extremely high elastic strain deformation, so the above features are well suited to stents made from this alloy. Therefore, this design feature allows for maximum utilization of the properties of Nitinol to enhance stent radial strength, improve stent strength uniformity and improve stent fatigue life by minimizing local strain levels. In addition, this design feature allows for smaller open areas which enhance entrapment of embolic material and improve stent opposition in irregular vessel wall shapes and curves.

As illustrated in Figure 3, the stent 100 comprises loops 110 each having a width, W1 , as measured at its center 112 and parallel to axis 103 (illustrated in Figures 1 and 2), which is greater than the width, W2, of each of the struts 108, as measured perpendicular to the axis 103. In a preferred embodiment, the loops 110 have a variable thickness wherein they are thicker at their centers 64. This configuration increases strain deformation at the strut and reduces the maximum strain levels at the extreme radii of the loop. This reduces the risk of stent failure and allows for maximization of the radial strength properties of the stent. This feature is particularly advantageous for stents having large expansion ratios, which in turn requires them to have extreme bending requirements where large elastic strains are required. As mentioned above, as a stent undergoes diametric change, strut angle and loop strain is affected. Given that the bridges connect loops on adjacent hoops, the bridges are affected by the application of a torque anywhere along the length of the stent. If the bridge design is duplicated around the stent perimeter, the displacement causes a rotational shifting of the two loops connected by each bridge. If the bridge design is duplicated throughout the stent, this shift will occur down the length of the stent. This is a cumulative effect as one considers rotation of one end with respect to the other, for example, upon deployment. When a strut is loaded into a delivery system, the stent may be twisted, thereby causing the above-described rotational shifting. Typically, stent delivery systems deploy the distal end of the stent first and then allow the proximal end to expand. It would be undesirable to allow the distal end of the stent to anchor into the vessel wall while holding the remainder of the stent fixed and then deploying the proximal end of the stent thereby potentially causing the proximal end to rotate as it expands and unwinds. Such rotation may cause damage to the vessel.

In the exemplary embodiment described herein, the above-described problem is minimized by mirroring the bridge geometry longitudinally down the stent. Essentially, by mirroring the bridge geometry longitudinally along the stent, the rotational shift of the S-shaped sections may be made to alternate which will minimize large rotational changes between any two points on a given stent during deployment or constraint. As illustrated in Figure 2, the bridges 114 connecting hoop 106(b) to hoop 106(c) are angled upwardly from left to right, while the bridge 114 connecting hoop 106(c) to hoop 106(d) are angled downwardly from left to right. This alternating pattern is repeated down the length of the stent. This alternating pattern of bridge shapes improves the torsional characteristics of the stent so as to minimize any twisting or rotation of the stent with respect to any two hoops. This alternating bridge shape is particularly beneficial if the stent starts to twist in vivo. Alternating bridge shapes tend to minimize this effect. The diameter of a stent having bridges which are all shaped in the same direction will tend to grow if twisted in one direction and shrink if twisted in the other direction. With alternating bridge shapes, this effect is minimized and localized. Preferably, stents are laser cut from small diameter tubing. For prior art stents, this manufacturing process leads to designs with features having axial widths which are larger than the tube wall thickness from which the stent is cut. When the stent is compressed, most of the bending occurs in the plane that is created if one were to cut longitudinally down the stent and flatten it out. However, for the individual bridges, loops and struts with widths greater than their thicknesses have a greater resistance to this in-plane bending than they do to out-of-plane bending. Given this, the bridges and struts tend to twist so that the stent as a whole can bend more easily. This twisting is essentially a buckling which is unpredictable and can cause potentially high strain. However, in a preferred embodiment of the present invention as illustrated in Figure 3, the widths of the struts (W2), loops (W1 ) and bridges (W3) are equal to or less than the wall thickness of the tube from which the stent is cut. Therefore, substantially all bending, and therefore, all strains are out-of-plane. This minimizes twisting of the stent, which minimizes or eliminates buckling and unpredictable strain conditions.

As briefly described above, the stent-based venous valve of the present invention comprises a self-expanding stent in which one or more of its elements are deformed inwardly towards its center, and a biocompatible fabric which is attached to the one or more deformed elements to form one or more valve flaps. In order to prevent the backflow of blood, the one or more valve flaps preferably occlude the lumen of the stent when there is no pressure differential between the upstream and downstream regions of the stent. Essentially, the occlusion of the stent lumen, and thus the vessel in which the stent is positioned, is the neutral position for the one or more valve flaps. Under normal circumstances, the pressure upstream is greater than the pressure downstream due to the nature of the circulatory system, as briefly described above. This pressure differential, albeit slight, easily opens the one or more valve flaps and allows the blood to flow substantially unimpeded. The one or more valve flaps may be positioned anywhere within the stent, including proximate to one of the open ends of the stent. In the exemplary embodiment illustrated in Figure 5, the one or more valve flaps 500 are positioned substantially in the center of the stent 100 as measured along the longitudinal axis 103. It is important to note that a multiplicity of different stent designs exist and that the stent-based venous valve may be constructed utilizing any of these stents.

Referring to Figure 6, there is illustrated an end view of the stent-based venous valve 600 of the present invention. Any of the elements comprising the stent 100 may be deformed inwardly to form the frame or support structure of the one or more valve flaps. For example, the bridges 114, struts 108 and/or loops 110 may be utilized. In the exemplary embodiment illustrated in Figure 6, the struts 108 are utilized. In order to deform the struts 108 out of the circumferential plane, the struts 108 have to be severed. The length of the deformed strut 108 and thus the point at which it is severed along its length depends on a number of factors, including the diameter of the stent 100, the number of deformed struts 108 comprising the frame of a valve flap and the number of valve flaps. With respect to the diameter factor, the length of the deformed strut 108 may vary with stent 100 diameter in order to provide sufficient support for the one or more valve flaps. For example, as the diameter of the stent 100 increases, the length of the deformed strut 108 should also preferably increase to compensate for the increased surface area of the one or more valve flaps. With respect to the number of deformed struts 108 comprising each frame of the one or more valve flaps and the number of valve flaps, it is obvious that the length of the deformed struts 108 will vary depending on the design and number of the one or more valve flaps. For example, if triangularly shaped valve flaps are utilized, two deformed struts 108 may be utilized as the legs of the triangularly shaped valve flap, and the length of the deformed struts 108 should be substantially equal to the radius of the stent 100 so that the apex of each triangularly shaped valve flap meets and is supported in the center of the lumen in order to substantially occlude the lumen in the absence of a pressure differential as described above. Any number of valve flaps having any number of configurations may be utilized in the stent-based venous valve of the present invention. In one exemplary embodiment, a single valve flap may be formed utilizing one or more deformed struts 108. For example, as illustrated in Figure 7, a single deformed strut 108 may support a substantially circularly shaped section 702 of biocompatible fabric having a diameter substantially equal to the inner diameter of the stent 100. In another exemplary embodiment, as illustrated in Figure 8, two valve flaps 802 may be formed utilizing one or more deformed struts 108. For example, back to back substantially D-shaped valve flaps may be utilized. In the exemplary embodiment illustrated in Figure 6, six substantially triangularly shaped valve flaps 602 are utilized. The valve flaps 602 cannot have a true triangular shape because the base of each valve flap 602 is curved to fit the circumferential arc of the stent 100. Each valve flap 602 comprises two deformed struts 108, which are angled to form the legs of the valve flap 602. Given that there are six valve flaps 602, each comprising two deformed struts 108, a total of twelve deformed struts 108 are utilized. Each of the deformed struts 108 extends from the wall of the stent 100 towards the center of the lumen such that their distal ends are proximate one another. Each of the deformed struts 108 may extend from the circumferential plane of the stent 100 substantially perpendicular thereto, or at any other angle as long as the distal ends terminate proximate to the center of the lumen. As stated above, the deformed struts 108 should be long enough to provide sufficient support for the valve flaps 602. Accordingly, depending on the angle, the length of each of the deformed struts 108 may vary. If any other angle other than ninety degrees is utilized, the deformed struts will be pointing more towards one of the open ends 102, 104 of the stent 100 than the center of the stent 100. In a preferred embodiment, the deformed struts 108 and thus the valve flaps 602, extend at an angle in the range from about twenty degrees to about seventy degrees. The end of the stent 100 towards which the deformed struts 108 are angled is the downstream end of the stent-based venous valve. With the angle of the deformed struts 108 in the above range, the valve flaps 602 easily open under the pressure differential existing in the venous position of the circulatory system. Accordingly, the downstream end of the stent-based venous valve 602 should be positioned at the downstream end of the section of the vein where the stent-based venous valve 600 is to be positioned.

