US20060085066A1 - Body lumen closure - Google Patents
Body lumen closure Download PDFInfo
- Publication number
- US20060085066A1 US20060085066A1 US11/296,590 US29659005A US2006085066A1 US 20060085066 A1 US20060085066 A1 US 20060085066A1 US 29659005 A US29659005 A US 29659005A US 2006085066 A1 US2006085066 A1 US 2006085066A1
- Authority
- US
- United States
- Prior art keywords
- anchoring end
- closure device
- flexible
- strand
- expander
- Prior art date
- Legal status (The legal status 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 status listed.)
- Abandoned
Links
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/02—Prostheses implantable into the body
- A61F2/24—Heart 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; Valves implantable in the body
- A61F2/2442—Annuloplasty rings or inserts for correcting the valve shape; Implants for improving the function of a native heart valve
- A61F2/2445—Annuloplasty rings in direct contact with the valve annulus
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/064—Surgical staples, i.e. penetrating the tissue
- A61B17/0644—Surgical staples, i.e. penetrating the tissue penetrating the tissue, deformable to closed position
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/02—Prostheses implantable into the body
- A61F2/24—Heart 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; Valves implantable in the body
- A61F2/2475—Venous valves
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/068—Surgical staplers, e.g. containing multiple staples or clamps
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/064—Surgical staples, i.e. penetrating the tissue
- A61B2017/0649—Coils or spirals
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2220/00—Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2220/0008—Fixation appliances for connecting prostheses to the body
- A61F2220/0016—Fixation appliances for connecting prostheses to the body with sharp anchoring protrusions, e.g. barbs, pins, spikes
Definitions
- a venous valve functions to prevent retrograde flow of blood and allow only antegrade flow of blood to the heart.
- a healthy venous valve 12 is illustrated in a vessel 10 .
- the valve is bicuspid, with opposed cusps 14 .
- the cusps 14 are drawn together to prevent retrograde flow (arrow 16 ) of blood.
- FIG. 1B if the valve is incompetent, the cusps 14 do not seal properly and retrograde flow of blood occurs. Incompetence of a venous valve is thought to arise from at least the following two medical conditions: varicose veins and chronic venous insufficiency.
- the invention features an implantable medical closure device.
- the device includes a flexible strand defining an arcuate form.
- the strand is deformable upon implantation from a large cross-section condition to a small cross-section condition and has at least two anchoring portions disposed along the strand.
- the anchoring portions are configured to penetrate a wall of a body lumen such that when the strand is deformed to the small cross-section condition, the wall of the body lumen is disposed inwardly.
- the strand can also be deformable from a second small cross-section condition to the large cross-section condition, for example, the strand may be deformed to the second small cross-section condition to facilitate delivery of the strand to a treatment site, where it is then deformed to the large cross-section condition upon implantation.
- the strand can include free ends, which free ends can include the anchoring portions of the strand.
- the strand can define an arc, a helix or can include linear leg portions.
- the strand can be a filament-form or a band and may be corrugated.
- the strand can deform from the large cross-section condition to the small cross-section condition by, for example, elastic recovery forces or thermal shape-memory effect.
- the strand can be formed of metal, for example, nitinol.
- the anchoring portions of the strand can include, for example, a loop or a barb.
- the invention features a catheter system, which system includes a catheter for delivery into a lumen.
- the catheter includes an expander that can be operated between a small cross-section and a large cross-section.
- the catheter system also includes a closure device positioned about the expander.
- the closure device is a strand defining an arcuate form and including at least two anchoring portions configured to penetrate a wall of a body lumen.
- the closure device is deformable by the expander from a first small cross-section condition to a larger cross-section condition to dispose the closure device into engagement with the lumen wall.
- the closure device is further deformable to a second small cross-section condition, so that the wall of the body lumen is disposed inwardly.
- the expander can take any convenient form, including, for example, an inflatable balloon, a mechanical expander or a leveraging device.
- the mechanical expander can include a two-part axial member having a first inner part connected to a first coiled spring and a second outer part connected to a second coiled spring.
- the closure device is mounted on the first and second coiled springs, and the first inner part of the axial member is rotatable to expand the first coiled spring and the second outer part of the axial member is rotatable to expand the second coiled spring. Expansion of the first and second coiled springs expands the closure device.
- Each coiled spring can include a distal end configured to fit within a groove formed on either end of the closure device.
- the leveraging device can include a two-part axial member including a first outer part and a second inner part.
- a splayed cuff is connected to the distal end of the first outer part of the two-part axial member, and at least two flexible legs are connected to the distal end of the second inner part of the two-part axial member. The legs are flared outwardly to contact the distal end of the splayed cuff.
- the second inner part of the two-part axial member is moveable toward the splayed cuff such that the flexible legs and the splayed cuff expand radially.
- the closure device is positioned about the flexible legs and expansion of the flexible legs expands the closure device from a first small cross-section condition to a larger cross-section condition.
- the second inner part of the two-part axial member is also moveable away from the splayed cuff such that the flexible legs and the splayed cuff retract.
- the invention features a method of treating a body lumen.
- the method includes delivering a closure device into a lumen and positioning the strand about the lumen such that a portion of the strand penetrates the wall of the lumen.
- the method further includes deforming the strand to a smaller cross-section condition such that the wall of the lumen is disposed inwardly.
- the strand can be positioned about the lumen such that an end of the strand extends through the wall of the lumen.
- the strand can be disposed on a catheter, which catheter is then delivered into the lumen.
- the catheter can include an expansion member.
- Embodiments may have one or more of the following advantages. Closure of a body lumen can be achieved in a minimally invasive manner by delivery of a closure device to a treatment site using a catheter.
- the closure device may be partially installed within the lumen but configured to minimize profile and thus reduce impedance to the flow of body fluids through the lumen.
- the amount of lumen closure can be controlled by selecting the size and/or recovery force of the closure device.
- FIG. 1A is a cross-sectional schematic of a vessel including a competent venous valve
- FIG. 1B is a schematic of a vessel including an incompetent venous valve.
- FIG. 2A is a longitudinal cross section of a vessel including a closure device
- FIG. 2B is a radial cross section of the vessel including the closure device.
- FIGS. 3A and 3B are longitudinal and radial cross-sectional views, respectively, illustrating delivery of a closure device using a catheter.
- FIGS. 4A, 4B and 4 C are radial cross-sectional views illustrating implantation of a closure device from within a vessel.
- FIG. 5 is a schematic view of an embodiment of a closure device.
- FIG. 6 is a schematic view of an embodiment of a closure device.
- FIG. 7 is a schematic view of an embodiment of a closure device.
- FIGS. 8A, 8B and 8 C are radial cross-sectional views illustrating implantation of a closure device from within a vessel.
- FIG. 9 is a schematic view of an embodiment of a closure device.
- FIG. 10 is a schematic view of an embodiment of a closure device.
- FIG. 11 is a schematic view of an embodiment of a closure device.
- FIGS. 12A, 12B , and 12 D are longitudinal cross-sectional schematic views and FIG. 12C is a radial cross-sectional schematic view illustrating implantation of a closure device from within a vessel.
- FIGS. 13A, 13B , 13 C, 13 D and 13 E are longitudinal cross-sectional schematic views illustrating implantation of a closure device from within a vessel.
- FIGS. 14A, 14B and 14 C are longitudinal cross-sectional schematic views illustrating implantation of a closure device from within a vessel.
- FIGS. 15A, 15B and 15 C are schematic views of an embodiment of a medical device.
- FIGS. 16A, 16B and 16 C are longitudinal cross-sectional schematic views illustrating implantation of a closure device from within a vessel.
- a valve closure device 20 is illustrated in position about a vessel 22 at the location of a valve 24 including cusps 26 .
- the closure device 20 is an arcuate, open-ended, filament-form defining an arc that includes a body 28 which is located in the lumen of the vessel and two anchoring portions 30 which extend into the walls 32 of the vessel.
- the device 20 provides a force (arrows 34 ) that draws the vessel walls inward, enhancing the function of the valve 24 .
- the closure device 20 does not substantially impede the flow of blood through the vessel.
- the body portion 30 is thin and conforms closely to the vessel wall, outside of central portions of the vessel, where flow volume and rate is greatest.
- the closure device 20 can be positioned at a treatment site in vessel 22 using a catheter 36 , which may be delivered into the vessel percutaneously.
- the catheter 36 includes a long, flexible body adapted for delivery through the vessel and has near its distal end an expander 38 , such as an inflatable balloon.
- Suitable balloon catheters include angioplasty balloon catheters and balloon catheters adapted for delivering stents.
- An example utilizing a coextruded balloon is described in Hamilton et al., U.S. Pat. No. 5,797,877, the entire contents of which is incorporated herein by reference.
- the catheter may be delivered over a guidewire (not shown).
- the device 20 may be friction fit over the catheter.
- a retractable sheath may be used to cover the device and balloon during delivery.
- the closure device 20 in a radially compacted form, is positioned over the expander 38 in a deflated condition for delivery to the treatment site.
- the closure device 20 is installed at the treatment site by expanding the expander 38 , i.e. by inflating the balloon.
- the expander and valve cusps are omitted to more clearly illustrate the installation of the closure device 32 ).
- the closure device 20 is in a compacted condition as it is carried to the treatment site on the catheter, with the expander in the unexpanded condition.
- the closure device 20 is sized such that it is smaller than the cross-section of the vessel.
- the closure device 20 defines an arc that is generally concentric with the arc defined by the vessel wall.
- the anchoring portions 30 terminate in ends 21 which are oriented along a line 40 , substantially parallel to the center line 44 through the cross-section of the vessel and generally parallel to a tangent 42 , on the blood vessel wall 32 .
- the device can both stretch axially (arrow 45 ) and deform radially (arrow 46 ) as well as be displaced upwardly (arrow 47 ). The axial stretching does not fully accommodate the expansion.
- the ends of the filament are deflected such that they are oriented along line 40 , and come into contact with the vessel wall 32 , such that the ends become embedded in the wall.
- the initial penetration of the ends can be enhanced by rotating the catheter slightly about the catheter axis. Referring to FIG. 4C , as the expander is contracted (i.e. deflated) device 30 begins to contract. The ends 21 further penetrate the wall 32 . As shown the ends may pierce the entire thickness of the wall, and deflect inwardly (arrow 49 ) to contract the vessel.
- the closure device can be deployed near the base of cusps of an incompetent venous valve, where the cusps meet the wall of the blood vessel. The deployment may be upstream of the cusps. Alternatively, the deployment site can be downstream of the cusps.
- the catheter is withdrawn through the blood vessel in the same manner the catheter was initially inserted.
- the closure device may be made of a thin elongate, filament form, such as a metal wire.
- the metal may be selected such that the device is elastically expandable from the compacted condition for delivery into a lumen to an expanded condition for implantation. Once implanted, elastic recovery of the wire contracts the device and the vessel wall.
- Suitable metals include elastic steels and superelastic alloy materials such as nitinol.
- the filament may also be a composite material, such as a composite wire. Superelastic metals and composite wires are described in Heath, U.S. Pat. No. 5,725,570, and Mayer, U.S. Pat. No. 5,800,511, the entire contents of both of which are incorporated herein by reference.
- the metal may also be a temperature-effect shape memory superelastic alloy that conforms to an implanted condition upon exposure to a controlled temperature, e.g. body temperature.
- a controlled temperature e.g. body temperature.
- Suitable shape memory alloys such as nitinol are discussed in Schetsky MacDonald “Shape Memory Alloys,” Encyclopedia of Chemical Technology (3 rd ed) John Wiley and Sons, 1982, vol. 20, p. 726-736.
- the temperature of the device may be controlled, for example, by heating the expander or by heating the balloon inflation fluid.
- the wire may also be selected such that the device is plastically deformed from the compacted condition to an expanded condition for embedding the anchoring elements into the vessel wall, with some elastic recovery after the expansion to contract the wall.
- a mechanical gripper can be used to draw the anchoring portions inward.
- the filament may also be made of a flexible polymer.
- the device may be coated with a lubricious polymer or a drug.
- the anchoring portions may include a tissue sealant to minimize bleeding and enhance vessel wall integrity in the penetration regions.
- the anchoring portions can also take a number of different forms that permit the ends of the closure device to penetrate the wall of the blood vessel, and restrain the ends from re-entering the vessel.
- the device 20 is formed of an open-ended strand in the shape of an arc. This shape facilitates deflection of the ends of the strand so that they can be embedded in the vessel wall and also provides a small profile within the vessel, so that blood flow is not substantially impeded.
- the body of the device, within the vessel closely conforms to the inner wall of the lumen.
- the closure device 61 can be an open strand defining an arc, which includes ends 64 with anchoring elements 62 , which define loops.
- the loops defined by the elements 62 prevent the ends 64 of the closure device 61 from reentering the blood vessel and secure the closure device 61 to the wall.
- the loops can be pressed into the vessel wall on implantation.
- the ends can be formed of a temperature effect shape memory metal, such that the ends are in a substantially straight condition for implantation but subsequently revert to a loop shape after being embedded in the vessel wall.
- the closure device 66 can alternatively include ends 68 with anchoring elements 69 configured with barbs, such that the ends 68 can penetrate the wall of the blood vessel and be prevented from reentering the blood vessel by the barbs of the fish hook-like anchoring elements 69 .