In addition to the above described advantage of angling the valve flaps 602, the angling of the valve flaps 602 allows the stent-based venous valve 600 to be compressed for delivery. When the stent-based venous valve 600 is collapsed for insertion into the vein of a patient, the valve flaps 602 simply deflect further along the longitudinal axis in the direction in which they are angled, thereby reducing the angle of the deformed struts 108. When the stent-based venous valve 600 is expanded during deployment, the valve flaps 602 return to an angle in the range set forth above.

In order to maintain the strength of the deformed struts 108 comprising the frames of the valve flaps 602 while affording adequate fatigue lifetime, it is preferable to have struts 108 with variable strut width, i.e., zones of reduced stiffness where the strut 108 begins to bend out of the circumferential plane of the stent 100. The struts 108 may be deformed at any time during the stent manufacturing process described subsequently, or upon completion of the stent manufacturing process as part of a separate valve manufacturing process.

Each of the valve flaps 602 comprise the frame formed from the deformed elements 108 as described above, and a biocompatible material attached thereto. Any suitable lightweight, strong, fluid impervious, biocompatible material may be utilized. In a preferred embodiment, a Dacron® or Teflon® fabric may be utilized. The fabric may be attached in any suitable manner and by any suitable means. For example, the fabric may be removably attached or permanently attached to the deformed elements. The fabric may be attached to the elements utilizing sutures, staples, chemical/heat bonding and/or adhesive. In a preferred embodiment, the fabric is attached utilizing sutures.

It may be necessary to include anchors to prevent migration of the stent- based venous valve due to the weight of the blood upstream of the valve flaps 602. Such anchors would be incorporated by bending metallic features of the stent 100 outwards from the circumferential plane of the stent 100. In other words, one or more of the elements comprising the stent 100 may be deformed outwardly from the stent 100 and formed into hooks or barbs which may be made to engage the endoluminal surface of the host vein.

Stents may be manufactured from a number of different materials and utilizing a number of different processes/techniques. The nickel-titanium self- expanding stent utilized in the stent-based venous valve of the present invention is preferably manufactured utilizing the materials and processes as generally described below. Sections of Nitinol tubing are cut into stents by machines in which the tubing is secured into position while a laser cuts predetermined patterns, such as the patterns described above, out of the tubing. Essentially, the machines are adapted to hold the tubing at its open ends while a cutting laser, preferably under microprocessor control, cuts the predetermined pattern. The pattern dimensions, geometries and associated laser positioning requirements are preprogrammed into a microprocessor based system, which controls all aspects of the laser cutting process. The length and the diameter of the section of tubing depends upon the size of the stent to be manufactured. Although stents are manufactured at a number of fixed dimensions, any size stent may be manufactured utilizing these techniques. Nitinol tubing is commercially available from a number of suppliers, including Nitinol Devices and Components, Freemont, California. Also, the cutting machines are commercially available and their use is known in the art.

Upon completion of the stent cutting step, the rough stent is treated and polished. The rough stent may be polished utilizing any number of processes well known to those skilled in the relevant art, including electropolishing and chemical polishing. The rough stents may be polished to the desired smoothness using one or more polishing techniques. The polished stent preferably has smooth surfaces with substantially no surface irregularities that might cause damage during or after deployment into a target vessel. The polished stent is then cooled until it is completely martensitic, crimped down to its unexpanded diameter and loaded into the sheath of a delivery apparatus, which are known to those of ordinary skill in the relevant art.

At various stages in the above-described manufacturing process, the stents are inspected to ensure that it meets all design requirements and all quality requirements. For example, the stents are preferably inspected/tested using a number of criteria, including pattern regularity, smoothness and dimension. A particular stent which fails to meet a certain criterion may be reworked one or more times in order to correct the defect, depending on where in the process it failed. The number of times a stent may be reworked is limited. However, the nickel-titanium alloy itself may always be re-utilized.

In order to manufacture the stent-based venous valve of the present invention, the above process may be modified and/or further steps may be added. For example, the cutting step may be modified such that certain elements are severed and then deformed inwards in a separate step as described above. The biocompatible fabric may be attached to the deformed elements upon completion of the polishing step and preferably prior to the crimping step utilizing any of the attachment means/methods described above. The attachment of the fabric may be done manually or by an automated means. The completed stent-based venous valve may be crimped similarly to a stent and loaded into a stent delivery device. The design and operation of stent delivery systems are well known in the art.

A concern with stents in general, as well as other medical devices, is that they may exhibit reduced radiopacity under X-ray fluoroscopy. To overcome this problem, it is common practice to attach markers made from highly radiopaque materials to the stent, or to use radiopaque materials in plating or coating processes. Those materials are typically gold, platinum, or tantalum. However, due to the relative position of these materials in the galvanic series versus the position of the base metal of the stent in the galvanic series, there is a certain challenge to overcome; namely, that of galvanic corrosion.

Referring to Figure 9, there is illustrated another exemplary embodiment of the present invention. In this exemplary embodiment, the cutting pattern of the stent 100 includes at least one tab or marker 900 attached to the loops 110 at the front and back ends of the stent 100. These tabs 900 may be formed from any suitable material, and are preferably formed from a highly radiopaque material to assist in positioning the stent-based venous valve within the lumen of the vessel. In this exemplary embodiment, it is preferable to "micro-alloy" a radiopaque material like gold, platinum, tantalum, niobium, molybdenum, rhodium, palladium, silver, hafnium, tungsten or iridium with the nickel titanium at specific locations and on specific features of the stent, for example tabs 900. Once the predetermined pattern is cut into the tubular member, as described above, in a secondary process, performed in a protective atmosphere or under vacuum, the tabs 900 or other features may selectively be melted by the application of heat from a source, while a predetermined amount of the radiopaque material is added. Means for applying this heat may include devices such as lasers, induction heating, electric arc melting, resistance heating and electron beam melting, and are well known to those of ordinary skill in the art, and are commercially available. Through surface tension, the molten pool will form a sphere 1000, as illustrated in Figure 10. The sphere 1000 remains attached to the device upon solidification. The sphere 1000 includes a micro-alloy of nickel titanium and a radiopaque alloy chosen from a group consisting of gold, platinum, tantalum, niobium, molybdenum, rhodium, palladium, silver, hafnium, tungsten and iridium, while the chemical composition of the balance of the device remains unchanged. The resulting nickel titanium alloy has a much reduced tendency to create a galvanic element with the binary nickel titanium. Although shown and described is what is believed to be the most practical and preferred embodiments, it is apparent that departures from specific designs and methods described and shown will suggest themselves to those skilled in the art and may be used without departing from the spirit and scope of the invention. The present invention is not restricted to the particular constructions described and illustrated, but should be constructed to cohere with all modifications that may fall within the scope of the appended claims.

Claims

WHAT IS CLAIMED IS:
1. An artificial venous valve comprising: a stent formed from a lattice of interconnected elements and having a substantially cylindrical configuration with first and second open ends, wherein one or more of the elements are deformed inwardly out of the circumferential plane; and a biocompatible material attached to the one or more elements thereby forming one or more valve flaps.
2. The artificial venous valve according to claim 1 , wherein the stent comprises: a plurality of hoops formed from a plurality of struts connected by a plurality of loops; and a plurality of bridges connecting adjacent hoops.
3. The artificial venous valve according to claim 1 , wherein the stent comprises a superelastic alloy.
4. The artificial venous valve according to claim 3, wherein the alloy comprises from about 50.5 percent to about 60 percent nickel and the remainder comprising titanium.
5. The artificial venous valve according to claim 2, wherein the one or more valve flaps each comprise two deformed elements arranged to form a substantially triangularly shaped support frame.
6. The artificial venous valve according to claim 5, wherein the deformed elements are angled towards one of the first and second open ends at an angle in the range from about twenty degrees to about seventy degrees.
7. The artificial venous valve according to claim 6, wherein the deformed elements are thinner where they are deformed out of the circumferential plane.
8. The artificial venous valve according to claim 1 , wherein the one or more valve flaps are dimensioned to substantially occlude the stent when there are no differential forces acting on the valve flaps.
9. The artificial venous valve according to claim 8, comprising six valve flaps.
10. The artificial venous valve according to claim 1 , wherein the biocompatible material comprises Teflon®.
11. The artificial venous valve according to claim 1 , wherein the biocompatible material comprises Dacron®.
12. An artificial venous valve comprising: a self-expanding stent formed from a lattice of interconnected elements and having a substantially cylindrical configuration with first and second ends and a compressed diameter for insertion into a vessel and an expanded diameter for deployment into the vessel, wherein the one or more of the elements are deformed out of the circumferential plane at a first angle when the self-expanding stent is at its compressed diameter and at a second angle when the self-expanding stent is at its expanded diameter, the second angle being greater than the first angle; and a biocompatible fabric attached to the one or more elements thereby forming one or more valve flaps.
13. The artificial venous valve according to claim 12, wherein the self- expanding stent comprises: a plurality of hoops formed from a plurality of struts connected by a plurality of loops; and a plurality of bridges connecting adjacent hoops.
14. The artificial venous valve according to claim 12, wherein the self- expanding stent comprises a superelastic alloy.
15. The artificial venous valve according to claim 14, wherein the alloy comprises from about 50.5 percent to about 60 percent nickel and the remainder comprising titanium.
16. The artificial venous valve according to claim 14, wherein the one or more valve flaps each comprise two deformed elements arranged to form a substantially triangularly shaped support frame.
17. The artificial venous valve according to claim 14, wherein the second angle is in the range from about twenty degrees to about seventy degrees.
18. The artificial venous valve according to claim 17, wherein the deformed elements are thinner where they are deformed out of the circumferential plane.
19. The artificial venous valve according to claim 12, wherein the one or more valve flaps are dimensioned to substantially occlude the stent when there are no differential forces acting on the valve flaps.
PCT/US2002/008610 2001-03-21 2002-03-20 Stent-based venous valves WO2002076349A1 (en)

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EP20020717683 EP1370201B1 (en) 2001-03-21 2002-03-20 Stent-based venous valves
CA 2441999 CA2441999C (en) 2001-03-21 2002-03-20 Stent-based venous valves
JP2002574866A JP4381681B2 (en) 2001-03-21 2002-03-20 The stent substrate type venous valve

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Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP1212991A3 (en) * 2000-12-07 2004-01-02 Cordis Corporation An intravascular device with improved radiopacity
US7377938B2 (en) 2001-07-19 2008-05-27 The Cleveland Clinic Foundation Prosthetic cardiac value and method for making same
US9216082B2 (en) 2005-12-22 2015-12-22 Symetis Sa Stent-valves for valve replacement and associated methods and systems for surgery
US9839513B2 (en) 2007-10-25 2017-12-12 Symetis Sa Stents, valved-stents and methods and systems for delivery thereof

Families Citing this family (332)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5954766A (en) * 1997-09-16 1999-09-21 Zadno-Azizi; Gholam-Reza Body fluid flow control device
US6006134A (en) * 1998-04-30 1999-12-21 Medtronic, Inc. Method and device for electronically controlling the beating of a heart using venous electrical stimulation of nerve fibers
US7452371B2 (en) * 1999-06-02 2008-11-18 Cook Incorporated Implantable vascular device
US8382822B2 (en) * 1999-06-02 2013-02-26 Cook Medical Technologies Llc Implantable vascular device
US7887578B2 (en) * 1998-09-05 2011-02-15 Abbott Laboratories Vascular Enterprises Limited Stent having an expandable web structure
US7815763B2 (en) * 2001-09-28 2010-10-19 Abbott Laboratories Vascular Enterprises Limited Porous membranes for medical implants and methods of manufacture
US6682554B2 (en) 1998-09-05 2004-01-27 Jomed Gmbh Methods and apparatus for a stent having an expandable web structure
US6755856B2 (en) 1998-09-05 2004-06-29 Abbott Laboratories Vascular Enterprises Limited Methods and apparatus for stenting comprising enhanced embolic protection, coupled with improved protection against restenosis and thrombus formation
US20020019660A1 (en) * 1998-09-05 2002-02-14 Marc Gianotti Methods and apparatus for a curved stent
US6254564B1 (en) 1998-09-10 2001-07-03 Percardia, Inc. Left ventricular conduit with blood vessel graft
US7749245B2 (en) 2000-01-27 2010-07-06 Medtronic, Inc. Cardiac valve procedure methods and devices
US6790229B1 (en) * 1999-05-25 2004-09-14 Eric Berreklouw Fixing device, in particular for fixing to vascular wall tissue
US20050267560A1 (en) * 2000-02-03 2005-12-01 Cook Incorporated Implantable bioabsorbable valve support frame
US8038708B2 (en) * 2001-02-05 2011-10-18 Cook Medical Technologies Llc Implantable device with remodelable material and covering material
US7628803B2 (en) * 2001-02-05 2009-12-08 Cook Incorporated Implantable vascular device
US7201771B2 (en) 2001-12-27 2007-04-10 Arbor Surgical Technologies, Inc. Bioprosthetic heart valve
US6440164B1 (en) * 1999-10-21 2002-08-27 Scimed Life Systems, Inc. Implantable prosthetic valve
US8016877B2 (en) * 1999-11-17 2011-09-13 Medtronic Corevalve Llc Prosthetic valve for transluminal delivery
US7018406B2 (en) * 1999-11-17 2006-03-28 Corevalve Sa Prosthetic valve for transluminal delivery
US20070043435A1 (en) * 1999-11-17 2007-02-22 Jacques Seguin Non-cylindrical prosthetic valve system for transluminal delivery
US8579966B2 (en) 1999-11-17 2013-11-12 Medtronic Corevalve Llc Prosthetic valve for transluminal delivery
US8241274B2 (en) 2000-01-19 2012-08-14 Medtronic, Inc. Method for guiding a medical device
US7798147B2 (en) 2001-03-02 2010-09-21 Pulmonx Corporation Bronchial flow control devices with membrane seal
US20040074491A1 (en) * 2001-03-02 2004-04-22 Michael Hendricksen Delivery methods and devices for implantable bronchial isolation devices
US6679264B1 (en) 2000-03-04 2004-01-20 Emphasys Medical, Inc. Methods and devices for use in performing pulmonary procedures
US8474460B2 (en) 2000-03-04 2013-07-02 Pulmonx Corporation Implanted bronchial isolation devices and methods
US7321677B2 (en) * 2000-05-09 2008-01-22 Paieon Inc. System and method for three-dimensional reconstruction of an artery
US6973617B1 (en) * 2000-05-24 2005-12-06 Cisco Technology, Inc. Apparatus and method for contacting a customer support line on customer's behalf and having a customer support representative contact the customer
US6676698B2 (en) * 2000-06-26 2004-01-13 Rex Medicol, L.P. Vascular device with valve for approximating vessel wall
US6695878B2 (en) * 2000-06-26 2004-02-24 Rex Medical, L.P. Vascular device for valve leaflet apposition
WO2002005888A1 (en) 2000-06-30 2002-01-24 Viacor Incorporated Intravascular filter with debris entrapment mechanism
US8623077B2 (en) 2001-06-29 2014-01-07 Medtronic, Inc. Apparatus for replacing a cardiac valve
US8771302B2 (en) * 2001-06-29 2014-07-08 Medtronic, Inc. Method and apparatus for resecting and replacing an aortic valve
US7544206B2 (en) 2001-06-29 2009-06-09 Medtronic, Inc. Method and apparatus for resecting and replacing an aortic valve
EP1401358B1 (en) * 2000-06-30 2016-08-17 Medtronic, Inc. Apparatus for performing a procedure on a cardiac valve
US7097659B2 (en) * 2001-09-07 2006-08-29 Medtronic, Inc. Fixation band for affixing a prosthetic heart valve to tissue
US7402173B2 (en) * 2000-09-18 2008-07-22 Boston Scientific Scimed, Inc. Metal stent with surface layer of noble metal oxide and method of fabrication
US7101391B2 (en) * 2000-09-18 2006-09-05 Inflow Dynamics Inc. Primarily niobium stent
US7527646B2 (en) * 2000-09-20 2009-05-05 Ample Medical, Inc. Devices, systems, and methods for retaining a native heart valve leaflet
US6893459B1 (en) * 2000-09-20 2005-05-17 Ample Medical, Inc. Heart valve annulus device and method of using same
US20090287179A1 (en) 2003-10-01 2009-11-19 Ample Medical, Inc. Devices, systems, and methods for reshaping a heart valve annulus, including the use of magnetic tools
US8956407B2 (en) * 2000-09-20 2015-02-17 Mvrx, Inc. Methods for reshaping a heart valve annulus using a tensioning implant
US6602286B1 (en) 2000-10-26 2003-08-05 Ernst Peter Strecker Implantable valve system
US20070173911A1 (en) * 2001-02-20 2007-07-26 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
US20070168006A1 (en) * 2001-02-20 2007-07-19 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
US20070168005A1 (en) * 2001-02-20 2007-07-19 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
US6829509B1 (en) * 2001-02-20 2004-12-07 Biophan Technologies, Inc. Electromagnetic interference immune tissue invasive system
US20020112729A1 (en) * 2001-02-21 2002-08-22 Spiration, Inc. Intra-bronchial obstructing device that controls biological interaction with the patient
US6733525B2 (en) * 2001-03-23 2004-05-11 Edwards Lifesciences Corporation Rolled minimally-invasive heart valves and methods of use
US20050055082A1 (en) * 2001-10-04 2005-03-10 Shmuel Ben Muvhar Flow reducing implant
US7211107B2 (en) * 2001-05-07 2007-05-01 Rafael Medical Technologies, Inc. Intravascular platforms and associated devices
FR2826863B1 (en) 2001-07-04 2003-09-26 Jacques Seguin An assembly for the introduction of a prosthetic valve in a body conduit
FR2828091B1 (en) * 2001-07-31 2003-11-21 Seguin Jacques An assembly for the introduction of a prosthetic valve in a body conduit
FR2828263B1 (en) * 2001-08-03 2007-05-11 Philipp Bonhoeffer The implantation device of an implant and method of implantation of the device
US20030050648A1 (en) * 2001-09-11 2003-03-13 Spiration, Inc. Removable lung reduction devices, systems, and methods
EP1516600B1 (en) * 2001-09-18 2007-03-14 Abbott Laboratories Vascular Enterprises Limited Stent
WO2004030568A3 (en) * 2002-10-01 2004-09-30 Ample Medical Inc Device and method for repairing a native heart valve leaflet
CA2462254A1 (en) * 2001-10-01 2003-04-10 Am Discovery, Incorporated Devices for treating atrial fibrilation
EP1562522B1 (en) * 2002-10-01 2008-12-31 Ample Medical, Inc. Devices and systems for reshaping a heart valve annulus
JP4446739B2 (en) * 2001-10-11 2010-04-07 パルモンクス・コーポレイションPulmonx Corporation Using bronchial flow control device and the device
US6592594B2 (en) * 2001-10-25 2003-07-15 Spiration, Inc. Bronchial obstruction device deployment system and method
US8308797B2 (en) 2002-01-04 2012-11-13 Colibri Heart Valve, LLC Percutaneously implantable replacement heart valve device and method of making same
US20060235432A1 (en) * 2002-02-21 2006-10-19 Devore Lauri J Intra-bronchial obstructing device that controls biological interaction with the patient
US6929637B2 (en) * 2002-02-21 2005-08-16 Spiration, Inc. Device and method for intra-bronchial provision of a therapeutic agent
US20030181922A1 (en) 2002-03-20 2003-09-25 Spiration, Inc. Removable anchored lung volume reduction devices and methods
US6752828B2 (en) 2002-04-03 2004-06-22 Scimed Life Systems, Inc. Artificial valve
US8721713B2 (en) * 2002-04-23 2014-05-13 Medtronic, Inc. System for implanting a replacement valve
WO2003094795A1 (en) 2002-05-10 2003-11-20 Cordis Corporation Method of making a medical device having a thin wall tubular membrane over a structural frame
US7270675B2 (en) * 2002-05-10 2007-09-18 Cordis Corporation Method of forming a tubular membrane on a structural frame
US7485141B2 (en) * 2002-05-10 2009-02-03 Cordis Corporation Method of placing a tubular membrane on a structural frame
US7351256B2 (en) 2002-05-10 2008-04-01 Cordis Corporation Frame based unidirectional flow prosthetic implant
US20030216769A1 (en) * 2002-05-17 2003-11-20 Dillard David H. Removable anchored lung volume reduction devices and methods
US8348963B2 (en) * 2002-07-03 2013-01-08 Hlt, Inc. Leaflet reinforcement for regurgitant valves
US7959674B2 (en) * 2002-07-16 2011-06-14 Medtronic, Inc. Suture locking assembly and method of use
DE60323502D1 (en) 2002-07-26 2008-10-23 Emphasys Medical Inc Bronchial flow device with a membrane seal
EP1592367B1 (en) * 2002-08-28 2016-04-13 HLT, Inc. Method and device for treating diseased valve