- the closure device can be an open strand 120 having flared ends 122 that terminate in barb elements 123 .
- the ends 122 can penetrate the wall of the blood vessel and secure the strand 120 to the wall by the curvature of the flared ends 122 .
- the barb elements are easily pushed into the vessel wall as the device is extended, but resist withdrawal from the wall as the device deflects inwardly.
- the closure device 70 can be a spiraled open strand to form a loop and a half or more, so that the ends 72 are positioned opposite one another, and include fish hook-like anchoring elements 71 .
- the closure device 70 is shown in a compacted condition, with the anchoring elements 71 oriented along a tangent line 73 , which is substantially parallel to the center line 75 through the cross-section of the blood vessel, and parallel to a tangent 74 , on the blood vessel wall.
- the strand can both stretch axially (arrow 78 ) and deform radially (arrow 79 ).
- the axial stretch does not fully accommodate the expansion.
- the free ends 72 of the strand are deflected such that the tangent line 73 defines an angle ⁇ with respect to the tangent 74 on the vessel wall and thus penetrates the vessel wall.
- the ends 72 of the strand further penetrate the wall and deflect inwardly to contract the wall.
- the closure device 76 can be a spiraled open strand to form a loop and a half, so that the ends 72 are positioned opposite one another, and include anchoring elements 77 defining loops. Implantation of this device would be similar to implantation of the device shown in FIG. 8 , as described above.
- the closure device 80 can be a strand in the shape of a thin, flat slotted band including three (or more) anchoring elements 60 .
- the slotted band 80 can include an upper band 65 , middle band 63 and lower band 67 , where the upper band 65 and lower band 67 each include an anchoring element 60 on their distal ends on an opposite side of the band 80 from an anchoring element 60 formed at the distal end of the middle band 63 .
- Expansion of the closure device 80 by an expansion device causes the anchoring elements 60 to penetrate the vessel wall.
- the band 80 attempts to contract to the smaller condition and, because the band 80 is secured to the vessel wall, contracts the cross-section of the vessel.
- the closure device can be a closed, corrugated band 82 .
- the band 82 includes anchoring elements 83 projecting from the exterior surface of the band. As the band 82 is expanded, the anchoring elements 83 penetrate the wall of the blood vessel.
- the anchoring elements 83 can be configured such that they lie flat while being transported through the vessel, and are caused to protrude from the band 82 by the expansion of the band 82 using an expansion device. When the expansion device is contracted, the band 82 attempts to contract to a smaller condition, and the anchoring elements 83 cause the cross-section of the vessel to contract.
- the closure device can be a helical winding 85 having two or more anchoring portions 86 and having any number of helical turns, for example three turns as shown.
- the helical winding 85 can be transported to the treatment site within a vessel 31 using a catheter 88 having an expander 87 on the distal end. The treatment site is in close proximity to an incompetent venous valve 24 .
- the helical winding 85 is mounted to the exterior of the expander 87 and can be held in place by any convenient manner, including, for example, a friction fit.
- a protective sheath 89 can cover the expander 87 and helical winding 85 during transport and be removed once the treatment site is reached.
- the expander 87 is expanded and thereby expands the helical winding 85 from a small condition to a larger condition.
- the expander 87 is expanded until the anchoring portions 86 of the helical winding 85 penetrate the wall 44 of the vessel 31 and secure the helical winding 85 to the interior of the vessel 31 .
- the helical winding 85 can have three anchoring portions 86 as shown in FIG. 12C , or more or less anchoring portions.
- the expander 87 is then contracted and the catheter 88 removed from the vessel 31 , for example, in the same manner the catheter 88 was deployed.
- the helical winding 85 tends to contract to the small condition, for example, due to elastic restoring forces or temperature-effect shape memory effect, thereby pulling the sides of the wall 44 inwardly and contracting the cross-sectional area of the vessel 31 .
- the cusps 38 of the valve 24 are pulled together so that the valve 24 can function competently to prevent antegrade flow within the vessel 31 .
- the closure device can be a helical winding 94 that is positioned about the exterior of a vessel 31 in the vicinity of an incompetent venous valve 24 .
- a catheter 90 having an expander 93 on the distal end is transported to a treatment site with the expander 93 in a contracted state.
- the treatment site is at or near the incompetent venous valve 24 .
- the catheter 90 includes a lumen 91 having an opening 92 at or near the base of the expander 93 .
- the expander 93 is expanded to at least the interior dimension of the vessel 31 .
- the helical winding 94 is formed of a shape-memory material and is passed through the catheter lumen 91 in a substantially straight position, as shown in FIG. 13C .
- the helical winding 94 is pushed through the opening 92 , which opening 92 is configured such that the winding 94 is directed toward the wall 44 of the vessel 31 .
- the winding 94 penetrates and is pushed through the wall 44 .
- the shape-memory effect causes the winding 94 to revert to a helix as the winding is pushed from the catheter lumen 91 , and rides along the outside of the vessel 31 .
- the expander 93 is contracted and the catheter 90 is withdrawn from the vessel.
- the helical winding 94 is configured so that when the shape-memory effect causes the winding to revert to a helix, the helical winding 94 pulls the wall 44 of the vessel 31 inwardly, causing the cusps 38 to pull together so that the valve can function competently.
- the winding 94 can be held in place by friction.
- the closure device 100 can be an angular hinge-form with at least two linear legs 102 .
- the closure device 100 can be transported in a compressed condition to a deployment site in the blood vessel by a delivery catheter 103 having a housing 105 for containing the closure device 100 in the compressed condition until the deployment site is reached.
- the device 100 can be pushed out of the housing 105 by the distal end of the catheter, which can be temporarily connected to the device 100 , for example, by a threaded connection.
- FIG. 14B the device 100 will naturally expand upon being released from the confines of the housing 105 .
- An expansion device 106 such as an inflatable balloon, on the distal end of the catheter 103 can be inflated to further expand the closure device 100 by spreading the legs 102 until the anchoring elements 104 penetrate the wall 44 of the blood vessel 41 .
- the device 100 is then pulled in the direction of the catheter by the distal end of the catheter, which is still connected to the device 100 . This movement causes the anchoring elements 104 to fully penetrate the wall of the blood vessel, and secure the device 100 to the vessel.
- the catheter is disconnected from the device 100 and removed from the vessel.
- the device 100 attempts to contract to a smaller condition, thus causing the cross section of the blood vessel to contract.
- the expander can be a mechanical expander 135 including at least two coiled springs 128 , 129 and having a two-part axial member including an outer tube 133 and an inner rod 134 .
- the inner rod 134 is affixed to a first coil 129 and can rotate independently of the outer tube 133 , which is affixed to a second coil 128 .
- the mechanical expander 135 is used in conjunction with a closure device 125 configured to mount about the coils 128 , 129 .
- Each coil 128 , 129 has an end 130 , 131 configured to fit within a groove 127 formed on either end of the closure device 125 .
- the coils 128 , 129 and closure device 125 are held together while the expansion device is transported to a treatment site.
- the mechanical expander 135 is expanded to expand the closure device 125 , thereby causing the anchoring portions 126 of the closure device 125 to penetrate a vessel wall, in a similar manner as described above.
- the mechanical expander 135 expands by rotating the inner rod 134 to expand the first coil 129 and rotating the outer tube 133 to expand the second coil 128 .
- the coils 128 , 129 expand radially in opposite directions, exerting a radial force on the closure device 125 , causing the anchoring portions 126 to penetrate a vessel wall.
- the mechanical expander 135 can be disengaged from the closure device 125 by sliding the mechanical expander 135 axially away from the closure device 125 .
- the mechanical expander 135 is contracted by rotating the inner rod and outer tube in the opposite directions used for expansion, and is withdrawn from the vessel.
- a retractable sheath can enclose the mechanical expander 135 and closure device 125 while positioning the assembly at the treatment site, which sheath is then retracted.
- the expander can be a leveraging device 112 having at least two flexible legs 114 , an axial member 115 and a splayed cuff 116 .
- a closure device 117 can be mounted onto the exterior of the legs 114 .
- the axial member 115 can be pulled causing the legs 114 to press against the cuff 116 .
- the force of the flexible legs 114 against the splayed cuff 116 causes the flexible legs 114 to expand outwardly and the splayed cuff 116 to fan out.
- the expansion of the circumference around the flexible legs 114 causes the closure device 117 to expand and anchor to the wall of the blood vessel 31 , as described above.
- the axial member 115 is pushed to release the pressure on the flexible legs 114 , causing them to revert back to the original compressed condition. Similarly, with the force on the splayed cuff 116 removed, the cuff 116 recovers to the original state. The expansion device can then be retracted from the vessel.
- a closure device may be used to treat vascular vessels at locations without a valve to constrict the vessel at a desired location and other body lumens outside the vascular system.
Abstract
Method and apparatus implementing and using techniques for body lumen closure, including use of an implantable medical closure device. The device includes a flexible strand defining an arcuate form. The strand is deformable upon implantation from a large cross-section condition to a small cross-section condition and has at least two anchoring portions disposed along the strand. The anchoring portions are configured to penetrate a wall of a body lumen such that when the strand is deformed to the small cross-section condition, the wall of the body lumen is disposed inwardly.
Description
- This application is a continuation of U.S. application Ser. No. 10/115,552, filed Apr. 3, 2002, the specification of which is incorporated herein by reference.
- A venous valve functions to prevent retrograde flow of blood and allow only antegrade flow of blood to the heart. Referring to
FIG. 1A , a healthyvenous valve 12 is illustrated in avessel 10. The valve is bicuspid, withopposed cusps 14. In the closed condition, thecusps 14 are drawn together to prevent retrograde flow (arrow 16) of blood. Referring toFIG. 1B , if the valve is incompetent, thecusps 14 do not seal properly and retrograde flow of blood occurs. Incompetence of a venous valve is thought to arise from at least the following two medical conditions: varicose veins and chronic venous insufficiency. - In a first aspect, the invention features an implantable medical closure device. The device includes a flexible strand defining an arcuate form. The strand is deformable upon implantation from a large cross-section condition to a small cross-section condition and has at least two anchoring portions disposed along the strand. The anchoring portions are configured to penetrate a wall of a body lumen such that when the strand is deformed to the small cross-section condition, the wall of the body lumen is disposed inwardly.
- The strand can also be deformable from a second small cross-section condition to the large cross-section condition, for example, the strand may be deformed to the second small cross-section condition to facilitate delivery of the strand to a treatment site, where it is then deformed to the large cross-section condition upon implantation. The strand can include free ends, which free ends can include the anchoring portions of the strand. The strand can define an arc, a helix or can include linear leg portions. The strand can be a filament-form or a band and may be corrugated. The strand can deform from the large cross-section condition to the small cross-section condition by, for example, elastic recovery forces or thermal shape-memory effect. The strand can be formed of metal, for example, nitinol. The anchoring portions of the strand can include, for example, a loop or a barb.
- In another aspect, the invention features a catheter system, which system includes a catheter for delivery into a lumen. The catheter includes an expander that can be operated between a small cross-section and a large cross-section. The catheter system also includes a closure device positioned about the expander. The closure device is a strand defining an arcuate form and including at least two anchoring portions configured to penetrate a wall of a body lumen. The closure device is deformable by the expander from a first small cross-section condition to a larger cross-section condition to dispose the closure device into engagement with the lumen wall. The closure device is further deformable to a second small cross-section condition, so that the wall of the body lumen is disposed inwardly.
- The expander can take any convenient form, including, for example, an inflatable balloon, a mechanical expander or a leveraging device. The mechanical expander can include a two-part axial member having a first inner part connected to a first coiled spring and a second outer part connected to a second coiled spring. The closure device is mounted on the first and second coiled springs, and the first inner part of the axial member is rotatable to expand the first coiled spring and the second outer part of the axial member is rotatable to expand the second coiled spring. Expansion of the first and second coiled springs expands the closure device. Each coiled spring can include a distal end configured to fit within a groove formed on either end of the closure device.
- The leveraging device can include a two-part axial member including a first outer part and a second inner part. A splayed cuff is connected to the distal end of the first outer part of the two-part axial member, and at least two flexible legs are connected to the distal end of the second inner part of the two-part axial member. The legs are flared outwardly to contact the distal end of the splayed cuff. The second inner part of the two-part axial member is moveable toward the splayed cuff such that the flexible legs and the splayed cuff expand radially. The closure device is positioned about the flexible legs and expansion of the flexible legs expands the closure device from a first small cross-section condition to a larger cross-section condition. The second inner part of the two-part axial member is also moveable away from the splayed cuff such that the flexible legs and the splayed cuff retract.
- In another aspect, the invention features a method of treating a body lumen. The method includes delivering a closure device into a lumen and positioning the strand about the lumen such that a portion of the strand penetrates the wall of the lumen. The method further includes deforming the strand to a smaller cross-section condition such that the wall of the lumen is disposed inwardly. The strand can be positioned about the lumen such that an end of the strand extends through the wall of the lumen. The strand can be disposed on a catheter, which catheter is then delivered into the lumen. The catheter can include an expansion member.