EP1551274B1 (en) * 2002-09-23 2014-12-24 Medtronic 3F Therapeutics, Inc. Prosthetic mitral valve
US7814912B2 (en) 2002-11-27 2010-10-19 Pulmonx Corporation Delivery methods and devices for implantable bronchial isolation devices
US7717115B2 (en) * 2002-11-27 2010-05-18 Pulmonx Corporation Delivery methods and devices for implantable bronchial isolation devices
US8551162B2 (en) 2002-12-20 2013-10-08 Medtronic, Inc. Biologically implantable prosthesis
US6945957B2 (en) * 2002-12-30 2005-09-20 Scimed Life Systems, Inc. Valve treatment catheter and methods
CA2515843A1 (en) * 2003-02-19 2004-09-02 Palomar Medical Technologies, Inc. Method and apparatus for treating pseudofolliculitis barbae
US8157810B2 (en) * 2003-02-26 2012-04-17 Cook Medical Technologies Llc Prosthesis adapted for placement under external imaging
CN100558320C (en) * 2003-03-19 2009-11-11 先进生物假体表面有限公司 Endoluminal stent having mid-interconnecting members
US20050107871A1 (en) * 2003-03-30 2005-05-19 Fidel Realyvasquez Apparatus and methods for valve repair
US7100616B2 (en) * 2003-04-08 2006-09-05 Spiration, Inc. Bronchoscopic lung volume reduction method
US7670366B2 (en) * 2003-04-08 2010-03-02 Cook Incorporated Intraluminal support device with graft
US7530995B2 (en) * 2003-04-17 2009-05-12 3F Therapeutics, Inc. Device for reduction of pressure effects of cardiac tricuspid valve regurgitation
US7159593B2 (en) * 2003-04-17 2007-01-09 3F Therapeutics, Inc. Methods for reduction of pressure effects of cardiac tricuspid valve regurgitation
US7175656B2 (en) * 2003-04-18 2007-02-13 Alexander Khairkhahan Percutaneous transcatheter heart valve replacement
US7676600B2 (en) * 2003-04-23 2010-03-09 Dot Hill Systems Corporation Network, storage appliance, and method for externalizing an internal I/O link between a server and a storage controller integrated within the storage appliance chassis
JP4940388B2 (en) 2003-04-24 2012-05-30 クック メディカル テクノロジーズ エルエルシーCook Medical Technologies Llc Prosthetic valve proteinase with improved hydrodynamic characteristics - Ze
US7658759B2 (en) * 2003-04-24 2010-02-09 Cook Incorporated Intralumenally implantable frames
US7717952B2 (en) * 2003-04-24 2010-05-18 Cook Incorporated Artificial prostheses with preferred geometries
US7625399B2 (en) * 2003-04-24 2009-12-01 Cook Incorporated Intralumenally-implantable frames
US6949929B2 (en) * 2003-06-24 2005-09-27 Biophan Technologies, Inc. Magnetic resonance imaging interference immune device
US7839146B2 (en) * 2003-06-24 2010-11-23 Medtronic, Inc. Magnetic resonance imaging interference immune device
US7388378B2 (en) * 2003-06-24 2008-06-17 Medtronic, Inc. Magnetic resonance imaging interference immune device
DE10334868B4 (en) 2003-07-29 2013-10-17 Pfm Medical Ag The implantable device as an organ valve replacement, its manufacturing method and the substrate and diaphragm element therefor
US7533671B2 (en) * 2003-08-08 2009-05-19 Spiration, Inc. Bronchoscopic repair of air leaks in a lung
US20050050042A1 (en) * 2003-08-20 2005-03-03 Marvin Elder Natural language database querying
US8021421B2 (en) 2003-08-22 2011-09-20 Medtronic, Inc. Prosthesis heart valve fixturing device
US20050049684A1 (en) * 2003-08-25 2005-03-03 Biophan Technologies, Inc. Electromagnetic radiation transparent device and method of making thereof
US20050288751A1 (en) * 2003-08-25 2005-12-29 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
US20050288755A1 (en) * 2003-08-25 2005-12-29 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
US20050288756A1 (en) * 2003-08-25 2005-12-29 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
US20050288754A1 (en) * 2003-08-25 2005-12-29 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
US20050283214A1 (en) * 2003-08-25 2005-12-22 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
US20050288753A1 (en) * 2003-08-25 2005-12-29 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
US20050283167A1 (en) * 2003-08-25 2005-12-22 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
US20050283213A1 (en) * 2003-08-25 2005-12-22 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
US8868212B2 (en) * 2003-08-25 2014-10-21 Medtronic, Inc. Medical device with an electrically conductive anti-antenna member
US20050288752A1 (en) * 2003-08-25 2005-12-29 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
US20050049692A1 (en) * 2003-09-02 2005-03-03 Numamoto Michael J. Medical device for reduction of pressure effects of cardiac tricuspid valve regurgitation
DE10342757A1 (en) * 2003-09-16 2005-04-07 Campus Gmbh & Co. Kg Stent terminated Verankerungselemeneten
US20060259137A1 (en) * 2003-10-06 2006-11-16 Jason Artof Minimally invasive valve replacement system
US9579194B2 (en) * 2003-10-06 2017-02-28 Medtronic ATS Medical, Inc. Anchoring structure with concave landing zone
US20050075720A1 (en) * 2003-10-06 2005-04-07 Nguyen Tuoc Tan Minimally invasive valve replacement system
US7556647B2 (en) * 2003-10-08 2009-07-07 Arbor Surgical Technologies, Inc. Attachment device and methods of using the same
US7070616B2 (en) * 2003-10-31 2006-07-04 Cordis Corporation Implantable valvular prosthesis
US7347869B2 (en) 2003-10-31 2008-03-25 Cordis Corporation Implantable valvular prosthesis
US7901770B2 (en) * 2003-11-04 2011-03-08 Boston Scientific Scimed, Inc. Embolic compositions
US7186265B2 (en) * 2003-12-10 2007-03-06 Medtronic, Inc. Prosthetic cardiac valves and systems and methods for implanting thereof
US8128681B2 (en) 2003-12-19 2012-03-06 Boston Scientific Scimed, Inc. Venous valve apparatus, system, and method
US7854761B2 (en) * 2003-12-19 2010-12-21 Boston Scientific Scimed, Inc. Methods for venous valve replacement with a catheter
US7261732B2 (en) 2003-12-22 2007-08-28 Henri Justino Stent mounted valve
US9005273B2 (en) * 2003-12-23 2015-04-14 Sadra Medical, Inc. Assessing the location and performance of replacement heart valves
US20050137696A1 (en) * 2003-12-23 2005-06-23 Sadra Medical Apparatus and methods for protecting against embolization during endovascular heart valve replacement
US20050137064A1 (en) * 2003-12-23 2005-06-23 Stephen Nothnagle Hand weights with finger support
US8840663B2 (en) 2003-12-23 2014-09-23 Sadra Medical, Inc. Repositionable heart valve method
US7824442B2 (en) 2003-12-23 2010-11-02 Sadra Medical, Inc. Methods and apparatus for endovascularly replacing a heart valve
US20050137691A1 (en) * 2003-12-23 2005-06-23 Sadra Medical Two piece heart valve and anchor
US20050137686A1 (en) * 2003-12-23 2005-06-23 Sadra Medical, A Delaware Corporation Externally expandable heart valve anchor and method
US7381219B2 (en) * 2003-12-23 2008-06-03 Sadra Medical, Inc. Low profile heart valve and delivery system
US7959666B2 (en) * 2003-12-23 2011-06-14 Sadra Medical, Inc. Methods and apparatus for endovascularly replacing a heart valve
US8052749B2 (en) * 2003-12-23 2011-11-08 Sadra Medical, Inc. Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements
US8579962B2 (en) * 2003-12-23 2013-11-12 Sadra Medical, Inc. Methods and apparatus for performing valvuloplasty
US8182528B2 (en) * 2003-12-23 2012-05-22 Sadra Medical, Inc. Locking heart valve anchor
US7748389B2 (en) * 2003-12-23 2010-07-06 Sadra Medical, Inc. Leaflet engagement elements and methods for use thereof
US8603160B2 (en) 2003-12-23 2013-12-10 Sadra Medical, Inc. Method of using a retrievable heart valve anchor with a sheath
US8343213B2 (en) 2003-12-23 2013-01-01 Sadra Medical, Inc. Leaflet engagement elements and methods for use thereof
US7329279B2 (en) * 2003-12-23 2008-02-12 Sadra Medical, Inc. Methods and apparatus for endovascularly replacing a patient's heart valve
US7445631B2 (en) 2003-12-23 2008-11-04 Sadra Medical, Inc. Methods and apparatus for endovascularly replacing a patient's heart valve
EP2529696B1 (en) * 2003-12-23 2014-01-29 Sadra Medical, Inc. Repositionable heart valve
US7824443B2 (en) 2003-12-23 2010-11-02 Sadra Medical, Inc. Medical implant delivery and deployment tool
US9526609B2 (en) * 2003-12-23 2016-12-27 Boston Scientific Scimed, Inc. Methods and apparatus for endovascularly replacing a patient's heart valve
US20050137687A1 (en) * 2003-12-23 2005-06-23 Sadra Medical Heart valve anchor and method
US20050137694A1 (en) 2003-12-23 2005-06-23 Haug Ulrich R. Methods and apparatus for endovascularly replacing a patient's heart valve
US8337545B2 (en) 2004-02-09 2012-12-25 Cook Medical Technologies Llc Woven implantable device
US8876791B2 (en) 2005-02-25 2014-11-04 Pulmonx Corporation Collateral pathway treatment using agent entrained by aspiration flow current
US8206684B2 (en) 2004-02-27 2012-06-26 Pulmonx Corporation Methods and devices for blocking flow through collateral pathways in the lung
US8109996B2 (en) 2004-03-03 2012-02-07 Sorin Biomedica Cardio, S.R.L. Minimally-invasive cardiac-valve prosthesis
EP1729685B1 (en) * 2004-03-31 2015-07-15 Cook Medical Technologies LLC Endoluminal graft with a prosthetic valve
WO2005096988A1 (en) * 2004-04-01 2005-10-20 Cook Incorporated A device for retracting the walls of a body vessel with remodelable material
EP1737390A1 (en) * 2004-04-08 2007-01-03 Cook Incorporated Implantable medical device with optimized shape
US7641686B2 (en) 2004-04-23 2010-01-05 Direct Flow Medical, Inc. Percutaneous heart valve with stentless support
WO2005102015A3 (en) 2004-04-23 2007-04-19 3F Therapeutics Inc Implantable prosthetic valve
US8012201B2 (en) * 2004-05-05 2011-09-06 Direct Flow Medical, Inc. Translumenally implantable heart valve with multiple chamber formed in place support
US20060122692A1 (en) * 2004-05-10 2006-06-08 Ran Gilad Stent valve and method of using same
US20060122686A1 (en) * 2004-05-10 2006-06-08 Ran Gilad Stent and method of manufacturing same
US20060122693A1 (en) * 2004-05-10 2006-06-08 Youssef Biadillah Stent valve and method of manufacturing same
US20060095115A1 (en) * 2004-05-10 2006-05-04 Youssef Bladillah Stent and method of manufacturing same
US7780725B2 (en) 2004-06-16 2010-08-24 Sadra Medical, Inc. Everting heart valve
WO2006023700A3 (en) * 2004-08-20 2007-04-19 Biophan Technologies Inc Magnetic resonance imaging interference immune device
US7566343B2 (en) 2004-09-02 2009-07-28 Boston Scientific Scimed, Inc. Cardiac valve, system, and method
US20060052867A1 (en) 2004-09-07 2006-03-09 Medtronic, Inc Replacement prosthetic heart valve, system and method of implant
WO2006041505A1 (en) * 2004-10-02 2006-04-20 Huber Christoph Hans Methods and devices for repair or replacement of heart valves or adjacent tissue without the need for full cardiopulmonary support
KR20070094888A (en) * 2004-11-19 2007-09-27 메드트로닉 인코포레이티드 Method and apparatus for treatment of cardiac valves
US7771472B2 (en) 2004-11-19 2010-08-10 Pulmonx Corporation Bronchial flow control devices and methods of use
US8562672B2 (en) 2004-11-19 2013-10-22 Medtronic, Inc. Apparatus for treatment of cardiac valves and method of its manufacture
US7766973B2 (en) * 2005-01-19 2010-08-03 Gi Dynamics, Inc. Eversion resistant sleeves
US7771382B2 (en) * 2005-01-19 2010-08-10 Gi Dynamics, Inc. Resistive anti-obesity devices
EP1838242A2 (en) * 2005-01-21 2007-10-03 Gen 4, LLC Modular stent graft employing bifurcated graft and leg locking stent elements
US20060173490A1 (en) * 2005-02-01 2006-08-03 Boston Scientific Scimed, Inc. Filter system and method
US7854755B2 (en) * 2005-02-01 2010-12-21 Boston Scientific Scimed, Inc. Vascular catheter, system, and method
US7878966B2 (en) * 2005-02-04 2011-02-01 Boston Scientific Scimed, Inc. Ventricular assist and support device
US7780722B2 (en) * 2005-02-07 2010-08-24 Boston Scientific Scimed, Inc. Venous valve apparatus, system, and method
US7670368B2 (en) * 2005-02-07 2010-03-02 Boston Scientific Scimed, Inc. Venous valve apparatus, system, and method
EP2319458B1 (en) * 2005-02-10 2013-04-24 Sorin Group Italia S.r.l. Cardiac-valve prosthesis
US7867274B2 (en) * 2005-02-23 2011-01-11 Boston Scientific Scimed, Inc. Valve apparatus, system and method
US8197534B2 (en) 2005-03-31 2012-06-12 Cook Medical Technologies Llc Valve device with inflatable chamber
US7513909B2 (en) 2005-04-08 2009-04-07 Arbor Surgical Technologies, Inc. Two-piece prosthetic valves with snap-in connection and methods for use
US7722666B2 (en) * 2005-04-15 2010-05-25 Boston Scientific Scimed, Inc. Valve apparatus, system and method
US7962208B2 (en) 2005-04-25 2011-06-14 Cardiac Pacemakers, Inc. Method and apparatus for pacing during revascularization
US7914569B2 (en) 2005-05-13 2011-03-29 Medtronics Corevalve Llc Heart valve prosthesis and methods of manufacture and use
US20070010734A1 (en) * 2005-05-19 2007-01-11 Biophan Technologies, Inc. Electromagnetic resonant circuit sleeve for implantable medical device
WO2006130505A3 (en) 2005-05-27 2007-06-28 Arbor Surgical Technologies Gasket with collar for prosthetic heart valves and methods for using them
CA2610669A1 (en) * 2005-06-07 2006-12-14 Direct Flow Medical, Inc. Stentless aortic valve replacement with high radial strength
US8012198B2 (en) 2005-06-10 2011-09-06 Boston Scientific Scimed, Inc. Venous valve, system, and method
US20070010781A1 (en) * 2005-06-27 2007-01-11 Venkataramana Vijay Implantable aorto-coronary sinus shunt for myocardial revascularization
US20070010780A1 (en) * 2005-06-27 2007-01-11 Venkataramana Vijay Methods of implanting an aorto-coronary sinus shunt for myocardial revascularization
WO2007009117A1 (en) * 2005-07-13 2007-01-18 Arbor Surgical Technologies, Inc. Two-piece percutaneous prosthetic heart valves and methods for making and using them
US20070027460A1 (en) * 2005-07-27 2007-02-01 Cook Incorporated Implantable remodelable materials comprising magnetic material
US20080269879A1 (en) * 2005-07-27 2008-10-30 Rahul Dilip Sathe Implantable Prosthetic Vascular Valve
WO2007016251A3 (en) * 2005-07-28 2008-04-03 Cook Inc Implantable thromboresistant valve
EP1919398B1 (en) * 2005-07-29 2014-03-05 Cook Medical Technologies LLC Elliptical implantable device
US20070038295A1 (en) * 2005-08-12 2007-02-15 Cook Incorporated Artificial valve prosthesis having a ring frame
US7712606B2 (en) 2005-09-13 2010-05-11 Sadra Medical, Inc. Two-part package for medical implant
US7569071B2 (en) 2005-09-21 2009-08-04 Boston Scientific Scimed, Inc. Venous valve, system, and method with sinus pocket
EP1945142B1 (en) 2005-09-26 2013-12-25 Medtronic, Inc. Prosthetic cardiac and venous valves
US7503928B2 (en) * 2005-10-21 2009-03-17 Cook Biotech Incorporated Artificial valve with center leaflet attachment
US8287584B2 (en) * 2005-11-14 2012-10-16 Sadra Medical, Inc. Medical implant deployment tool
US9078781B2 (en) * 2006-01-11 2015-07-14 Medtronic, Inc. Sterile cover for compressible stents used in percutaneous device delivery systems
US7799038B2 (en) * 2006-01-20 2010-09-21 Boston Scientific Scimed, Inc. Translumenal apparatus, system, and method
US7967857B2 (en) 2006-01-27 2011-06-28 Medtronic, Inc. Gasket with spring collar for prosthetic heart valves and methods for making and using them
EP1988851A2 (en) 2006-02-14 2008-11-12 Sadra Medical, Inc. Systems and methods for delivering a medical implant
WO2007106755A1 (en) * 2006-03-10 2007-09-20 Arbor Surgical Technologies, Inc. Valve introducers and methods for making and using them
US8075615B2 (en) * 2006-03-28 2011-12-13 Medtronic, Inc. Prosthetic cardiac valve formed from pericardium material and methods of making same
US7691151B2 (en) * 2006-03-31 2010-04-06 Spiration, Inc. Articulable Anchor
US7524331B2 (en) * 2006-04-06 2009-04-28 Medtronic Vascular, Inc. Catheter delivered valve having a barrier to provide an enhanced seal
US7740655B2 (en) * 2006-04-06 2010-06-22 Medtronic Vascular, Inc. Reinforced surgical conduit for implantation of a stented valve therein
US20070239269A1 (en) * 2006-04-07 2007-10-11 Medtronic Vascular, Inc. Stented Valve Having Dull Struts
US20070239271A1 (en) * 2006-04-10 2007-10-11 Than Nguyen Systems and methods for loading a prosthesis onto a minimally invasive delivery system
US20070244545A1 (en) * 2006-04-14 2007-10-18 Medtronic Vascular, Inc. Prosthetic Conduit With Radiopaque Symmetry Indicators
US20070244544A1 (en) * 2006-04-14 2007-10-18 Medtronic Vascular, Inc. Seal for Enhanced Stented Valve Fixation
US20070244546A1 (en) * 2006-04-18 2007-10-18 Medtronic Vascular, Inc. Stent Foundation for Placement of a Stented Valve
WO2007130881A3 (en) * 2006-04-29 2008-01-31 Arbor Surgical Technologies Multiple component prosthetic heart valve assemblies and apparatus and methods for delivering them
US7811316B2 (en) 2006-05-25 2010-10-12 Deep Vein Medical, Inc. Device for regulating blood flow
US8092517B2 (en) * 2006-05-25 2012-01-10 Deep Vein Medical, Inc. Device for regulating blood flow
WO2007142935B1 (en) * 2006-05-30 2008-02-14 Cook Inc Artificial valve prosthesis
US7828916B2 (en) * 2006-07-20 2010-11-09 Abbott Cardiovascular Systems Inc. Methods of crimping expandable medical devices
US20080072914A1 (en) * 2006-08-25 2008-03-27 Hendricksen Michael J Bronchial Isolation Devices for Placement in Short Lumens
US8834564B2 (en) 2006-09-19 2014-09-16 Medtronic, Inc. Sinus-engaging valve fixation member
US8876895B2 (en) 2006-09-19 2014-11-04 Medtronic Ventor Technologies Ltd. Valve fixation member having engagement arms
EP2083901B1 (en) 2006-10-16 2017-12-27 Medtronic Ventor Technologies Ltd. Transapical delivery system with ventriculo-arterial overflow bypass
US7935144B2 (en) * 2006-10-19 2011-05-03 Direct Flow Medical, Inc. Profile reduction of valve implant
US8133213B2 (en) * 2006-10-19 2012-03-13 Direct Flow Medical, Inc. Catheter guidance through a calcified aortic valve
CA2671754C (en) * 2006-12-06 2015-08-18 Medtronic Corevalve Llc System and method for transapical delivery of an annulus anchored self-expanding valve
US8768486B2 (en) * 2006-12-11 2014-07-01 Medtronic, Inc. Medical leads with frequency independent magnetic resonance imaging protection
WO2008091493A1 (en) 2007-01-08 2008-07-31 California Institute Of Technology In-situ formation of a valve
ES2441801T3 (en) 2007-02-05 2014-02-06 Boston Scientific Limited Percutaneous valve and delivery system
WO2008097556A1 (en) * 2007-02-05 2008-08-14 Boston Scientific Limited Systems and methods for valve delivery
US20080262593A1 (en) * 2007-02-15 2008-10-23 Ryan Timothy R Multi-layered stents and methods of implanting
US8092522B2 (en) * 2007-02-15 2012-01-10 Cook Medical Technologies Llc Artificial valve prostheses with a free leaflet portion
EP2129332A1 (en) 2007-02-16 2009-12-09 Medtronic, Inc. Replacement prosthetic heart valves and methods of implantation
US8974514B2 (en) 2007-03-13 2015-03-10 Abbott Cardiovascular Systems Inc. Intravascular stent with integrated link and ring strut
FR2915087A1 (en) 2007-04-20 2008-10-24 Corevalve Inc Implant treatment of a heart valve, particularly a mitral valve implant inculant material and equipment for setting up of this implant.
US8500787B2 (en) * 2007-05-15 2013-08-06 Abbott Laboratories Radiopaque markers and medical devices comprising binary alloys of titanium
US8500786B2 (en) * 2007-05-15 2013-08-06 Abbott Laboratories Radiopaque markers comprising binary alloys of titanium
US8128679B2 (en) * 2007-05-23 2012-03-06 Abbott Laboratories Vascular Enterprises Limited Flexible stent with torque-absorbing connectors
US8016874B2 (en) * 2007-05-23 2011-09-13 Abbott Laboratories Vascular Enterprises Limited Flexible stent with elevated scaffolding properties
US8828079B2 (en) * 2007-07-26 2014-09-09 Boston Scientific Scimed, Inc. Circulatory valve, system and method
US8747458B2 (en) 2007-08-20 2014-06-10 Medtronic Ventor Technologies Ltd. Stent loading tool and method for use thereof
CA2697364C (en) * 2007-08-23 2017-10-17 Direct Flow Medical, Inc. Translumenally implantable heart valve with formed in place support
US8834551B2 (en) 2007-08-31 2014-09-16 Rex Medical, L.P. Vascular device with valve for approximating vessel wall
US20090138079A1 (en) * 2007-10-10 2009-05-28 Vector Technologies Ltd. Prosthetic heart valve for transfemoral delivery
US8043301B2 (en) * 2007-10-12 2011-10-25 Spiration, Inc. Valve loader method, system, and apparatus