- Embodiments may have one or more of the following advantages. Closure of a body lumen can be achieved in a minimally invasive manner by delivery of a closure device to a treatment site using a catheter. The closure device may be partially installed within the lumen but configured to minimize profile and thus reduce impedance to the flow of body fluids through the lumen. The amount of lumen closure can be controlled by selecting the size and/or recovery force of the closure device.
- The details of one or more embodiments of the invention are set forth in the accompanying drawings and the description below. Other features, objects, and advantages of the invention will be apparent from the description and drawings, and from the claims.
-
FIG. 1A is a cross-sectional schematic of a vessel including a competent venous valve, whileFIG. 1B is a schematic of a vessel including an incompetent venous valve. -
FIG. 2A is a longitudinal cross section of a vessel including a closure device, whileFIG. 2B is a radial cross section of the vessel including the closure device. -
FIGS. 3A and 3B are longitudinal and radial cross-sectional views, respectively, illustrating delivery of a closure device using a catheter. -
FIGS. 4A, 4B and 4C are radial cross-sectional views illustrating implantation of a closure device from within a vessel. -
FIG. 5 is a schematic view of an embodiment of a closure device. -
FIG. 6 is a schematic view of an embodiment of a closure device. -
FIG. 7 is a schematic view of an embodiment of a closure device. -
FIGS. 8A, 8B and 8C are radial cross-sectional views illustrating implantation of a closure device from within a vessel. -
FIG. 9 is a schematic view of an embodiment of a closure device. -
FIG. 10 is a schematic view of an embodiment of a closure device. -
FIG. 11 is a schematic view of an embodiment of a closure device. -
FIGS. 12A, 12B , and 12D are longitudinal cross-sectional schematic views andFIG. 12C is a radial cross-sectional schematic view illustrating implantation of a closure device from within a vessel. -
FIGS. 13A, 13B , 13C, 13D and 13E are longitudinal cross-sectional schematic views illustrating implantation of a closure device from within a vessel. -
FIGS. 14A, 14B and 14C are longitudinal cross-sectional schematic views illustrating implantation of a closure device from within a vessel. -
FIGS. 15A, 15B and 15C are schematic views of an embodiment of a medical device. -
FIGS. 16A, 16B and 16C are longitudinal cross-sectional schematic views illustrating implantation of a closure device from within a vessel. - Like reference symbols in the various drawings indicate like elements.
- Referring to
FIGS. 2A and 2B , avalve closure device 20 is illustrated in position about avessel 22 at the location of avalve 24 includingcusps 26. Theclosure device 20 is an arcuate, open-ended, filament-form defining an arc that includes abody 28 which is located in the lumen of the vessel and two anchoringportions 30 which extend into thewalls 32 of the vessel. Thedevice 20 provides a force (arrows 34) that draws the vessel walls inward, enhancing the function of thevalve 24. As evident, theclosure device 20 does not substantially impede the flow of blood through the vessel. Thebody portion 30 is thin and conforms closely to the vessel wall, outside of central portions of the vessel, where flow volume and rate is greatest. - Referring to
FIGS. 3A and 3B , theclosure device 20 can be positioned at a treatment site invessel 22 using acatheter 36, which may be delivered into the vessel percutaneously. Thecatheter 36 includes a long, flexible body adapted for delivery through the vessel and has near its distal end anexpander 38, such as an inflatable balloon. Suitable balloon catheters include angioplasty balloon catheters and balloon catheters adapted for delivering stents. An example utilizing a coextruded balloon is described in Hamilton et al., U.S. Pat. No. 5,797,877, the entire contents of which is incorporated herein by reference. The catheter may be delivered over a guidewire (not shown). Thedevice 20 may be friction fit over the catheter. A retractable sheath may be used to cover the device and balloon during delivery. - The
closure device 20, in a radially compacted form, is positioned over theexpander 38 in a deflated condition for delivery to the treatment site. Referring as well toFIGS. 4A-4C , theclosure device 20 is installed at the treatment site by expanding theexpander 38, i.e. by inflating the balloon. (InFIGS. 4A-4C , the expander and valve cusps are omitted to more clearly illustrate the installation of the closure device 32). Referring particularly toFIG. 4A , theclosure device 20 is in a compacted condition as it is carried to the treatment site on the catheter, with the expander in the unexpanded condition. Theclosure device 20 is sized such that it is smaller than the cross-section of the vessel. In the embodiment illustrated, theclosure device 20 defines an arc that is generally concentric with the arc defined by the vessel wall. In this condition, the anchoringportions 30 terminate inends 21 which are oriented along aline 40, substantially parallel to thecenter line 44 through the cross-section of the vessel and generally parallel to a tangent 42, on theblood vessel wall 32. Referring particularly toFIG. 4B , as theclosure device 20 is expanded, the device can both stretch axially (arrow 45) and deform radially (arrow 46) as well as be displaced upwardly (arrow 47). The axial stretching does not fully accommodate the expansion. As a result, the ends of the filament are deflected such that they are oriented alongline 40, and come into contact with thevessel wall 32, such that the ends become embedded in the wall. The initial penetration of the ends can be enhanced by rotating the catheter slightly about the catheter axis. Referring toFIG. 4C , as the expander is contracted (i.e. deflated)device 30 begins to contract. The ends 21 further penetrate thewall 32. As shown the ends may pierce the entire thickness of the wall, and deflect inwardly (arrow 49) to contract the vessel. The closure device can be deployed near the base of cusps of an incompetent venous valve, where the cusps meet the wall of the blood vessel. The deployment may be upstream of the cusps. Alternatively, the deployment site can be downstream of the cusps. The catheter is withdrawn through the blood vessel in the same manner the catheter was initially inserted. - The closure device may be made of a thin elongate, filament form, such as a metal wire. The metal may be selected such that the device is elastically expandable from the compacted condition for delivery into a lumen to an expanded condition for implantation. Once implanted, elastic recovery of the wire contracts the device and the vessel wall. Suitable metals include elastic steels and superelastic alloy materials such as nitinol. The filament may also be a composite material, such as a composite wire. Superelastic metals and composite wires are described in Heath, U.S. Pat. No. 5,725,570, and Mayer, U.S. Pat. No. 5,800,511, the entire contents of both of which are incorporated herein by reference. The metal may also be a temperature-effect shape memory superelastic alloy that conforms to an implanted condition upon exposure to a controlled temperature, e.g. body temperature. Suitable shape memory alloys such as nitinol are discussed in Schetsky MacDonald “Shape Memory Alloys,” Encyclopedia of Chemical Technology (3rd ed) John Wiley and Sons, 1982, vol. 20, p. 726-736. The temperature of the device may be controlled, for example, by heating the expander or by heating the balloon inflation fluid. The wire may also be selected such that the device is plastically deformed from the compacted condition to an expanded condition for embedding the anchoring elements into the vessel wall, with some elastic recovery after the expansion to contract the wall. Alternatively, a mechanical gripper can be used to draw the anchoring portions inward. The filament may also be made of a flexible polymer. The device may be coated with a lubricious polymer or a drug. For example, the anchoring portions may include a tissue sealant to minimize bleeding and enhance vessel wall integrity in the penetration regions.
- The anchoring portions can also take a number of different forms that permit the ends of the closure device to penetrate the wall of the blood vessel, and restrain the ends from re-entering the vessel. In the embodiment illustrated above, the
device 20 is formed of an open-ended strand in the shape of an arc. This shape facilitates deflection of the ends of the strand so that they can be embedded in the vessel wall and also provides a small profile within the vessel, so that blood flow is not substantially impeded. As illustrated above, the body of the device, within the vessel, closely conforms to the inner wall of the lumen. - Referring to
FIG. 5 , in another embodiment, theclosure device 61 can be an open strand defining an arc, which includes ends 64 with anchoringelements 62, which define loops. Once the anchoringelements 62 are positioned on the exterior of the blood vessel, the loops defined by theelements 62 prevent theends 64 of theclosure device 61 from reentering the blood vessel and secure theclosure device 61 to the wall. The loops can be pressed into the vessel wall on implantation. Alternatively, the ends can be formed of a temperature effect shape memory metal, such that the ends are in a substantially straight condition for implantation but subsequently revert to a loop shape after being embedded in the vessel wall. - Referring to
FIG. 6 , theclosure device 66 can alternatively include ends 68 with anchoringelements 69 configured with barbs, such that the ends 68 can penetrate the wall of the blood vessel and be prevented from reentering the blood vessel by the barbs of the fish hook-like anchoring elements 69. - Referring to
FIG. 7 , the closure device can be anopen strand 120 having flared ends 122 that terminate inbarb elements 123. The ends 122 can penetrate the wall of the blood vessel and secure thestrand 120 to the wall by the curvature of the flared ends 122. The barb elements are easily pushed into the vessel wall as the device is extended, but resist withdrawal from the wall as the device deflects inwardly. - As shown in
FIGS. 8A-8C , theclosure device 70 can be a spiraled open strand to form a loop and a half or more, so that the ends 72 are positioned opposite one another, and include fish hook-like anchoring elements 71. Referring particularly toFIG. 8A , theclosure device 70 is shown in a compacted condition, with the anchoring elements 71 oriented along atangent line 73, which is substantially parallel to thecenter line 75 through the cross-section of the blood vessel, and parallel to a tangent 74, on the blood vessel wall. Referring particularly toFIG. 8B , as theclosure device 70 is expanded by the expansion device (not shown), the strand can both stretch axially (arrow 78) and deform radially (arrow 79). The axial stretch does not fully accommodate the expansion. As a result, the free ends 72 of the strand are deflected such that thetangent line 73 defines an angle θ with respect to the tangent 74 on the vessel wall and thus penetrates the vessel wall. Referring toFIG. 8C , as thedevice 70 begins to contract, the ends 72 of the strand further penetrate the wall and deflect inwardly to contract the wall. - Referring to
FIG. 9 , theclosure device 76 can be a spiraled open strand to form a loop and a half, so that the ends 72 are positioned opposite one another, and include anchoringelements 77 defining loops. Implantation of this device would be similar to implantation of the device shown inFIG. 8 , as described above. - Referring to
FIG. 10 , theclosure device 80 can be a strand in the shape of a thin, flat slotted band including three (or more) anchoring elements 60. The slottedband 80 can include anupper band 65,middle band 63 andlower band 67, where theupper band 65 andlower band 67 each include an anchoring element 60 on their distal ends on an opposite side of theband 80 from an anchoring element 60 formed at the distal end of themiddle band 63. Expansion of theclosure device 80 by an expansion device causes the anchoring elements 60 to penetrate the vessel wall. Upon contracting the expansion device, theband 80 attempts to contract to the smaller condition and, because theband 80 is secured to the vessel wall, contracts the cross-section of the vessel. - Referring to