CN101868199B (en) 2007-10-12 2016-04-06 斯波瑞申有限公司 Valve loader methods, systems, and devices
US9848981B2 (en) * 2007-10-12 2017-12-26 Mayo Foundation For Medical Education And Research Expandable valve prosthesis with sealing mechanism
US7846199B2 (en) * 2007-11-19 2010-12-07 Cook Incorporated Remodelable prosthetic valve
US8920488B2 (en) * 2007-12-20 2014-12-30 Abbott Laboratories Vascular Enterprises Limited Endoprosthesis having a stable architecture
US7850726B2 (en) * 2007-12-20 2010-12-14 Abbott Laboratories Vascular Enterprises Limited Endoprosthesis having struts linked by foot extensions
US8337544B2 (en) * 2007-12-20 2012-12-25 Abbott Laboratories Vascular Enterprises Limited Endoprosthesis having flexible connectors
US7892276B2 (en) 2007-12-21 2011-02-22 Boston Scientific Scimed, Inc. Valve with delayed leaflet deployment
US20090171456A1 (en) * 2007-12-28 2009-07-02 Kveen Graig L Percutaneous heart valve, system, and method
US8211165B1 (en) 2008-01-08 2012-07-03 Cook Medical Technologies Llc Implantable device for placement in a vessel having a variable size
US20090287290A1 (en) * 2008-01-24 2009-11-19 Medtronic, Inc. Delivery Systems and Methods of Implantation for Prosthetic Heart Valves
US9149358B2 (en) * 2008-01-24 2015-10-06 Medtronic, Inc. Delivery systems for prosthetic heart valves
US9393115B2 (en) * 2008-01-24 2016-07-19 Medtronic, Inc. Delivery systems and methods of implantation for prosthetic heart valves
US8157853B2 (en) * 2008-01-24 2012-04-17 Medtronic, Inc. Delivery systems and methods of implantation for prosthetic heart valves
EP2254513B1 (en) * 2008-01-24 2015-10-28 Medtronic, Inc. Stents for prosthetic heart valves
WO2009094501A1 (en) * 2008-01-24 2009-07-30 Medtronic, Inc. Markers for prosthetic heart valves
CA2714062A1 (en) 2008-01-24 2009-07-30 Medtronic, Inc. Stents for prosthetic heart valves
EP2244668A1 (en) 2008-01-25 2010-11-03 JenaValve Technology Inc. Medical apparatus for the therapeutic treatment of an insufficient cardiac valve
CN101951858B (en) * 2008-02-25 2015-02-11 麦德托尼克瓦斯科尔勒公司 Infundibular reducer devices
US20090264989A1 (en) * 2008-02-28 2009-10-22 Philipp Bonhoeffer Prosthetic heart valve systems
US8313525B2 (en) 2008-03-18 2012-11-20 Medtronic Ventor Technologies, Ltd. Valve suturing and implantation procedures
ES2366266T3 (en) * 2008-03-27 2011-10-18 Ab Medica S.P.A. Valve prosthesis for implantation in body channels.
EP2282684B1 (en) * 2008-04-03 2016-06-15 Cook Medical Technologies LLC Occlusion device
US8430927B2 (en) * 2008-04-08 2013-04-30 Medtronic, Inc. Multiple orifice implantable heart valve and methods of implantation
US8696743B2 (en) * 2008-04-23 2014-04-15 Medtronic, Inc. Tissue attachment devices and methods for prosthetic heart valves
US8312825B2 (en) * 2008-04-23 2012-11-20 Medtronic, Inc. Methods and apparatuses for assembly of a pericardial prosthetic heart valve
US8840661B2 (en) * 2008-05-16 2014-09-23 Sorin Group Italia S.R.L. Atraumatic prosthetic heart valve prosthesis
ES2645920T3 (en) * 2008-06-06 2017-12-11 Edwards Lifesciences Corporation Transcatheter heart valve low profile
US8998981B2 (en) * 2008-09-15 2015-04-07 Medtronic, Inc. Prosthetic heart valve having identifiers for aiding in radiographic positioning
US8721714B2 (en) * 2008-09-17 2014-05-13 Medtronic Corevalve Llc Delivery system for deployment of medical devices
ES2627860T3 (en) * 2008-10-10 2017-07-31 Boston Scientific Scimed, Inc. to place medical devices medical devices and installation systems
US8137398B2 (en) * 2008-10-13 2012-03-20 Medtronic Ventor Technologies Ltd Prosthetic valve having tapered tip when compressed for delivery
US8986361B2 (en) 2008-10-17 2015-03-24 Medtronic Corevalve, Inc. Delivery system for deployment of medical devices
US8834563B2 (en) 2008-12-23 2014-09-16 Sorin Group Italia S.R.L. Expandable prosthetic valve having anchoring appendages
EP2628465A1 (en) 2009-04-27 2013-08-21 Sorin Group Italia S.r.l. Prosthetic vascular conduit
WO2011002996A3 (en) * 2009-07-02 2011-06-30 The Cleveland Clinic Foundation Apparatus and method for replacing a diseased cardiac valve
US8597716B2 (en) * 2009-06-23 2013-12-03 Abbott Cardiovascular Systems Inc. Methods to increase fracture resistance of a drug-eluting medical device
JP4852631B2 (en) * 2009-06-28 2012-01-11 株式会社沖データ Communication device and connection control method thereof
FR2947716B1 (en) * 2009-07-10 2011-09-02 Cormove Implant prosthetic improves
US8475522B2 (en) 2009-07-14 2013-07-02 Edwards Lifesciences Corporation Transapical delivery system for heart valves
US8808369B2 (en) * 2009-10-05 2014-08-19 Mayo Foundation For Medical Education And Research Minimally invasive aortic valve replacement
US8377115B2 (en) * 2009-11-16 2013-02-19 Medtronic Vascular, Inc. Implantable valve prosthesis for treating venous valve insufficiency
US9226826B2 (en) * 2010-02-24 2016-01-05 Medtronic, Inc. Transcatheter valve structure and methods for valve delivery
US8652204B2 (en) 2010-04-01 2014-02-18 Medtronic, Inc. Transcatheter valve with torsion spring fixation and related systems and methods
WO2011130579A1 (en) 2010-04-14 2011-10-20 Abbott Cardiovascular Systems Inc. Intraluminal scaffold and method of making and using same
EP2387972B1 (en) 2010-05-21 2013-12-25 Sorin Group Italia S.r.l. A support device for valve prostheses and corresponding kit
EP2585157A4 (en) 2010-06-28 2017-02-08 Colibri Heart Valve Llc Method and apparatus for the endoluminal delivery of intravascular devices
WO2012004679A3 (en) 2010-07-09 2012-08-23 Highlife Sas Transcatheter atrio-ventricular valve prosthesis
US8556085B2 (en) 2010-11-08 2013-10-15 Stuart Bogle Anti-viral device
US9737400B2 (en) 2010-12-14 2017-08-22 Colibri Heart Valve Llc Percutaneously deliverable heart valve including folded membrane cusps with integral leaflets
US8845717B2 (en) 2011-01-28 2014-09-30 Middle Park Medical, Inc. Coaptation enhancement implant, system, and method
US8888843B2 (en) 2011-01-28 2014-11-18 Middle Peak Medical, Inc. Device, system, and method for transcatheter treatment of valve regurgitation
EP2486894A1 (en) 2011-02-14 2012-08-15 Sorin Biomedica Cardio S.r.l. Sutureless anchoring device for cardiac valve prostheses
ES2641902T3 (en) 2011-02-14 2017-11-14 Sorin Group Italia S.R.L. Anchoring device for sutureless heart valve prostheses
WO2012127309A4 (en) 2011-03-21 2013-01-31 Montorfano Matteo Disk-based valve apparatus and method for the treatment of valve dysfunction
US8795241B2 (en) 2011-05-13 2014-08-05 Spiration, Inc. Deployment catheter
JP2014527425A (en) 2011-07-12 2014-10-16 ボストン サイエンティフィック サイムド,インコーポレイテッドBoston Scientific Scimed,Inc. Coupling system for medical equipment
WO2013019756A3 (en) * 2011-07-29 2014-05-08 Carnegie Mellon University Artificial valved conduits for cardiac reconstructive procedures and methods for their production
US9668859B2 (en) 2011-08-05 2017-06-06 California Institute Of Technology Percutaneous heart valve delivery systems
WO2013044267A1 (en) 2011-09-23 2013-03-28 Pulmonx, Inc. Implant loading device and system
US8986368B2 (en) * 2011-10-31 2015-03-24 Merit Medical Systems, Inc. Esophageal stent with valve
US9131926B2 (en) 2011-11-10 2015-09-15 Boston Scientific Scimed, Inc. Direct connect flush system
US8940014B2 (en) 2011-11-15 2015-01-27 Boston Scientific Scimed, Inc. Bond between components of a medical device
US8951243B2 (en) 2011-12-03 2015-02-10 Boston Scientific Scimed, Inc. Medical device handle
CN104114127B (en) 2011-12-09 2017-09-05 爱德华兹生命科学公司 With improved commissure support of artificial heart valves
US9510945B2 (en) 2011-12-20 2016-12-06 Boston Scientific Scimed Inc. Medical device handle
US9277993B2 (en) 2011-12-20 2016-03-08 Boston Scientific Scimed, Inc. Medical device delivery systems
EP2842517A1 (en) 2011-12-29 2015-03-04 Sorin Group Italia S.r.l. A kit for implanting prosthetic vascular conduits
CN107031037A (en) * 2012-01-24 2017-08-11 史密夫和内修有限公司 Porous structure and methods of making same
US9168122B2 (en) 2012-04-26 2015-10-27 Rex Medical, L.P. Vascular device and method for valve leaflet apposition
WO2013184630A1 (en) 2012-06-05 2013-12-12 Merit Medical Systems, Inc. Esophageal stent
US9168129B2 (en) 2013-02-12 2015-10-27 Edwards Lifesciences Corporation Artificial heart valve with scalloped frame design
WO2014138006A1 (en) 2013-03-05 2014-09-12 Merit Medical Systems, Inc. Reinforced valve
EP2967945A4 (en) 2013-03-15 2016-11-09 California Inst Of Techn Handle mechanism and functionality for repositioning and retrieval of transcatheter heart valves
US9629718B2 (en) 2013-05-03 2017-04-25 Medtronic, Inc. Valve delivery tool
WO2015002832A1 (en) * 2013-07-01 2015-01-08 St. Jude Medical, Cardiology Division, Inc. Hybrid orientation pravalvular sealing stent
US8870948B1 (en) 2013-07-17 2014-10-28 Cephea Valve Technologies, Inc. System and method for cardiac valve repair and replacement
CN103550015B (en) * 2013-11-01 2015-07-01 金仕生物科技(常熟)有限公司 Heart valve prosthesis valve frame and intervened heart valve prosthesis using valve frame
US9763779B2 (en) * 2014-03-11 2017-09-19 Highlife Sas Transcatheter valve prosthesis
US9668861B2 (en) 2014-03-15 2017-06-06 Rex Medical, L.P. Vascular device for treating venous valve insufficiency
EP2921140A1 (en) * 2014-03-18 2015-09-23 St. Jude Medical, Cardiology Division, Inc. Percutaneous valve anchoring for a prosthetic aortic valve
US20160158000A1 (en) 2014-12-09 2016-06-09 Juan F. Granada Replacement cardiac valves and methods of use and manufacture
US9861477B2 (en) 2015-01-26 2018-01-09 Boston Scientific Scimed Inc. Prosthetic heart valve square leaflet-leaflet stitch
US9788942B2 (en) 2015-02-03 2017-10-17 Boston Scientific Scimed Inc. Prosthetic heart valve having tubular seal
US9592121B1 (en) 2015-11-06 2017-03-14 Middle Peak Medical, Inc. Device, system, and method for transcatheter treatment of valvular regurgitation
US20170156863A1 (en) * 2015-12-03 2017-06-08 Medtronic Vascular, Inc. Venous valve prostheses