FIG. 11 , in another embodiment, the closure device can be a closed,corrugated band 82. Theband 82 includes anchoringelements 83 projecting from the exterior surface of the band. As theband 82 is expanded, the anchoringelements 83 penetrate the wall of the blood vessel. The anchoringelements 83 can be configured such that they lie flat while being transported through the vessel, and are caused to protrude from theband 82 by the expansion of theband 82 using an expansion device. When the expansion device is contracted, theband 82 attempts to contract to a smaller condition, and theanchoring elements 83 cause the cross-section of the vessel to contract. - Referring to
FIGS. 12A-12D , the closure device can be a helical winding 85 having two ormore anchoring portions 86 and having any number of helical turns, for example three turns as shown. Referring toFIG. 12A , the helical winding 85 can be transported to the treatment site within avessel 31 using acatheter 88 having anexpander 87 on the distal end. The treatment site is in close proximity to an incompetentvenous valve 24. The helical winding 85 is mounted to the exterior of theexpander 87 and can be held in place by any convenient manner, including, for example, a friction fit. Optionally, aprotective sheath 89 can cover theexpander 87 and helical winding 85 during transport and be removed once the treatment site is reached. Referring toFIG. 12B , theexpander 87 is expanded and thereby expands the helical winding 85 from a small condition to a larger condition. Theexpander 87 is expanded until the anchoringportions 86 of the helical winding 85 penetrate thewall 44 of thevessel 31 and secure the helical winding 85 to the interior of thevessel 31. The helical winding 85 can have three anchoringportions 86 as shown inFIG. 12C , or more or less anchoring portions. Theexpander 87 is then contracted and thecatheter 88 removed from thevessel 31, for example, in the same manner thecatheter 88 was deployed. Referring toFIG. 12D , with theexpander 87 no longer exerting pressure on the helical winding 85, the helical winding 85 tends to contract to the small condition, for example, due to elastic restoring forces or temperature-effect shape memory effect, thereby pulling the sides of thewall 44 inwardly and contracting the cross-sectional area of thevessel 31. With the helical winding 85 in place within thevessel 31, thecusps 38 of thevalve 24 are pulled together so that thevalve 24 can function competently to prevent antegrade flow within thevessel 31. - Referring to
FIGS. 13A-13E , the closure device can be a helical winding 94 that is positioned about the exterior of avessel 31 in the vicinity of an incompetentvenous valve 24. Referring toFIG. 13A , acatheter 90 having anexpander 93 on the distal end is transported to a treatment site with theexpander 93 in a contracted state. The treatment site is at or near the incompetentvenous valve 24. Thecatheter 90 includes alumen 91 having anopening 92 at or near the base of theexpander 93. Referring toFIG. 13B , at the treatment site theexpander 93 is expanded to at least the interior dimension of thevessel 31. The helical winding 94 is formed of a shape-memory material and is passed through thecatheter lumen 91 in a substantially straight position, as shown inFIG. 13C . The helical winding 94 is pushed through theopening 92, whichopening 92 is configured such that the winding 94 is directed toward thewall 44 of thevessel 31. The winding 94 penetrates and is pushed through thewall 44. The shape-memory effect causes the winding 94 to revert to a helix as the winding is pushed from thecatheter lumen 91, and rides along the outside of thevessel 31. Once the helical winding 94 has completely exited thecatheter lumen 91 and is situated about the exterior of thevessel 31, theexpander 93 is contracted and thecatheter 90 is withdrawn from the vessel. The helical winding 94 is configured so that when the shape-memory effect causes the winding to revert to a helix, the helical winding 94 pulls thewall 44 of thevessel 31 inwardly, causing thecusps 38 to pull together so that the valve can function competently. The winding 94 can be held in place by friction. - Referring to
FIGS. 14A-14C , theclosure device 100 can be an angular hinge-form with at least twolinear legs 102. Theclosure device 100 can be transported in a compressed condition to a deployment site in the blood vessel by adelivery catheter 103 having ahousing 105 for containing theclosure device 100 in the compressed condition until the deployment site is reached. Thedevice 100 can be pushed out of thehousing 105 by the distal end of the catheter, which can be temporarily connected to thedevice 100, for example, by a threaded connection. Referring particularly toFIG. 14B , thedevice 100 will naturally expand upon being released from the confines of thehousing 105. Anexpansion device 106, such as an inflatable balloon, on the distal end of thecatheter 103 can be inflated to further expand theclosure device 100 by spreading thelegs 102 until the anchoringelements 104 penetrate thewall 44 of the blood vessel 41. Thedevice 100 is then pulled in the direction of the catheter by the distal end of the catheter, which is still connected to thedevice 100. This movement causes the anchoringelements 104 to fully penetrate the wall of the blood vessel, and secure thedevice 100 to the vessel. The catheter is disconnected from thedevice 100 and removed from the vessel. Thedevice 100 attempts to contract to a smaller condition, thus causing the cross section of the blood vessel to contract. - Referring to
FIGS. 15A-15C , the expander can be amechanical expander 135 including at least twocoiled springs outer tube 133 and aninner rod 134. Theinner rod 134 is affixed to afirst coil 129 and can rotate independently of theouter tube 133, which is affixed to asecond coil 128. Themechanical expander 135 is used in conjunction with aclosure device 125 configured to mount about thecoils coil end groove 127 formed on either end of theclosure device 125. In this manner, thecoils closure device 125 are held together while the expansion device is transported to a treatment site. At the treatment site, themechanical expander 135 is expanded to expand theclosure device 125, thereby causing the anchoringportions 126 of theclosure device 125 to penetrate a vessel wall, in a similar manner as described above. - The
mechanical expander 135 expands by rotating theinner rod 134 to expand thefirst coil 129 and rotating theouter tube 133 to expand thesecond coil 128. Thecoils closure device 125, causing the anchoringportions 126 to penetrate a vessel wall. Once theclosure device 125 is secured to the vessel wall, themechanical expander 135 can be disengaged from theclosure device 125 by sliding themechanical expander 135 axially away from theclosure device 125. Themechanical expander 135 is contracted by rotating the inner rod and outer tube in the opposite directions used for expansion, and is withdrawn from the vessel. Optionally, a retractable sheath can enclose themechanical expander 135 andclosure device 125 while positioning the assembly at the treatment site, which sheath is then retracted. - Referring to
FIGS. 16A-16B , the expander can be a leveragingdevice 112 having at least twoflexible legs 114, anaxial member 115 and a splayedcuff 116. Aclosure device 117 can be mounted onto the exterior of thelegs 114. At a deployment site, theaxial member 115 can be pulled causing thelegs 114 to press against thecuff 116. The force of theflexible legs 114 against the splayedcuff 116 causes theflexible legs 114 to expand outwardly and the splayedcuff 116 to fan out. The expansion of the circumference around theflexible legs 114 causes theclosure device 117 to expand and anchor to the wall of theblood vessel 31, as described above. Once theclosure device 117 is secured to the wall, theaxial member 115 is pushed to release the pressure on theflexible legs 114, causing them to revert back to the original compressed condition. Similarly, with the force on the splayedcuff 116 removed, thecuff 116 recovers to the original state. The expansion device can then be retracted from the vessel. - Other embodiments are within the scope of the following claims. For example, a closure device may be used to treat vascular vessels at locations without a valve to constrict the vessel at a desired location and other body lumens outside the vascular system.
Claims (20)
1. An implantable medical closure device, comprising:
a flexible strand defining a continuous arcuate form having a first half with a first anchoring end and a second half with a second anchoring end, the first half and the second half being opposed relative a center line bisecting the flexible strand, where in a first state the flexible strand adjacent the first anchoring end and the second anchoring end provide for a tangential line that is parallel with the center line, and in a second state the flexible strand adjacent the first anchoring end and the second anchoring end provide for lines that are no longer parallel with the center line.
2. The device of claim 1 , where the flexible strand is formed of a material that can provide a force to move the first anchoring end and the second anchoring end toward the first state.
3. The device of claim 2 , where the material is a metal.
4. The device of claim 3 , where the metal is nitinol.
5. The device of claim 1 , where the strand is a filament-form.
6. The device of claim 1 , where the first anchoring end and the second anchoring end include a barb.
7. The device of claim 1 , where the flexible strand is a flexible polymer.
8. The device of claim 1 , where the flexible strand defines at least one loop for the continuous arcuate form.
9. An implantable medical closure device, comprising:
a flexible member having a first half and a second half that extend from a center line in a continuous arcuate form, and having a first anchoring end and a second anchoring end opposed to the first anchoring end across the center line, where in a first state the flexible strand adjacent the first anchoring end and the second anchoring end provide for a tangential line that is parallel with the center line, and in a second state the flexible strand adjacent the first anchoring end and the second anchoring end provide for lines that are no longer parallel with the center line.
10. The device of claim 9 , where the flexible strand is formed of a material that can provide a force to move the first anchoring end and the second anchoring end toward the first state.
11. The device of claim 10 , where the material is nitinol.
12. The device of claim 9 , where the first anchoring end and the second anchoring end include a barb.
13. The device of claim 9 , where the flexible strand defines at least one loop for the continuous arcuate form.
14. A catheter system, comprising:
a catheter for delivery into a lumen, the catheter including an expander that can be operated between a small cross-section and a large cross-section; and
a closure device positioned about the expander, the closure device comprising a flexible strand defining a continuous arcuate form having a first half and a second half that extend from a center line, the first half having a first anchoring end and the second half having a second anchoring end, where when the closure device is positioned on the expander in the small cross-section the flexible strand adjacent the first anchoring end and the second anchoring end provide for a tangential line that is parallel with the center line, and when the closure device is positioned on the expanded in the large cross-section, relative the small cross-section, the flexible strand adjacent the first anchoring end and the second anchoring end provide for lines that are no longer parallel with the center line.
15. The catheter system of claim 14 , where the expander comprises an inflatable balloon.
16. The catheter system of claim 14 , where the expander comprises a mechanical expander.
17. The catheter system of claim 14 , where the expander comprises a leveraging device.
18. The catheter system of claim 17 , where the leveraging device comprises:
a two-part axial member including a first outer part and a second inner part;