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5855597A (en) * 1997-05-07 1999-01-05 Iowa-India Investments Co. Limited Stent valve and stent graft for percutaneous surgery
EP0928606A1 (en) * 1998-01-09 1999-07-14 Nitinol Development Corporation An intravascular stent having curved bridges for connecting adjacent hoops
WO2000047139A1 (en) * 1999-02-10 2000-08-17 Heartport, Inc. Methods and devices for implanting cardiac valves
WO2000047136A1 (en) * 1999-02-12 2000-08-17 Johns Hopkins University Venous valve implant bioprosthesis and endovascular treatment for venous insufficiency
WO2001049213A2 (en) * 1999-12-31 2001-07-12 Advanced Bio Prosthetic Surfaces, Ltd. Endoluminal cardiac and venous valve prostheses and methods of manufacture and delivery thereof
US20020032481A1 (en) * 2000-09-12 2002-03-14 Shlomo Gabbay Heart valve prosthesis and sutureless implantation of a heart valve prosthesis

Family Cites Families (20)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US325824A (en) * 1885-09-08 Cook foe gas
US5609626A (en) 1989-05-31 1997-03-11 Baxter International Inc. Stent devices and support/restrictor assemblies for use in conjunction with prosthetic vascular grafts
EP0474748B1 (en) 1989-05-31 1995-01-25 Baxter International Inc. Biological valvular prosthesis
DK124690D0 (en) * 1990-05-18 1990-05-18 Henning Rud Andersen Klapprotes for implantation in the body for replacement of the natural folding and catheter for use in the implantation of such a prosthesis flap
EP0520126A1 (en) 1991-06-25 1992-12-30 Sante Camilli Artificial venous value
US5662713A (en) 1991-10-09 1997-09-02 Boston Scientific Corporation Medical stents for body lumens exhibiting peristaltic motion
US5876445A (en) 1991-10-09 1999-03-02 Boston Scientific Corporation Medical stents for body lumens exhibiting peristaltic motion
US5332402A (en) 1992-05-12 1994-07-26 Teitelbaum George P Percutaneously-inserted cardiac valve
US5609627A (en) 1994-02-09 1997-03-11 Boston Scientific Technology, Inc. Method for delivering a bifurcated endoluminal prosthesis
WO1996013228A1 (en) 1994-10-27 1996-05-09 Schneider (Usa) Inc. Stent delivery device
JPH11513577A (en) 1995-10-13 1999-11-24 トランスバスキュラー インコーポレイテッド Apparatus for tissue between transluminal intervention, the system and method
US5747128A (en) 1996-01-29 1998-05-05 W. L. Gore & Associates, Inc. Radially supported polytetrafluoroethylene vascular graft
US6036687A (en) 1996-03-05 2000-03-14 Vnus Medical Technologies, Inc. Method and apparatus for treating venous insufficiency
US5855601A (en) 1996-06-21 1999-01-05 The Trustees Of Columbia University In The City Of New York Artificial heart valve and method and device for implanting the same
US6086610A (en) 1996-10-22 2000-07-11 Nitinol Devices & Components Composite self expanding stent device having a restraining element
US5957949A (en) 1997-05-01 1999-09-28 World Medical Manufacturing Corp. Percutaneous placement valve stent
US6245102B1 (en) * 1997-05-07 2001-06-12 Iowa-India Investments Company Ltd. Stent, stent graft and stent valve
US6254564B1 (en) * 1998-09-10 2001-07-03 Percardia, Inc. Left ventricular conduit with blood vessel graft
US6299637B1 (en) * 1999-08-20 2001-10-09 Samuel M. Shaolian Transluminally implantable venous valve
US6440164B1 (en) * 1999-10-21 2002-08-27 Scimed Life Systems, Inc. Implantable prosthetic valve

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5855597A (en) * 1997-05-07 1999-01-05 Iowa-India Investments Co. Limited Stent valve and stent graft for percutaneous surgery
EP0928606A1 (en) * 1998-01-09 1999-07-14 Nitinol Development Corporation An intravascular stent having curved bridges for connecting adjacent hoops
WO2000047139A1 (en) * 1999-02-10 2000-08-17 Heartport, Inc. Methods and devices for implanting cardiac valves
WO2000047136A1 (en) * 1999-02-12 2000-08-17 Johns Hopkins University Venous valve implant bioprosthesis and endovascular treatment for venous insufficiency
WO2001049213A2 (en) * 1999-12-31 2001-07-12 Advanced Bio Prosthetic Surfaces, Ltd. Endoluminal cardiac and venous valve prostheses and methods of manufacture and delivery thereof
US20020032481A1 (en) * 2000-09-12 2002-03-14 Shlomo Gabbay Heart valve prosthesis and sutureless implantation of a heart valve prosthesis

Cited By (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6935404B2 (en) 1998-01-09 2005-08-30 Thomas Duerig Intravascular device with improved radiopacity
EP1212991A3 (en) * 2000-12-07 2004-01-02 Cordis Corporation An intravascular device with improved radiopacity
US7377938B2 (en) 2001-07-19 2008-05-27 The Cleveland Clinic Foundation Prosthetic cardiac value and method for making same
US7547322B2 (en) 2001-07-19 2009-06-16 The Cleveland Clinic Foundation Prosthetic valve and method for making same
US9216082B2 (en) 2005-12-22 2015-12-22 Symetis Sa Stent-valves for valve replacement and associated methods and systems for surgery
US9839515B2 (en) 2005-12-22 2017-12-12 Symetis, SA Stent-valves for valve replacement and associated methods and systems for surgery
US9839513B2 (en) 2007-10-25 2017-12-12 Symetis Sa Stents, valved-stents and methods and systems for delivery thereof

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