a splayed cuff connected to the distal end of the first outer part of the two-part axial member; and
at least two flexible legs connected to the distal end of the second inner part of the two-part axial member and flared outwardly to contact the distal end of the splayed cuff.
19. The catheter system of claim 17 , where the closure device is positioned about the flexible legs;
the second inner part of the two-part axial member is moveable in a first direction such that the flexible legs are pressed against the splayed cuff causing the flexible legs and the splayed cuff to expand radially; and
expansion of the flexible legs expands the closure device from the first small cross-section condition to the larger cross-section condition.
20. The catheter system of claim 19 , where the second inner part of the two-part axial member is moveable in a second direction such that the flexible legs move away from the splayed cuff causing the flexible legs and the splayed cuff to retract.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US11/296,590 US20060085066A1 (en) | 2002-04-03 | 2005-12-07 | Body lumen closure |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US10/115,552 US7007698B2 (en) | 2002-04-03 | 2002-04-03 | Body lumen closure |
US11/296,590 US20060085066A1 (en) | 2002-04-03 | 2005-12-07 | Body lumen closure |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/115,552 Continuation US7007698B2 (en) | 2002-04-03 | 2002-04-03 | Body lumen closure |
Publications (1)
Publication Number | Publication Date |
---|---|
US20060085066A1 true US20060085066A1 (en) | 2006-04-20 |
Family
ID=28673796
Family Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/115,552 Expired - Fee Related US7007698B2 (en) | 2002-04-03 | 2002-04-03 | Body lumen closure |
US11/296,590 Abandoned US20060085066A1 (en) | 2002-04-03 | 2005-12-07 | Body lumen closure |
Family Applications Before (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/115,552 Expired - Fee Related US7007698B2 (en) | 2002-04-03 | 2002-04-03 | Body lumen closure |
Country Status (6)
Country | Link |
---|---|
US (2) | US7007698B2 (en) |
EP (1) | EP1489997A1 (en) |
JP (1) | JP4388821B2 (en) |
AU (1) | AU2003226217A1 (en) |
CA (1) | CA2480876A1 (en) |
WO (1) | WO2003084442A1 (en) |
Families Citing this family (86)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6676698B2 (en) * | 2000-06-26 | 2004-01-13 | Rex Medicol, L.P. | Vascular device with valve for approximating vessel wall |
ES2349952T3 (en) * | 2002-08-29 | 2011-01-13 | St. Jude Medical, Cardiology Division, Inc. | IMPLANTABLE DEVICES FOR CONTROLLING THE INTERNAL CIRCUMFERENCE OF AN ANATOMICAL ORIFICE OR LUMEN. |
US7223266B2 (en) | 2003-02-04 | 2007-05-29 | Cardiodex Ltd. | Methods and apparatus for hemostasis following arterial catheterization |
US7056286B2 (en) * | 2003-11-12 | 2006-06-06 | Adrian Ravenscroft | Medical device anchor and delivery system |
EP1547526A1 (en) * | 2003-12-23 | 2005-06-29 | UMC Utrecht Holding B.V. | Operation element, operation set and method for use thereof |
CA2587228A1 (en) | 2004-11-22 | 2006-05-26 | Cardiodex Ltd. | Techniques for heat-treating varicose veins |
US7331991B2 (en) * | 2005-02-25 | 2008-02-19 | California Institute Of Technology | Implantable small percutaneous valve and methods of delivery |
EP2767260B1 (en) * | 2005-03-25 | 2019-07-03 | St. Jude Medical, Cardiology Division, Inc. | Apparatus for controlling the internal circumference of an anatomic orifice or lumen |
US8864823B2 (en) * | 2005-03-25 | 2014-10-21 | StJude Medical, Cardiology Division, Inc. | Methods and apparatus for controlling the internal circumference of an anatomic orifice or lumen |
US7758594B2 (en) * | 2005-05-20 | 2010-07-20 | Neotract, Inc. | Devices, systems and methods for treating benign prostatic hyperplasia and other conditions |
US8502681B2 (en) * | 2005-06-20 | 2013-08-06 | Biovigil, Llc | Hand cleanliness |
US7936275B2 (en) * | 2005-06-20 | 2011-05-03 | Biovigil, Llc | Hand cleanliness |
US7616122B2 (en) | 2005-06-20 | 2009-11-10 | Biovigil, Llc | Hand cleanliness |
US7286057B2 (en) * | 2005-06-20 | 2007-10-23 | Biovigil Llc | Hand cleanliness |
US20070112423A1 (en) * | 2005-11-16 | 2007-05-17 | Chu Jack F | Devices and methods for treatment of venous valve insufficiency |
US7780724B2 (en) * | 2006-02-24 | 2010-08-24 | California Institute Of Technology | Monolithic in situ forming valve system |
US20080275550A1 (en) * | 2006-02-24 | 2008-11-06 | Arash Kheradvar | Implantable small percutaneous valve and methods of delivery |
US7955380B2 (en) * | 2006-03-17 | 2011-06-07 | Medtronic Vascular, Inc. | Prosthesis fixation apparatus and methods |
JP5148598B2 (en) | 2006-05-03 | 2013-02-20 | ラプトール リッジ, エルエルシー | Tissue closure system and method |
US20080031838A1 (en) * | 2006-08-03 | 2008-02-07 | Bolling Steven F | Tracing hand cleaner |
US9220487B2 (en) | 2006-08-09 | 2015-12-29 | Coherex Medical, Inc. | Devices for reducing the size of an internal tissue opening |
US20080039743A1 (en) | 2006-08-09 | 2008-02-14 | Coherex Medical, Inc. | Methods for determining characteristics of an internal tissue opening |
US8529597B2 (en) | 2006-08-09 | 2013-09-10 | Coherex Medical, Inc. | Devices for reducing the size of an internal tissue opening |
US8784439B1 (en) * | 2006-11-28 | 2014-07-22 | Stephen V. Ward | Percutaneous medical procedures and devices for closing vessels using mechanical closures |
EP2111189B1 (en) * | 2007-01-03 | 2017-04-05 | St. Jude Medical, Cardiology Division, Inc. | Implantable devices for controlling the size and shape of an anatomical structure or lumen |
WO2008091493A1 (en) * | 2007-01-08 | 2008-07-31 | California Institute Of Technology | In-situ formation of a valve |
US20100249920A1 (en) * | 2007-01-08 | 2010-09-30 | Millipede Llc | Reconfiguring heart features |
US9192471B2 (en) * | 2007-01-08 | 2015-11-24 | Millipede, Inc. | Device for translumenal reshaping of a mitral valve annulus |
US20100121433A1 (en) * | 2007-01-08 | 2010-05-13 | Millipede Llc, A Corporation Of Michigan | Reconfiguring heart features |
US20080215072A1 (en) * | 2007-02-15 | 2008-09-04 | Graham Kelly | Methods and apparatus for utilization of barbed sutures in human tissue including a method for eliminating or improving blood flow in veins |
JP2010536437A (en) | 2007-08-15 | 2010-12-02 | カーディオデックス リミテッド | System and method for occluding a puncture |
US8834551B2 (en) | 2007-08-31 | 2014-09-16 | Rex Medical, L.P. | Vascular device with valve for approximating vessel wall |
CA2701755A1 (en) * | 2007-10-05 | 2009-04-09 | Noam Mizrahi | Systems and methods for puncture closure |
US10166127B2 (en) | 2007-12-12 | 2019-01-01 | Intact Vascular, Inc. | Endoluminal device and method |
US9603730B2 (en) | 2007-12-12 | 2017-03-28 | Intact Vascular, Inc. | Endoluminal device and method |
US9375327B2 (en) | 2007-12-12 | 2016-06-28 | Intact Vascular, Inc. | Endovascular implant |
US7896911B2 (en) | 2007-12-12 | 2011-03-01 | Innovasc Llc | Device and method for tacking plaque to blood vessel wall |
US20110230954A1 (en) * | 2009-06-11 | 2011-09-22 | Peter Schneider | Stent device having focal elevating elements for minimal surface area contact with lumen walls |
US8128677B2 (en) | 2007-12-12 | 2012-03-06 | Intact Vascular LLC | Device and method for tacking plaque to a blood vessel wall |
US10022250B2 (en) | 2007-12-12 | 2018-07-17 | Intact Vascular, Inc. | Deployment device for placement of multiple intraluminal surgical staples |
US9480826B2 (en) | 2008-03-21 | 2016-11-01 | Cagent Vascular, Llc | Intravascular device |
US11219750B2 (en) | 2008-03-21 | 2022-01-11 | Cagent Vascular, Inc. | System and method for plaque serration |
WO2009117158A2 (en) | 2008-03-21 | 2009-09-24 | Innovasc Llc | Device and method for opening blood vessels by pre-angioplasty serration and dilatation of aetherosclerotic plaque |
US20090248142A1 (en) * | 2008-03-25 | 2009-10-01 | Medtronic Vascular, Inc. | Methods, Devices and Systems for Treating Venous Insufficiency |
WO2009121001A1 (en) * | 2008-03-28 | 2009-10-01 | Coherex Medical, Inc. | Delivery systems for a medical device and related methods |
US10016196B2 (en) | 2008-09-11 | 2018-07-10 | Covidien Lp | Tapered looped suture |
US20100204729A1 (en) * | 2008-09-11 | 2010-08-12 | Ahmad Robert Hadba | Tapered Looped Suture |
WO2010085649A1 (en) * | 2009-01-22 | 2010-07-29 | St. Jude Medical | Post-operative adjustment tool, minimally invasive attachment apparatus, and adjustable tricuspid ring |
US20120010645A1 (en) * | 2009-03-20 | 2012-01-12 | Proarc Medical Ltd. | Methods and devices for urethral treatment |
US8292948B2 (en) * | 2010-02-17 | 2012-10-23 | Medtronic Vascular, Inc. | Apparatus and methods for creating a venous valve from autologous tissue |
US9504572B2 (en) * | 2010-02-17 | 2016-11-29 | Medtronic Vascular, Inc. | Apparatus and methods for creating a venous valve from autologous tissue |
US8496671B1 (en) * | 2010-06-16 | 2013-07-30 | Cardica, Inc. | Mitral valve treatment |
US20120053680A1 (en) | 2010-08-24 | 2012-03-01 | Bolling Steven F | Reconfiguring Heart Features |
EP2685933B1 (en) * | 2011-03-17 | 2019-02-27 | Proarc Medical Ltd. | Devices for urethral treatment |
US10271973B2 (en) | 2011-06-03 | 2019-04-30 | Intact Vascular, Inc. | Endovascular implant |
US9668859B2 (en) | 2011-08-05 | 2017-06-06 | California Institute Of Technology | Percutaneous heart valve delivery systems |
EP2806826B1 (en) | 2012-01-25 | 2020-01-08 | Intact Vascular, Inc. | Endoluminal device |
US9168122B2 (en) | 2012-04-26 | 2015-10-27 | Rex Medical, L.P. | Vascular device and method for valve leaflet apposition |
US10849755B2 (en) | 2012-09-14 | 2020-12-01 | Boston Scientific Scimed, Inc. | Mitral valve inversion prostheses |
US10543088B2 (en) | 2012-09-14 | 2020-01-28 | Boston Scientific Scimed, Inc. | Mitral valve inversion prostheses |
CA2939823C (en) | 2013-03-14 | 2021-11-16 | Proarc Medical Ltd. | Methods and devices for urethral treatment |
WO2014144247A1 (en) | 2013-03-15 | 2014-09-18 | Arash Kheradvar | Handle mechanism and functionality for repositioning and retrieval of transcatheter heart valves |
WO2015077356A1 (en) | 2013-11-19 | 2015-05-28 | Wheeler William K | Fastener applicator with interlock |
US9668861B2 (en) | 2014-03-15 | 2017-06-06 | Rex Medical, L.P. | Vascular device for treating venous valve insufficiency |
US10463842B2 (en) | 2014-06-04 | 2019-11-05 | Cagent Vascular, Llc | Cage for medical balloon |
US9180005B1 (en) | 2014-07-17 | 2015-11-10 | Millipede, Inc. | Adjustable endolumenal mitral valve ring |
CA2969535A1 (en) | 2014-11-03 | 2016-05-12 | Cagent Vascular, Llc | Serration balloon |
US9433520B2 (en) | 2015-01-29 | 2016-09-06 | Intact Vascular, Inc. | Delivery device and method of delivery |
US9375336B1 (en) | 2015-01-29 | 2016-06-28 | Intact Vascular, Inc. | Delivery device and method of delivery |
JP6735294B2 (en) | 2015-02-13 | 2020-08-05 | 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. | Implantable heart valve device |
WO2016196270A1 (en) | 2015-06-01 | 2016-12-08 | Edwards Lifesciences Corporation | Cardiac valve repair devices configured for percutaneous delivery |
US20170020671A1 (en) * | 2015-07-22 | 2017-01-26 | Boston Scientific Scimed Inc. | Actuated extra-venous valve |
US10166374B2 (en) | 2015-09-17 | 2019-01-01 | Cagent Vascular, Llc | Wedge dissectors for a medical balloon |
US10335275B2 (en) | 2015-09-29 | 2019-07-02 | Millipede, Inc. | Methods for delivery of heart valve devices using intravascular ultrasound imaging |
ES2554296B1 (en) * | 2015-10-02 | 2017-01-18 | Jose Ignacio ARAMENDI GALLARDO | REABSORBABLE SUBAORTIC RING |
EP3377000B1 (en) | 2015-11-17 | 2023-02-01 | Boston Scientific Scimed, Inc. | Implantable device and delivery system for reshaping a heart valve annulus |
US10993824B2 (en) | 2016-01-01 | 2021-05-04 | Intact Vascular, Inc. | Delivery device and method of delivery |
US20200146854A1 (en) | 2016-05-16 | 2020-05-14 | Elixir Medical Corporation | Methods and devices for heart valve repair |
CN110114108B (en) | 2016-11-16 | 2022-12-06 | 开金血管公司 | System and method for depositing a drug into tissue through teeth |
IT201700001625A1 (en) * | 2017-01-10 | 2018-07-10 | Tarabini Carlo Castellani | CORRECTIVE PROSTHESIS FOR PROLASSED BIOLOGICAL VASES |
CN110381887B (en) | 2017-02-10 | 2022-03-29 | 波士顿科学国际有限公司 | Implantable device and delivery system for remodeling a heart valve annulus |
US11069220B2 (en) | 2017-07-10 | 2021-07-20 | Biovigil Hygiene Technologies, Llc | Hand cleanliness monitoring |
US11660218B2 (en) | 2017-07-26 | 2023-05-30 | Intact Vascular, Inc. | Delivery device and method of delivery |
EP3764921A1 (en) | 2018-03-16 | 2021-01-20 | Boston Scientific Scimed Inc. | Devices for vein closure |
EP3773256A4 (en) | 2018-03-28 | 2021-12-15 | Datascope Corporation | Device for atrial appendage exclusion |
WO2020023749A1 (en) | 2018-07-25 | 2020-01-30 | Cagent Vascular, Llc | Medical balloon catheters with enhanced pushability |
Citations (84)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3716058A (en) * | 1970-07-17 | 1973-02-13 | Atlanta Res Inst | Barbed suture |
US4904254A (en) * | 1986-07-17 | 1990-02-27 | Vaso Products Australia Pty. Limited | Correction of incompetent venous valves |
US5002563A (en) * | 1990-02-22 | 1991-03-26 | Raychem Corporation | Sutures utilizing shape memory alloys |
US5601572A (en) * | 1989-08-16 | 1997-02-11 | Raychem Corporation | Device or apparatus for manipulating matter having a elastic ring clip |
US20020013571A1 (en) * | 1999-04-09 | 2002-01-31 | Evalve, Inc. | Methods and devices for capturing and fixing leaflets in valve repair |
US20020026216A1 (en) * | 1999-10-13 | 2002-02-28 | Grimes Randall Y. | Devices and methods for percutaneous mitral valve repair |
US20030050694A1 (en) * | 2001-09-13 | 2003-03-13 | Jibin Yang | Methods and apparatuses for deploying minimally-invasive heart valves |
US20040002719A1 (en) * | 1997-06-27 | 2004-01-01 | Oz Mehmet C. | Method and apparatus for circulatory valve repair |
US6673109B2 (en) * | 1993-11-01 | 2004-01-06 | 3F Therapeutics, Inc. | Replacement atrioventricular heart valve |
US20040003819A1 (en) * | 1999-04-09 | 2004-01-08 | Evalve, Inc. | Methods and apparatus for cardiac valve repair |
US6676702B2 (en) * | 2001-05-14 | 2004-01-13 | Cardiac Dimensions, Inc. | Mitral valve therapy assembly and method |
US6676698B2 (en) * | 2000-06-26 | 2004-01-13 | Rex Medicol, L.P. | Vascular device with valve for approximating vessel wall |
US20040010305A1 (en) * | 2001-12-05 | 2004-01-15 | Cardiac Dimensions, Inc. | Device and method for modifying the shape of a body organ |
US20040015230A1 (en) * | 1996-12-18 | 2004-01-22 | Moll Franciscus Laurens | Methods for regulating the flow of blood through the blood system |
US20040015232A1 (en) * | 2002-07-16 | 2004-01-22 | Medtronic, Inc. | Suturing rings for implantable heart valve prosthesis |
US20040015233A1 (en) * | 2000-10-09 | 2004-01-22 | Josef Jansen | Cardiac valve prosthesis, especially mitral cardiac valve and method for producing the same |
US6682558B2 (en) * | 2001-05-10 | 2004-01-27 | 3F Therapeutics, Inc. | Delivery system for a stentless valve bioprosthesis |
US6682559B2 (en) * | 2000-01-27 | 2004-01-27 | 3F Therapeutics, Inc. | Prosthetic heart valve |
US20040019377A1 (en) * | 2002-01-14 | 2004-01-29 | Taylor Daniel C. | Method and apparatus for reducing mitral regurgitation |
US20040019374A1 (en) * | 2002-05-10 | 2004-01-29 | Hikmat Hojeibane | Frame based unidirectional flow prosthetic implant |
US20040019378A1 (en) * | 2001-04-24 | 2004-01-29 | Hlavka Edwin J. | Method and apparatus for performing catheter-based annuloplasty |
US6685739B2 (en) * | 1999-10-21 | 2004-02-03 | Scimed Life Systems, Inc. | Implantable prosthetic valve |
US20040024451A1 (en) * | 2002-01-02 | 2004-02-05 | Medtronic, Inc. | Prosthetic heart valve system |
US20040024452A1 (en) * | 2002-08-02 | 2004-02-05 | Kruse Steven D. | Valved prostheses with preformed tissue leaflets |
US20040024447A1 (en) * | 2000-04-27 | 2004-02-05 | Axel Haverich | Individual venous valve prosthesis |
US20040030381A1 (en) * | 2002-07-16 | 2004-02-12 | Shu Mark C.S. | Heart valve prosthesis |
US20040030405A1 (en) * | 1994-07-29 | 2004-02-12 | Sophie Carpentier | Methods for treating implantable biological tissues to mitigate the calcification thereof and bioprosthetic articles treated by such methods |
US20040030321A1 (en) * | 2000-07-11 | 2004-02-12 | Fangrow Thomas F. | Medical valve with positive flow characteristics |
US6692512B2 (en) * | 1998-10-13 | 2004-02-17 | Edwards Lifesciences Corporation | Percutaneous filtration catheter for valve repair surgery and methods of use |
US20040034380A1 (en) * | 2001-06-29 | 2004-02-19 | Woolfson Steven B. | Method and apparatus for resecting and replacing an aortic valve |
US20040034411A1 (en) * | 2002-08-16 | 2004-02-19 | Quijano Rodolfo C. | Percutaneously delivered heart valve and delivery means thereof |
US6695878B2 (en) * | 2000-06-26 | 2004-02-24 | Rex Medical, L.P. | Vascular device for valve leaflet apposition |
US6695866B1 (en) * | 1998-07-15 | 2004-02-24 | St. Jude Medical, Inc. | Mitral and tricuspid valve repair |
US20040039443A1 (en) * | 1999-06-30 | 2004-02-26 | Solem Jan Otto | Method and device for treatment of mitral insufficiency |
US20040039436A1 (en) * | 2001-10-11 | 2004-02-26 | Benjamin Spenser | Implantable prosthetic valve |
US20040044350A1 (en) * | 1999-04-09 | 2004-03-04 | Evalve, Inc. | Steerable access sheath and methods of use |
US6837902B2 (en) * | 1997-04-03 | 2005-01-04 | Edwards Lifesciences Corporation | Methods of making bioprosthetic heart valves with strain matched leaflets |
US20050004667A1 (en) * | 2003-06-05 | 2005-01-06 | Cardiac Dimensions, Inc. A Delaware Corporation | Device, system and method to affect the mitral valve annulus of a heart |
US6840246B2 (en) * | 2000-06-20 | 2005-01-11 | University Of Maryland, Baltimore | Apparatuses and methods for performing minimally invasive diagnostic and surgical procedures inside of a beating heart |
US20050010285A1 (en) * | 1999-01-27 | 2005-01-13 | Lambrecht Gregory H. | Cardiac valve procedure methods and devices |
US20050010287A1 (en) * | 2000-09-20 | 2005-01-13 | Ample Medical, Inc. | Devices, systems, and methods for supplementing, repairing, or replacing a native heart valve leaflet |
US20050015112A1 (en) * | 2000-01-27 | 2005-01-20 | Cohn William E. | Cardiac valve procedure methods and devices |
US6846325B2 (en) * | 2000-09-07 | 2005-01-25 | Viacor, Inc. | Fixation band for affixing a prosthetic heart valve to tissue |
US6846324B2 (en) * | 1999-01-26 | 2005-01-25 | Edwards Lifesciences Corporation | Combination anatomical orifice sizer and heart valve |
US20050021136A1 (en) * | 2002-03-21 | 2005-01-27 | Hua Xie | Method for suturelessly attaching a biomaterial to an implantable bioprosthesis frame |
US20050027353A1 (en) * | 2001-05-14 | 2005-02-03 | Alferness Clifton A. | Mitral valve therapy device, system and method |
US20050027261A1 (en) * | 2003-07-30 | 2005-02-03 | Karla Weaver | Pressure actuated valve with improved slit configuration |
US20050027348A1 (en) * | 2003-07-31 | 2005-02-03 | Case Brian C. | Prosthetic valve devices and methods of making such devices |
US20050033398A1 (en) * | 2001-07-31 | 2005-02-10 | Jacques Seguin | Assembly for setting a valve prosthesis in a corporeal duct |
US20050038506A1 (en) * | 2002-11-15 | 2005-02-17 | Webler William E. | Apparatuses and methods for heart valve repair |
US6858039B2 (en) * | 2002-07-08 | 2005-02-22 | Edwards Lifesciences Corporation | Mitral valve annuloplasty ring having a posterior bow |
US20050043792A1 (en) * | 1999-06-29 | 2005-02-24 | Edwards Lifesciences Ag | Device and method for treatment of mitral insufficiency |
US20050043790A1 (en) * | 2001-07-04 | 2005-02-24 | Jacques Seguin | Kit enabling a prosthetic valve to be placed in a body enabling a prosthetic valve to be put into place in a duct in the body |
US20060004442A1 (en) * | 2004-06-30 | 2006-01-05 | Benjamin Spenser | Paravalvular leak detection, sealing, and prevention |
US20060000715A1 (en) * | 2000-01-25 | 2006-01-05 | Whitcher Forrest D | Manufacturing medical devices by vapor deposition |
US20060004439A1 (en) * | 2004-06-30 | 2006-01-05 | Benjamin Spenser | Device and method for assisting in the implantation of a prosthetic valve |
US20060009841A1 (en) * | 2003-05-05 | 2006-01-12 | Rex Medical | Percutaneous aortic valve |
US20060009804A1 (en) * | 2004-07-12 | 2006-01-12 | Pederson Brian D | Anti-coagulation and demineralization system for conductive medical devices |
US20060009842A1 (en) * | 1997-03-27 | 2006-01-12 | Huynh Van L | Contoured heart valve suture rings |
US6986775B2 (en) * | 2002-06-13 | 2006-01-17 | Guided Delivery Systems, Inc. | Devices and methods for heart valve repair |
US20060013855A1 (en) * | 2004-04-05 | 2006-01-19 | Medivas, Llc | Bioactive stents for type II diabetics and methods for use thereof |
US20060015179A1 (en) * | 2004-07-19 | 2006-01-19 | Neil Bulman-Fleming | Aortic annuloplasty ring |
US20060015136A1 (en) * | 2002-09-19 | 2006-01-19 | Memory Metal Holland Bv | Vascular filter with improved strength and flexibility |
US20060013805A1 (en) * | 1998-11-24 | 2006-01-19 | Regents Of The University Of Minnesota | Transgenic circulating endothelial cells |
US20060015178A1 (en) * | 2004-07-15 | 2006-01-19 | Shahram Moaddeb | Implants and methods for reshaping heart valves |
US6989027B2 (en) * | 2003-04-30 | 2006-01-24 | Medtronic Vascular Inc. | Percutaneously delivered temporary valve assembly |
US6989028B2 (en) * | 2000-01-31 | 2006-01-24 | Edwards Lifesciences Ag | Medical system and method for remodeling an extravascular tissue structure |
US20060020275A1 (en) * | 1999-04-09 | 2006-01-26 | Evalve, Inc. | Locking mechanisms for fixation devices and methods of engaging tissue |
US20060020327A1 (en) * | 2004-05-05 | 2006-01-26 | Lashinski Randall T | Nonstented heart valves with formed in situ support |
US20060020336A1 (en) * | 2001-10-23 | 2006-01-26 | Liddicoat John R | Automated annular plication for mitral valve repair |
US20060020335A1 (en) * | 2002-12-26 | 2006-01-26 | Leonard Kowalsky | System and method to effect the mitral valve annulus of a heart |
US20060025750A1 (en) * | 2002-06-13 | 2006-02-02 | Guided Delivery Systems, Inc. | Delivery devices and methods for heart valve repair |
US20060025857A1 (en) * | 2004-04-23 | 2006-02-02 | Bjarne Bergheim | Implantable prosthetic valve |
US20060025784A1 (en) * | 2003-09-04 | 2006-02-02 | Guided Delivery Systems, Inc. | Delivery devices and methods for heart valve repair |
US20060025856A1 (en) * | 2001-03-15 | 2006-02-02 | Medtronic, Inc. | Annuloplasty band and method |
US20060030882A1 (en) * | 2002-03-06 | 2006-02-09 | Adams John M | Transvenous staples, assembly and method for mitral valve repair |
US20060030747A1 (en) * | 2004-07-09 | 2006-02-09 | Kantrowitz Allen B | Synchronization system between aortic valve and cardiac assist device |
US20060030885A1 (en) * | 2002-10-15 | 2006-02-09 | Hyde Gregory M | Apparatuses and methods for heart valve repair |
US20060030866A1 (en) * | 2002-03-26 | 2006-02-09 | Stefan Schreck | Sequential heart valve leaflet repair device and method of use |
US6997950B2 (en) * | 2003-01-16 | 2006-02-14 | Chawla Surendra K | Valve repair device |
US20060036317A1 (en) * | 2002-11-12 | 2006-02-16 | Myocor, Inc. | Decives and methods for heart valve treatment |
US20060041305A1 (en) * | 1996-06-20 | 2006-02-23 | Karl-Lutz Lauterjung | Prosthetic repair of body passages |
US20060041306A1 (en) * | 2002-01-09 | 2006-02-23 | Myocor, Inc. | Devices and methods for heart valve treatment |
US7004176B2 (en) * | 2003-10-17 | 2006-02-28 | Edwards Lifesciences Ag | Heart valve leaflet locator |
Family Cites Families (86)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4170990A (en) * | 1977-01-28 | 1979-10-16 | Fried. Krupp Gesellschaft Mit Beschrankter Haftung | Method for implanting and subsequently removing mechanical connecting elements from living tissue |
US4512338A (en) * | 1983-01-25 | 1985-04-23 | Balko Alexander B | Process for restoring patency to body vessels |
US4580568A (en) | 1984-10-01 | 1986-04-08 | Cook, Incorporated | Percutaneous endovascular stent and method for insertion thereof |
US4872874A (en) | 1987-05-29 | 1989-10-10 | Taheri Syde A | Method and apparatus for transarterial aortic graft insertion and implantation |
US5053047A (en) * | 1989-05-16 | 1991-10-01 | Inbae Yoon | Suture devices particularly useful in endoscopic surgery and methods of suturing |
US5290300A (en) | 1989-07-31 | 1994-03-01 | Baxter International Inc. | Flexible suture guide and holder |
US6010531A (en) * | 1993-02-22 | 2000-01-04 | Heartport, Inc. | Less-invasive devices and methods for cardiac valve surgery |
IL106738A (en) | 1993-08-19 | 1998-02-08 | Mind E M S G Ltd | Device for external correction of deficient valves in venous junctions |
US5582616A (en) * | 1994-08-05 | 1996-12-10 | Origin Medsystems, Inc. | Surgical helical fastener with applicator |
US5549666A (en) | 1994-09-02 | 1996-08-27 | Baxter International Inc. | Natural tissue valve prostheses having variably complaint leaflets |
US5609598A (en) | 1994-12-30 | 1997-03-11 | Vnus Medical Technologies, Inc. | Method and apparatus for minimally invasive treatment of chronic venous insufficiency |
CA2223160C (en) | 1995-06-07 | 2007-09-18 | St. Jude Medical, Inc. | Prosthetic heart valve with increased lumen |
US6764509B2 (en) | 1996-09-06 | 2004-07-20 | Carbomedics Inc. | Prosthetic heart valve with surface modification |
US5957949A (en) | 1997-05-01 | 1999-09-28 | World Medical Manufacturing Corp. | Percutaneous placement valve stent |
US6071292A (en) | 1997-06-28 | 2000-06-06 | Transvascular, Inc. | Transluminal methods and devices for closing, forming attachments to, and/or forming anastomotic junctions in, luminal anatomical structures |
US6059800A (en) | 1997-09-10 | 2000-05-09 | Applied Medical Resources Corporation | Suturing apparatus and method |
FR2768324B1 (en) | 1997-09-12 | 1999-12-10 | Jacques Seguin | SURGICAL INSTRUMENT FOR PERCUTANEOUSLY FIXING TWO AREAS OF SOFT TISSUE, NORMALLY MUTUALLY REMOTE, TO ONE ANOTHER |
US5989268A (en) * | 1997-10-28 | 1999-11-23 | Boston Scientific Corporation | Endoscopic hemostatic clipping device |
US6074418A (en) | 1998-04-20 | 2000-06-13 | St. Jude Medical, Inc. | Driver tool for heart valve prosthesis fasteners |
US6250308B1 (en) | 1998-06-16 | 2001-06-26 | Cardiac Concepts, Inc. | Mitral valve annuloplasty ring and method of implanting |
US6736845B2 (en) | 1999-01-26 | 2004-05-18 | Edwards Lifesciences Corporation | Holder for flexible heart valve |
US6364905B1 (en) | 1999-01-27 | 2002-04-02 | Sulzer Carbomedics Inc. | Tri-composite, full root, stentless valve |
US6179767B1 (en) * | 1999-02-01 | 2001-01-30 | International Business Machines Corporation | Focussing of therapeutic radiation on internal structures of living bodies |
US6666886B1 (en) | 1999-02-16 | 2003-12-23 | Regents Of The University Of Minnesota | Tissue equivalent approach to a tissue-engineered cardiovascular valve |
US7226467B2 (en) * | 1999-04-09 | 2007-06-05 | Evalve, Inc. | Fixation device delivery catheter, systems and methods of use |
US6666885B2 (en) | 1999-04-16 | 2003-12-23 | Carbomedics Inc. | Heart valve leaflet |
BR0010096A (en) * | 1999-04-28 | 2002-02-19 | St Jude Medical | Cardiac valve prosthesis, kit, process to connect a cardiac valve prosthesis to a patient, and a fastener applicator to implant a cardiac valve prosthesis |
US6790229B1 (en) | 1999-05-25 | 2004-09-14 | Eric Berreklouw | Fixing device, in particular for fixing to vascular wall tissue |
US6241763B1 (en) | 1999-06-08 | 2001-06-05 | William J. Drasler | In situ venous valve device and method of formation |
DE19945587A1 (en) | 1999-09-23 | 2001-05-10 | Co Don Ag | Procedure for inserting implants into human organs |
WO2001034068A1 (en) | 1999-11-10 | 2001-05-17 | Impsa International Incorporated | Prosthetic heart valve |
FR2800984B1 (en) | 1999-11-17 | 2001-12-14 | Jacques Seguin | DEVICE FOR REPLACING A HEART VALVE PERCUTANEOUSLY |
US6709457B1 (en) | 1999-11-24 | 2004-03-23 | St. Jude Medical, Inc. | Attachment of suture cuff to prosthetic heart valve |
US6402781B1 (en) | 2000-01-31 | 2002-06-11 | Mitralife | Percutaneous mitral annuloplasty and cardiac reinforcement |
US6821297B2 (en) | 2000-02-02 | 2004-11-23 | Robert V. Snyders | Artificial heart valve, implantation instrument and method therefor |
US6797002B2 (en) | 2000-02-02 | 2004-09-28 | Paul A. Spence | Heart valve repair apparatus and methods |
US6454799B1 (en) | 2000-04-06 | 2002-09-24 | Edwards Lifesciences Corporation | Minimally-invasive heart valves and methods of use |
US7083628B2 (en) * | 2002-09-03 | 2006-08-01 | Edwards Lifesciences Corporation | Single catheter mitral valve repair device and method for use |
US6805711B2 (en) | 2000-06-02 | 2004-10-19 | 3F Therapeutics, Inc. | Expandable medical implant and percutaneous delivery |
EP1401358B1 (en) | 2000-06-30 | 2016-08-17 | Medtronic, Inc. | Apparatus for performing a procedure on a cardiac valve |
US6419696B1 (en) | 2000-07-06 | 2002-07-16 | Paul A. Spence | Annuloplasty devices and related heart valve repair methods |
US6693512B1 (en) * | 2000-07-17 | 2004-02-17 | Armstrong World Industries, Inc. | Device location and identification system |
SE0002878D0 (en) | 2000-08-11 | 2000-08-11 | Kimblad Ola | Device and method of treatment of atrioventricular regurgitation |
US6716224B2 (en) * | 2000-08-28 | 2004-04-06 | Linvatec Corporation | Intracorporeal knot tier |
DE10046550A1 (en) | 2000-09-19 | 2002-03-28 | Adiam Life Science Ag | Prosthetic mitral heart valve consists of support housing with base ring and two stanchions |
US6723038B1 (en) | 2000-10-06 | 2004-04-20 | Myocor, Inc. | Methods and devices for improving mitral valve function |
DE10049865B8 (en) | 2000-10-09 | 2008-10-30 | Universitätsklinikum Freiburg | Device for removing an aortic valve on the human heart by means of a minimally invasive surgical procedure |
US6602286B1 (en) * | 2000-10-26 | 2003-08-05 | Ernst Peter Strecker | Implantable valve system |
US6730122B1 (en) | 2000-11-28 | 2004-05-04 | St. Jude Medical, Inc. | Prosthetic heart valve with increased lumen |
US6716244B2 (en) | 2000-12-20 | 2004-04-06 | Carbomedics, Inc. | Sewing cuff assembly for heart valves |
US6669725B2 (en) | 2000-12-28 | 2003-12-30 | Centerpulse Biologics Inc. | Annuloplasty ring for regeneration of diseased or damaged heart valve annulus |
US6810882B2 (en) | 2001-01-30 | 2004-11-02 | Ev3 Santa Rosa, Inc. | Transluminal mitral annuloplasty |
AU2002243851A1 (en) | 2001-02-05 | 2002-08-19 | Viacor, Inc. | Apparatus and method for reducing mitral regurgitation |
US6786924B2 (en) | 2001-03-15 | 2004-09-07 | Medtronic, Inc. | Annuloplasty band and method |
US6916338B2 (en) * | 2001-03-16 | 2005-07-12 | Mayo Foundation For Medical Education And Research | Synthetic leaflets for heart valve repair or replacement |
DE10121210B4 (en) | 2001-04-30 | 2005-11-17 | Universitätsklinikum Freiburg | Anchoring element for the intraluminal anchoring of a heart valve replacement and method for its production |
ITMI20011012A1 (en) | 2001-05-17 | 2002-11-17 | Ottavio Alfieri | ANNULAR PROSTHESIS FOR MITRAL VALVE |
US7087088B2 (en) * | 2001-05-24 | 2006-08-08 | Torax Medical, Inc. | Methods and apparatus for regulating the flow of matter through body tubing |
US6558400B2 (en) * | 2001-05-30 | 2003-05-06 | Satiety, Inc. | Obesity treatment tools and methods |
US6726716B2 (en) | 2001-08-24 | 2004-04-27 | Edwards Lifesciences Corporation | Self-molding annuloplasty ring |
US6749630B2 (en) | 2001-08-28 | 2004-06-15 | Edwards Lifesciences Corporation | Tricuspid ring and template |
US6723122B2 (en) | 2001-08-30 | 2004-04-20 | Edwards Lifesciences Corporation | Container and method for storing and delivering minimally-invasive heart valves |
US6726715B2 (en) | 2001-10-23 | 2004-04-27 | Childrens Medical Center Corporation | Fiber-reinforced heart valve prosthesis |
US20040044403A1 (en) * | 2001-10-30 | 2004-03-04 | Joyce Bischoff | Tissue-engineered vascular structures |
US6824562B2 (en) | 2002-05-08 | 2004-11-30 | Cardiac Dimensions, Inc. | Body lumen device anchor, device and assembly |
US7311729B2 (en) | 2002-01-30 | 2007-12-25 | Cardiac Dimensions, Inc. | Device and method for modifying the shape of a body organ |
US6805710B2 (en) | 2001-11-13 | 2004-10-19 | Edwards Lifesciences Corporation | Mitral valve annuloplasty ring for molding left ventricle geometry |
US6719784B2 (en) | 2001-11-21 | 2004-04-13 | Scimed Life Systems, Inc. | Counter rotational layering of ePTFE to improve mechanical properties of a prosthesis |
US6755857B2 (en) | 2001-12-12 | 2004-06-29 | Sulzer Carbomedics Inc. | Polymer heart valve with perforated stent and sewing cuff |
US7125420B2 (en) * | 2002-02-05 | 2006-10-24 | Viacor, Inc. | Method and apparatus for improving mitral valve function |
US6716241B2 (en) | 2002-03-05 | 2004-04-06 | John G. Wilder | Venous valve and graft combination |
US6797001B2 (en) | 2002-03-11 | 2004-09-28 | Cardiac Dimensions, Inc. | Device, assembly and method for mitral valve repair |
US6719786B2 (en) | 2002-03-18 | 2004-04-13 | Medtronic, Inc. | Flexible annuloplasty prosthesis and holder |
US6752828B2 (en) | 2002-04-03 | 2004-06-22 | Scimed Life Systems, Inc. | Artificial valve |
US6761735B2 (en) | 2002-04-25 | 2004-07-13 | Medtronic, Inc. | Heart valve fixation process and apparatus |
US20030229394A1 (en) | 2002-06-06 | 2003-12-11 | Ogle Matthew F. | Processed tissue for medical device formation |
WO2003105667A2 (en) * | 2002-06-12 | 2003-12-24 | Mitral Interventions, Inc. | Method and apparatus for tissue connection |
US6761734B2 (en) | 2002-07-22 | 2004-07-13 | William S. Suhr | Segmented balloon catheter for stenting bifurcation lesions |
US8172856B2 (en) * | 2002-08-02 | 2012-05-08 | Cedars-Sinai Medical Center | Methods and apparatus for atrioventricular valve repair |
US6695886B1 (en) | 2002-08-22 | 2004-02-24 | Axcelis Technologies, Inc. | Optical path improvement, focus length change compensation, and stray light reduction for temperature measurement system of RTP tool |
US6875231B2 (en) * | 2002-09-11 | 2005-04-05 | 3F Therapeutics, Inc. | Percutaneously deliverable heart valve |
US20040059412A1 (en) * | 2002-09-25 | 2004-03-25 | Lytle Thomas William | Heart valve holder |
US20040060161A1 (en) * | 2002-09-27 | 2004-04-01 | David Leal | Methods of forming a heart valve stent |
GB0225075D0 (en) * | 2002-10-29 | 2002-12-04 | Smiths Group Plc | Valves |
US20040082910A1 (en) * | 2002-10-29 | 2004-04-29 | Constantz Brent R. | Devices and methods for treating aortic valve stenosis |
US6830585B1 (en) | 2003-01-14 | 2004-12-14 | 3F Therapeutics, Inc. | Percutaneously deliverable heart valve and methods of implantation |
-
2002
- 2002-04-03 US US10/115,552 patent/US7007698B2/en not_active Expired - Fee Related
-
2003
- 2003-04-03 CA CA002480876A patent/CA2480876A1/en not_active Abandoned
- 2003-04-03 EP EP03746114A patent/EP1489997A1/en not_active Withdrawn
- 2003-04-03 WO PCT/US2003/010165 patent/WO2003084442A1/en active Application Filing
- 2003-04-03 AU AU2003226217A patent/AU2003226217A1/en not_active Abandoned
- 2003-04-03 JP JP2003581687A patent/JP4388821B2/en not_active Expired - Fee Related
-
2005
- 2005-12-07 US US11/296,590 patent/US20060085066A1/en not_active Abandoned
Patent Citations (99)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3716058A (en) * | 1970-07-17 | 1973-02-13 | Atlanta Res Inst | Barbed suture |
US4904254A (en) * | 1986-07-17 | 1990-02-27 | Vaso Products Australia Pty. Limited | Correction of incompetent venous valves |
US5601572A (en) * | 1989-08-16 | 1997-02-11 | Raychem Corporation | Device or apparatus for manipulating matter having a elastic ring clip |
US5002563A (en) * | 1990-02-22 | 1991-03-26 | Raychem Corporation | Sutures utilizing shape memory alloys |
US6673109B2 (en) * | 1993-11-01 | 2004-01-06 | 3F Therapeutics, Inc. | Replacement atrioventricular heart valve |
US20040030405A1 (en) * | 1994-07-29 | 2004-02-12 | Sophie Carpentier | Methods for treating implantable biological tissues to mitigate the calcification thereof and bioprosthetic articles treated by such methods |
US20060041305A1 (en) * | 1996-06-20 | 2006-02-23 | Karl-Lutz Lauterjung | Prosthetic repair of body passages |
US20040015230A1 (en) * | 1996-12-18 | 2004-01-22 | Moll Franciscus Laurens | Methods for regulating the flow of blood through the blood system |
US20060009842A1 (en) * | 1997-03-27 | 2006-01-12 | Huynh Van L | Contoured heart valve suture rings |
US6837902B2 (en) * | 1997-04-03 | 2005-01-04 | Edwards Lifesciences Corporation | Methods of making bioprosthetic heart valves with strain matched leaflets |
US20040002719A1 (en) * | 1997-06-27 | 2004-01-01 | Oz Mehmet C. | Method and apparatus for circulatory valve repair |
US20050004583A1 (en) * | 1997-06-27 | 2005-01-06 | Oz Mehmet C. | Method and apparatus for circulatory valve repair |
US6695866B1 (en) * | 1998-07-15 | 2004-02-24 | St. Jude Medical, Inc. | Mitral and tricuspid valve repair |
US6692512B2 (en) * | 1998-10-13 | 2004-02-17 | Edwards Lifesciences Corporation | Percutaneous filtration catheter for valve repair surgery and methods of use |
US20060013805A1 (en) * | 1998-11-24 | 2006-01-19 | Regents Of The University Of Minnesota | Transgenic circulating endothelial cells |
US6846324B2 (en) * | 1999-01-26 | 2005-01-25 | Edwards Lifesciences Corporation | Combination anatomical orifice sizer and heart valve |
US20050010285A1 (en) * | 1999-01-27 | 2005-01-13 | Lambrecht Gregory H. | Cardiac valve procedure methods and devices |
US20040003819A1 (en) * | 1999-04-09 | 2004-01-08 | Evalve, Inc. | Methods and apparatus for cardiac valve repair |
US20050021056A1 (en) * | 1999-04-09 | 2005-01-27 | Evalve, Inc. | Leaflet structuring |
US20050033446A1 (en) * | 1999-04-09 | 2005-02-10 | Evalve, Inc. A California Corporation | Methods and apparatus for cardiac valve repair |
US20020013571A1 (en) * | 1999-04-09 | 2002-01-31 | Evalve, Inc. | Methods and devices for capturing and fixing leaflets in valve repair |
US20040039442A1 (en) * | 1999-04-09 | 2004-02-26 | Evalve, Inc. | Methods and apparatus for cardiac valve repair |
US20040044350A1 (en) * | 1999-04-09 | 2004-03-04 | Evalve, Inc. | Steerable access sheath and methods of use |
US20060020275A1 (en) * | 1999-04-09 | 2006-01-26 | Evalve, Inc. | Locking mechanisms for fixation devices and methods of engaging tissue |
US20040030382A1 (en) * | 1999-04-09 | 2004-02-12 | Evalve, Inc. | Methods and apparatus for cardiac valve repair |
US20050043792A1 (en) * | 1999-06-29 | 2005-02-24 | Edwards Lifesciences Ag | Device and method for treatment of mitral insufficiency |
US6997951B2 (en) * | 1999-06-30 | 2006-02-14 | Edwards Lifesciences Ag | Method and device for treatment of mitral insufficiency |
US20040039443A1 (en) * | 1999-06-30 | 2004-02-26 | Solem Jan Otto | Method and device for treatment of mitral insufficiency |
US20020026216A1 (en) * | 1999-10-13 | 2002-02-28 | Grimes Randall Y. | Devices and methods for percutaneous mitral valve repair |
US6840957B2 (en) * | 1999-10-21 | 2005-01-11 | Scimed Life Systems, Inc. | Implantable prosthetic valve |
US6685739B2 (en) * | 1999-10-21 | 2004-02-03 | Scimed Life Systems, Inc. | Implantable prosthetic valve |
US20060000715A1 (en) * | 2000-01-25 | 2006-01-05 | Whitcher Forrest D | Manufacturing medical devices by vapor deposition |
US6682559B2 (en) * | 2000-01-27 | 2004-01-27 | 3F Therapeutics, Inc. | Prosthetic heart valve |
US20050015112A1 (en) * | 2000-01-27 | 2005-01-20 | Cohn William E. | Cardiac valve procedure methods and devices |
US6989028B2 (en) * | 2000-01-31 | 2006-01-24 | Edwards Lifesciences Ag | Medical system and method for remodeling an extravascular tissue structure |
US20040024447A1 (en) * | 2000-04-27 | 2004-02-05 | Axel Haverich | Individual venous valve prosthesis |
US6840246B2 (en) * | 2000-06-20 | 2005-01-11 | University Of Maryland, Baltimore | Apparatuses and methods for performing minimally invasive diagnostic and surgical procedures inside of a beating heart |
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 |
US20040030321A1 (en) * | 2000-07-11 | 2004-02-12 | Fangrow Thomas F. | Medical valve with positive flow characteristics |
US6846325B2 (en) * | 2000-09-07 | 2005-01-25 | Viacor, Inc. | Fixation band for affixing a prosthetic heart valve to tissue |
US20050010287A1 (en) * | 2000-09-20 | 2005-01-13 | Ample Medical, Inc. | Devices, systems, and methods for supplementing, repairing, or replacing a native heart valve leaflet |
US20040015233A1 (en) * | 2000-10-09 | 2004-01-22 | Josef Jansen | Cardiac valve prosthesis, especially mitral cardiac valve and method for producing the same |
US20060025856A1 (en) * | 2001-03-15 | 2006-02-02 | Medtronic, Inc. | Annuloplasty band and method |
US20040019378A1 (en) * | 2001-04-24 | 2004-01-29 | Hlavka Edwin J. | Method and apparatus for performing catheter-based annuloplasty |
US6682558B2 (en) * | 2001-05-10 | 2004-01-27 | 3F Therapeutics, Inc. | Delivery system for a stentless valve bioprosthesis |
US20050027351A1 (en) * | 2001-05-14 | 2005-02-03 | Cardiac Dimensions, Inc. A Washington Corporation | Mitral valve regurgitation treatment device and method |
US6676702B2 (en) * | 2001-05-14 | 2004-01-13 | Cardiac Dimensions, Inc. | Mitral valve therapy assembly and method |
US20050027353A1 (en) * | 2001-05-14 | 2005-02-03 | Alferness Clifton A. | Mitral valve therapy device, system and method |
US20050038507A1 (en) * | 2001-05-14 | 2005-02-17 | Alferness Clifton A. | Mitral valve therapy device, system and method |
US20050033419A1 (en) * | 2001-05-14 | 2005-02-10 | Alferness Clifton A. | Mitral valve therapy device, system and method |
US20040034380A1 (en) * | 2001-06-29 | 2004-02-19 | Woolfson Steven B. | Method and apparatus for resecting and replacing an aortic valve |
US20050043790A1 (en) * | 2001-07-04 | 2005-02-24 | Jacques Seguin | Kit enabling a prosthetic valve to be placed in a body enabling a prosthetic valve to be put into place in a duct in the body |
US20050033398A1 (en) * | 2001-07-31 | 2005-02-10 | Jacques Seguin | Assembly for setting a valve prosthesis in a corporeal duct |
US20030050694A1 (en) * | 2001-09-13 | 2003-03-13 | Jibin Yang | Methods and apparatuses for deploying minimally-invasive heart valves |
US20040039436A1 (en) * | 2001-10-11 | 2004-02-26 | Benjamin Spenser | Implantable prosthetic valve |
US20060020336A1 (en) * | 2001-10-23 | 2006-01-26 | Liddicoat John R | Automated annular plication for mitral valve repair |
US20040010305A1 (en) * | 2001-12-05 | 2004-01-15 | Cardiac Dimensions, Inc. | Device and method for modifying the shape of a body organ |
US20040024451A1 (en) * | 2002-01-02 | 2004-02-05 | Medtronic, Inc. | Prosthetic heart valve system |
US20060041306A1 (en) * | 2002-01-09 | 2006-02-23 | Myocor, Inc. | Devices and methods for heart valve treatment |
US20040019377A1 (en) * | 2002-01-14 | 2004-01-29 | Taylor Daniel C. | Method and apparatus for reducing mitral regurgitation |
US20060030882A1 (en) * | 2002-03-06 | 2006-02-09 | Adams John M | Transvenous staples, assembly and method for mitral valve repair |
US20050021136A1 (en) * | 2002-03-21 | 2005-01-27 | Hua Xie | Method for suturelessly attaching a biomaterial to an implantable bioprosthesis frame |
US20060030866A1 (en) * | 2002-03-26 | 2006-02-09 | Stefan Schreck | Sequential heart valve leaflet repair device and method of use |
US20040019374A1 (en) * | 2002-05-10 | 2004-01-29 | Hikmat Hojeibane | Frame based unidirectional flow prosthetic implant |
US20060025787A1 (en) * | 2002-06-13 | 2006-02-02 | Guided Delivery Systems, Inc. | Devices and methods for heart valve repair |
US20060025750A1 (en) * | 2002-06-13 | 2006-02-02 | Guided Delivery Systems, Inc. | Delivery devices and methods for heart valve repair |
US6986775B2 (en) * | 2002-06-13 | 2006-01-17 | Guided Delivery Systems, Inc. | Devices and methods for heart valve repair |
US6858039B2 (en) * | 2002-07-08 | 2005-02-22 | Edwards Lifesciences Corporation | Mitral valve annuloplasty ring having a posterior bow |
US20040030381A1 (en) * | 2002-07-16 | 2004-02-12 | Shu Mark C.S. | Heart valve prosthesis |
US20040015232A1 (en) * | 2002-07-16 | 2004-01-22 | Medtronic, Inc. | Suturing rings for implantable heart valve prosthesis |
US20040024452A1 (en) * | 2002-08-02 | 2004-02-05 | Kruse Steven D. | Valved prostheses with preformed tissue leaflets |
US20040034411A1 (en) * | 2002-08-16 | 2004-02-19 | Quijano Rodolfo C. | Percutaneously delivered heart valve and delivery means thereof |
US20060015136A1 (en) * | 2002-09-19 | 2006-01-19 | Memory Metal Holland Bv | Vascular filter with improved strength and flexibility |
US20060030885A1 (en) * | 2002-10-15 | 2006-02-09 | Hyde Gregory M | Apparatuses and methods for heart valve repair |
US20060036317A1 (en) * | 2002-11-12 | 2006-02-16 | Myocor, Inc. | Decives and methods for heart valve treatment |
US20050038506A1 (en) * | 2002-11-15 | 2005-02-17 | Webler William E. | Apparatuses and methods for heart valve repair |
US20060020335A1 (en) * | 2002-12-26 | 2006-01-26 | Leonard Kowalsky | System and method to effect the mitral valve annulus of a heart |
US6997950B2 (en) * | 2003-01-16 | 2006-02-14 | Chawla Surendra K | Valve repair device |
US6989027B2 (en) * | 2003-04-30 | 2006-01-24 | Medtronic Vascular Inc. | Percutaneously delivered temporary valve assembly |
US20060009841A1 (en) * | 2003-05-05 | 2006-01-12 | Rex Medical | Percutaneous aortic valve |
US20050004667A1 (en) * | 2003-06-05 | 2005-01-06 | Cardiac Dimensions, Inc. A Delaware Corporation | Device, system and method to affect the mitral valve annulus of a heart |
US20050027261A1 (en) * | 2003-07-30 | 2005-02-03 | Karla Weaver | Pressure actuated valve with improved slit configuration |
US20050027348A1 (en) * | 2003-07-31 | 2005-02-03 | Case Brian C. | Prosthetic valve devices and methods of making such devices |
US20060025784A1 (en) * | 2003-09-04 | 2006-02-02 | Guided Delivery Systems, Inc. | Delivery devices and methods for heart valve repair |
US7004176B2 (en) * | 2003-10-17 | 2006-02-28 | Edwards Lifesciences Ag | Heart valve leaflet locator |
US20060013855A1 (en) * | 2004-04-05 | 2006-01-19 | Medivas, Llc | Bioactive stents for type II diabetics and methods for use thereof |
US20060025857A1 (en) * | 2004-04-23 | 2006-02-02 | Bjarne Bergheim | Implantable prosthetic valve |
US20060025855A1 (en) * | 2004-05-05 | 2006-02-02 | Lashinski Randall T | Translumenally implantable heart valve with multiple chamber formed in place support |
US20060025854A1 (en) * | 2004-05-05 | 2006-02-02 | Lashinski Randall T | Translumenally implantable heart valve with formed in place support |
US20060020334A1 (en) * | 2004-05-05 | 2006-01-26 | Lashinski Randall T | Methods of cardiac valve replacement using nonstented prosthetic valve |
US20060020332A1 (en) * | 2004-05-05 | 2006-01-26 | Lashinski Randall T | Nonstented temporary valve for cardiovascular therapy |
US20060020327A1 (en) * | 2004-05-05 | 2006-01-26 | Lashinski Randall T | Nonstented heart valves with formed in situ support |
US20060004442A1 (en) * | 2004-06-30 | 2006-01-05 | Benjamin Spenser | Paravalvular leak detection, sealing, and prevention |
US20060004439A1 (en) * | 2004-06-30 | 2006-01-05 | Benjamin Spenser | Device and method for assisting in the implantation of a prosthetic valve |
US20060030747A1 (en) * | 2004-07-09 | 2006-02-09 | Kantrowitz Allen B | Synchronization system between aortic valve and cardiac assist device |
US20060009804A1 (en) * | 2004-07-12 | 2006-01-12 | Pederson Brian D | Anti-coagulation and demineralization system for conductive medical devices |
US20060015178A1 (en) * | 2004-07-15 | 2006-01-19 | Shahram Moaddeb | Implants and methods for reshaping heart valves |
US20060015179A1 (en) * | 2004-07-19 | 2006-01-19 | Neil Bulman-Fleming | Aortic annuloplasty ring |
Also Published As
Publication number | Publication date |
---|---|
CA2480876A1 (en) | 2003-10-16 |
WO2003084442A1 (en) | 2003-10-16 |
JP4388821B2 (en) | 2009-12-24 |
AU2003226217A1 (en) | 2003-10-20 |
EP1489997A1 (en) | 2004-12-29 |
US7007698B2 (en) | 2006-03-07 |
JP2005521515A (en) | 2005-07-21 |
US20030191479A1 (en) | 2003-10-09 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US7007698B2 (en) | Body lumen closure | |
US11564818B2 (en) | Vascular implant | |
AU723785B2 (en) | Methods and apparatus for connecting openings formed in adjacent blood vessels or other anatomical structures | |
US10376364B2 (en) | Implant delivery capsule | |
US6425915B1 (en) | Helical mesh endoprosthesis and methods of use | |
US5824053A (en) | Helical mesh endoprosthesis and methods of use | |
US20180043133A1 (en) | Expandable sheath and methods of use | |
US5836965A (en) | Stent delivery and deployment method | |
US6660032B2 (en) | Expandable coil endoluminal prosthesis | |
EP1653882B1 (en) | Clutch driven stent delivery system | |
US6488700B2 (en) | Endoluminal prosthesis placing method | |
US20010047150A1 (en) | Delivery system and method for expandable intracorporeal device | |
US20080114391A1 (en) | Aneurysm covering devices and delivery devices | |
US10932932B2 (en) | Delivery device with an expandable positioner for positioning a prosthesis | |
JP7150920B2 (en) | Stent graft device having anchor members with adjustable geometry | |
US20070173924A1 (en) | Axially-elongating stent and method of deployment | |
US8784439B1 (en) | Percutaneous medical procedures and devices for closing vessels using mechanical closures | |
US20170105857A1 (en) | Retrieval of medical devices | |
WO2008148385A1 (en) | A stent |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION |