US20050177180A1 - Devices, systems, and methods for supporting tissue and/or structures within a hollow body organ - Google Patents

Devices, systems, and methods for supporting tissue and/or structures within a hollow body organ Download PDF

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Publication number
US20050177180A1
US20050177180A1 US10808216 US80821604A US2005177180A1 US 20050177180 A1 US20050177180 A1 US 20050177180A1 US 10808216 US10808216 US 10808216 US 80821604 A US80821604 A US 80821604A US 2005177180 A1 US2005177180 A1 US 2005177180A1
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Prior art keywords
tissue
hollow body
body organ
system
prosthesis
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Abandoned
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US10808216
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Alan Kaganov
Lee Bolduc
Andrew Chiang
Philip Houle
Gilbert Laroya
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Aptus Endosystems Inc
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Aptus Endosystems Inc
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Abstract

Devices, systems and methods support tissue in a body organ for the purpose of restoring or maintaining native function of the organ. The devices, systems, and methods do not require invasive, open surgical approaches to be implemented, but, instead, lend themselves to catheter-based, intra-vascular and/or percutaneous techniques.

Description

    RELATED APPLICATIONS
  • This application claims the benefit of co-pending U.S. patent application Ser. No. 10/307,226, filed Nov. 29, 2002, which claims the benefit of co-pending U.S. Provisional Application Ser. No. 60/333,937 filed 28 Nov. 2001. This application also claims the benefit of co-pending U.S. patent application Ser. No. 10/271,334, filed Oct. 15, 2002.
  • FIELD OF THE INVENTION
  • The features of the invention are generally applicable to devices, systems, and methods that support tissue and/or structures within a hollow body organ. In a more particular sense, the features of the invention are applicable to improving heart function by supporting tissue and related structures in the heart, e.g., for the treatment of conditions such as congestive heart failure and/or heart valve dysfunction and/or atrial fibrillation and/or septal defects.
  • BACKGROUND OF THE INVENTION
  • Hollow body organs are shaped in particular native ways to perform specific native functions. When a body organ looses its native shape due to disease, injury, or simply the natural aging process, the native functions can be adversely affected. The heart serves as a good example of this marriage between native shape and native function, as well as the dysfunctions that can occur should the native shape change.
  • I. The Anatomy of a Healthy Heart
  • The heart (see FIG. 1) is slightly larger than a clenched fist. It is a double (left and right side), self-adjusting muscular pump, the parts of which work in unison to propel blood to all parts of the body. The right side of the heart receives poorly oxygenated (“venous”) blood from the body from the superior vena cava and inferior vena cava and pumps it through the pulmonary artery to the lungs for oxygenation. The left side receives well-oxygenation (“arterial”) blood from the lungs through the pulmonary veins and pumps it into the aorta for distribution to the body.
  • The heart has four chambers, two on each side—the right and left atria, and the right and left ventricles. The atria are the blood-receiving chambers, which pump blood into the ventricles. A wall composed of membranous and muscular parts, called the interatrial septum, separates the right and left atria. The ventricles are the blood-discharging chambers. A wall composed of membranous and muscular parts, called the interventricular septum, separates the right and left ventricles.
  • The synchronous pumping actions of the left and right sides of the heart constitute the cardiac cycle. The cycle begins with a period of ventricular relaxation, called ventricular diastole. The cycle ends with a period of ventricular contraction, called ventricular systole.
  • The heart has four valves (see FIGS. 2 and 3) that ensure that blood does not flow in the wrong direction during the cardiac cycle; that is, to ensure that the blood does not back flow from the ventricles into the corresponding atria, or back flow from the arteries into the corresponding ventricles. The valve between the left atrium and the left ventricle is the mitral valve. The valve between the right atrium and the right ventricle is the tricuspid valve. The pulmonary valve is at the opening of the pulmonary artery. The aortic valve is at the opening of the aorta.
  • At the beginning of ventricular diastole (i.e., ventricular filling) (see FIG. 2), the aortic and pulmonary valves are closed to prevent back flow from the arteries into the ventricles. Shortly thereafter, the tricuspid and mitral valves open (as FIG. 2 shows), to allow flow from the atria into the corresponding ventricles. Shortly after ventricular systole (i.e., ventricular emptying) begins, the tricuspid and mitral valves close (see FIG. 3)—to prevent back flow from the ventricles into the corresponding atria—and the aortic and pulmonary valves open—to permit discharge of blood into the arteries from the corresponding ventricles.
  • The heart valves are defined by fibrous rings of collagen, each called an annulus, which forms a part of the fibrous skeleton of the heart. The annulus provides attachments for the cusps or leaflets of the valves. In a healthy heart, muscles and their tendinous chords (chordae tendineae) support the valves, allowing the leaflets of the valves to open and close in accordance with their intended functions.
  • II. Heart Dysfunctions
  • Infection, myocardial infarction, atrial fibrillation, other diseases, or anatomic defects can adversely affect the normal synchronous pumping actions of the left and right sides of the heart and/or the operation of heart valves during the cardiac cycle.
  • For example, due to one or more of these causes, a heart chamber may become stretched and enlarged. This condition can lead to adverse consequences. For example, (1) due to its enlarged condition the heart must pump harder to move the blood, and/or too little blood may move from the heart to the rest of the body. Over time, other chambers of the heart may also become weaker. The stretching and enlargement of a heart chamber, e.g., in the left ventricle, can lead to a condition called congestive heart failure. If not treated, congestive heart failure can lead to pulmonary embolisms, circulatory shutdown, and death.
  • The enlargement of a heart chamber can also lead to the enlargement or stretching a heart valve annulus. Also, the stretching or tearing of the chords surrounding a heart valve, or other forms of muscle failure in this region, can also change the shape of a heart valve annulus, even when enlargement of a heart chamber is absent. When the heart valve annulus changes its shape, the valve leaflets can fail to coapt. An undesired back flow of blood can occur between an atrium and a ventricle (called regurgitation), or back flow between an artery and a ventricle can occur. Such dysfunctions can eventually also weaken the heart and can result in heart failure.
  • Anatomic defects, e.g., in the septum, can also lead to heart dysfunction. These defects can be congenital, or they can result from disease or injury.
  • III. Prior Treatment Modalities
  • Medications can be successful in treating heart dysfunctions. For chronic or acute dysfunction, however, surgery is often necessary. For congestive heart failure, a heart transplant may be required. Like invasive, open heart surgical approaches have been used to repair or replace a dysfunctional heart valves or to correct septal defects.
  • The need remains for simple, cost-effective, and less invasive devices, systems, and methods for treating heart conditions such as congestive heart failure and/or heart valve dysfunction and/or septal defects. A parallel need also remains for similarly treating other dysfunctions that arise from unintended shape changes in other body organs.
  • SUMMARY OF THE INVENTION
  • The invention provides devices, systems and methods that support tissue in a hollow body organ for the purpose of restoring or maintaining native function of the organ. The devices, systems, and methods do not require invasive, open surgical approaches to be implemented, but, instead, lend themselves to catheter-based, intra-vascular and/or percutaneous techniques.
  • One aspect of the invention provides systems and methods for supporting tissue within a hollow body organ. The systems and methods employ first and second implants that are coupled together. The first implant is sized and configured to penetrate a first region of tissue in the hollow body organ. The second implant is sized and configured to penetrate a second region of tissue in the hollow body organ spatially distinct from the first region. At least one tension element couples the first and second implants together, to apply tension to the first and second implants, and thereby draw tissue inward, supporting it. The supporting effect serves, e.g., to draw tissue surfaces together to reduce tissue volume within the hollow body organ, as well as resist subsequent enlargement of tissue volume. Desirably, the supporting effect does not interfere with contraction of the hollow body organ to a lesser tissue volume. However, if desired, this form of bracing can be achieved.
  • Another aspect of the invention provides systems and methods for forming a tissue fold within a hollow body organ. The systems and methods employ first and second implants. The implants are sized and configured to penetrate spatially distinct regions of tissue in the hollow body organ. At least one tension element couples the first and second implants together to apply tension on the first and second implants. The tension creates a tissue fold between the first and second implants. The tissue fold serves, e.g., to reduce internal tissue volume within the hollow body organ, as well as resist subsequent enlargement of tissue volume. Desirably, the tensioning does not interfere with contraction of the hollow body organ to a lesser tissue volume. However, if desired, this form of bracing can be achieved with tissue folding.
  • In one embodiment, the first and second implants are part of an array of implants that penetrates spatially distinct regions of tissue in the hollow body organ. In this embodiment, at least one tension element extends among the array of implants to apply tension between adjacent implants and thereby create a pattern of multiple tissue folds. The multiple tissue folds serve, e.g., to draw a circumferential region of tissue together, forming a closure or seal.
  • Another aspect of the invention provides systems and methods for supporting tissue in a hollow body organ. The systems and methods employ a prosthesis sized and configured for placement either within an interior of the hollow body organ or about an exterior of the hollow body organ to regulate a maximum size and/or shape of the hollow body organ. The systems and methods also employ at least one fastener to secure the prosthesis to tissue in the hollow body organ. In one embodiment, the fastener comprises a helical fastener.
  • Another aspect of the invention provides systems and methods for supporting tissue within a hollow body organ making use of an elongated implant. The elongated implant is sized and configured to penetrate tissue and extend along a curvilinear path within or partially within a tissue wall. The elongated implant regulates a maximum size and/or shape of the hollow body organ. In one embodiment, the elongated implant comprises a helical shape.
  • The systems and methods that embody all or some of the various aspects of the invention, as described, are well suited for use in, e.g., a heart. The systems and methods can be used to support tissue within a heart chamber and/or in or near a heart valve annulus in the treatment, e.g., of congestive heart failure or other conditions in which the volume of the heart becomes enlarged. The systems and methods can be used to seal or close perforations, holes, or defects in tissue. The systems and methods can be used to close or seal atrial appendages or septal defects.
  • Other features and advantages of the invention shall be apparent based upon the accompanying description, drawings, and claims.
  • DESCRIPTION OF THE DRAWINGS
  • FIG. 1 is a perspective, anterior anatomic view of the interior of a healthy heart.
  • FIG. 2 is a superior anatomic view of the interior of a healthy heart, with the atria removed, showing the condition of the heart valves during ventricular diastole.
  • FIG. 3 is a superior anatomic view of the interior of a healthy heart, with the atria removed, showing the condition of the heart valves during ventricular systole.
  • FIG. 4A is a perspective view of an implant for supporting tissue within a hollow body organ.
  • FIG. 4B is a side view of an applier instrument for implanting the implant shown in FIG. 4A in tissue.
  • FIG. 4C is a side view of the implant shown in FIG. 4A after implantation in tissue.
  • FIGS. 5A and 5B are tissue support systems established within a hollow body organ that comprises two or more of the implants as shown in FIG. 4A placed and maintained in tension by a clip element.
  • FIGS. 6A and 6B show the tissue supporting system shown in FIG. 5 established in a left ventricle of a heart, FIG. 6A showing the enlarged volume of the ventricle prior to establishment of the system, and FIG. 6B showing the system reducing the volume of ventricle.
  • FIGS. 7A to 7D show the steps in establishing the system shown in FIG. 6B by use of intra-vascular tools and techniques.
  • FIGS. 8A and 8B show a tissue supporting system like that shown in FIG. 5, established in a left ventricle of a heart in or near the annulus of the aortic valve, FIG. 8A showing the dilated condition of the aortic valve annulus prior to establishment of the system, and FIG. 8B showing the system reshaping the annulus to restore leafet coaption.
  • FIGS. 9A to 9D show the steps in establishing the system shown in FIG. 8B by use of intra-vascular tools and techniques.
  • FIGS. 10A and 10B show a tissue folding system established in a left ventricle of a heart, FIG. 10A showing the enlarged volume of the ventricle prior to establishment of the system, and FIG. 10B showing the system reducing the volume of ventricle.
  • FIGS. 11A to 11D show the steps in establishing the system shown in FIG. 10B by use of intra-vascular tools and techniques.
  • FIG. 12 shows another embodiment of a tissue folding system possessing the features of the system shown in FIG. 10B.
  • FIGS. 13A to 13C show the steps in establishing, by use of intra-vascular tools and techniques, another embodiment of a tissue folding system possessing the features of the system shown in FIG. 10B.
  • FIGS. 14A and 14B show the steps in establishing, by use of intra-vascular tools and techniques, another embodiment of a tissue folding system possessing the features of the system shown in FIG. 10B.
  • FIG. 15A is a tissue folding system as shown in FIG. 10B, with the including of an overlaying patch component that is secured by fasteners over the tissue fold established by the tissue folding system.
  • FIG. 15B is a catheter that deploys the patch component shown in FIG. 15A by intra-vascular access.
  • FIG. 16A shows the establishment of a system that creates a pattern of folds in a hollow body organ to isolate or seal one region of the hollow body organ from another region of the hollow body organ.
  • FIG. 16B is a plane view of the pattern of folds created by the system shown in FIG. 16A, taken generally along line 16B-16B in FIG. 16A.
  • FIGS. 17A and 17B show the establishment of a pattern of multiple folds in the region between an atrial appendage and an atrial septum using the system shown in FIGS. 16A and 16B, FIG. 17A showing the atrium prior to establishment of the system, and FIG. 17B showing the atrium after establishment of the system to isolate and/or seal the atrial appendage from the atrial septum.
  • FIG. 17C is a plane view of the pattern of folds created by the system shown in FIG. 17B, taken generally along line 17C-17C in FIG. 17B.
  • FIGS. 18A and 18B show the establishment of a pattern of multiple folds to seal a perforation in a hollow body organ using the system shown in FIGS. 16A and 16B, FIG. 18A showing the perforation prior to establishment of the system, and FIG. 18B showing the closing of the perforation after establishment of the system.
  • FIGS. 19A to 19F show various embodiments of a prothesis that can be installed in a hollow body organ to shape the organ and prevent its enlargement.
  • FIG. 20A shows a prosthesis of a type shown in FIGS. 19A to 19F installed in the interior of a hollow body organ.
  • FIG. 20B shows a prosthesis of a type shown in FIGS. 19A to 19F installed about the exterior of a hollow body organ.
  • FIG. 21A shows a prosthesis of a type shown in FIGS. 19A to 19F installed in the interior of a heart chamber.
  • FIGS. 22A to 22D show the steps in establishing, by use of intra-vascular tools and techniques, the prosthesis shown in FIG. 20A.
  • FIG. 23 shows a prosthesis of a type shown in FIGS. 19A to 19F installed about the exterior of a heart.
  • FIGS. 24A and 24B show a composite prosthesis having the features of the prosthesis shown in FIGS. 19A to 19F, being formed by an array of two or more patch components installed in a left ventricle of a heart.
  • FIG. 25 shows a prosthesis having the features of the prosthesis shown in FIGS. 19A to 19F, being formed in the form of a ring for placement in or near a heart valve annulus.
  • FIG. 26A shows a prosthesis as shown in FIG. 25 installed in or near an annulus of an aortic valve.
  • FIG. 26B shows a prosthesis as shown in FIG. 25 installed in or near an annulus of a mitral valve.
  • FIG. 27 is a catheter that deploys the prosthesis shown in FIG. 25 by intra-vascular access.
  • FIG. 28 shows a patch component having the features of the patch component shown in FIG. 15A, being sized and configured for repairing a septal defect in a heart.
  • FIGS. 29A and 29B show the patch component shown in FIG. 28 installed in a septal defect between the left and right ventricles of heart.
  • FIGS. 30A and 30B show various embodiments of an elongated implant that can be implanted in a hollow body organ to shape the organ and prevent its enlargement, FIG. 30A showing an implant having a generally linear shape, and FIG. 30B showing an implant having a generally curvilinear shape.
  • FIG. 31 shows the elongated implant shown in FIGS. 30A and 30B implanted in a left ventricle of a heart.
  • FIG. 32 shows a heart valve assembly having many of the features of the prosthesis shown in FIGS. 19A to 19F, being formed for placement in or near a heart valve annulus.
  • FIG. 33 shows an assembly as shown in FIG. 32 installed in or near an annulus of an aortic valve.
  • FIGS. 34A to 34C show the steps in installing, by use of intra-vascular tools and techniques, the heart valve assembly shown in FIG. 32 in or near an annulus of an aortic valve.
  • DETAILED DESCRIPTION
  • Although the disclosure hereof is detailed and exact to enable those skilled in the art to practice the invention, the physical embodiments herein disclosed merely exemplify the invention, which may be embodied in other specific structure. While the preferred embodiment has been described, the details may be changed without departing from the invention, which is defined by the claims.
  • The technology disclosed in this specification is divided for clarity of presentation into sections, as follows:
      • I. Implants for Externally Supporting Tissue in a Hollow Body Organ
        • A. Overview
        • B. Systems and Methods for Supporting Tissue in a Heart Chamber
        • C. Systems and Methods to Support Tissue In or Near a Heart Valve Annulus
      • II. Implants for Creating Tissue Folds
        • A. Overview
        • B. Systems and Methods Defining Discrete Tissue Folds
          • 1. Tissue Folding with Overlaying Patch Component
        • C. Systems and Methods Defining Patterns of Tissue Folds
          • 1. Overview
          • 2. Appendage Isolation and Sealing
          • 3. Closing Perforations, Holes, or Defects
      • III. Prostheses for Externally Supporting Tissue in a Hollow Body Organ
        • A. Overview
        • B. Systems and Methods for Supporting Tissue in a Heart Chamber
        • C. Systems and Methods for Supporting Tissue In or Near a Heart Valve Annulus
      • IV. Implants for Internally Supporting Tissue in a Hollow Body Organ
  • It should be appreciated that the technology described in a given section can be combined with technology described in another section, and that there are features that are common to all technology described herein.
  • I. Implants for Externally Supporting Tissue in a Hollow Body Organ
  • A. Overview
  • FIG. 4A shows an implant 10 sized and configured for placement in a hollow body organ. The implant includes a body 12 that can be made from a formed plastic or metal or ceramic material suited for implantation in the body.
  • The body 12 includes a distal region 14. The distal region 14 is sized and configured to penetrate tissue. The body 12 and its distal region 14 are sized and configured to take purchase in tissue (see FIG. 4C) sufficient to significantly resist release and/or migration of the body 12 from tissue, once implanted.
  • The body 12 also includes a proximal region 16. The proximal region 16 is sized and configured to engage an instrument or tool 20 (see FIG. 4B) that applies a force to cause the implant 10 to penetrate tissue.
  • As shown in FIG. 4A, the body 12 also includes a tether element 18. In the illustrated embodiment, the tether element 18 is carried on or near the proximal region 16 of the body 12. By virtue of this, when the body 12 is implanted in a tissue wall in a vessel or hollow body organ (see FIG. 4C), the tether element 16 extends outside the tissue wall.
  • The tether element 18 comprises a thread, braid, wire, or tube structure with a metallic or polymer material (e.g., polyester suture) having a break strength that is desirably at least equal to the resistance the distal region 14 of the body 12 has to release or migration from tissue. The tether element 18 is desirably flexible, to enable its deployment through an intra-vascular path. The tether element 18 is desirably not significantly elastic, but it can be, depending upon the tissue conditions encountered.
  • The tether element 18 is securely fastened to the proximal region 16, e.g., by soldering, gluing, riveting, or like attachment techniques. The junction between the tether element 18 and the body 12 desirably has a material strength that is greater than the material strength of the tether element 18 itself.
  • The body 12 of the implant 10 can take various forms. In the illustrated embodiment (as FIG. 4A shows), the body 12 comprises an open helical coil. In the arrangement, the distal region 14 comprises a sharpened leading tip. This type of body 12 and distal region 14 can be deployed into tissue by rotational movement, which the applier instrument 20 imparts to the implant 10.
  • Also, in the illustrated embodiment (as FIG. 4A shows), the proximal region 16 comprises an L-shaped leg. The L-shape leg desirably bisects the entire interior diameter of the coil body 12; that is, the L-shaped leg 16 extends completely across the interior diameter of the coil body 12. The L-shaped leg 16 serves as a stop to prevent the coil body 12, when rotated, from penetrating too far into tissue. Furthermore, as FIG. 4B generally shows, a rotatable implant drive mechanism 22 on the applier instrument 20 is sized and configured to engage the L-shaped leg 16 and impart rotation to the coil body 12 to achieve implantation in tissue.
  • FIGS. 5A and 5B show a tissue shaping system 24 comprising at least two implants 10 shown in FIG. 4A. The implants 10 are implanted in a tissue wall within a hollow body organ or vessel (shown generically in FIGS. 5A and 5B) in a spaced-apart relationship or pattern. The number of tethered implants 10 deployed can vary according to the size and geometry of the targeted tissue volume, as well as the tissue support objectives.
  • The system 24 includes at least one clip element 26 joined to the tether elements 18 of the implants 10. FIG. 5A shows a single clip element 26. FIG. 5B shows multiple clip elements 26. The clip element or elements 26 mutually couple the tether elements 18 together, and allow tension to be applied and maintained external to the tissue, as the arrows in FIGS. 5A and 5B show. The tension individually applied and maintained by each tether element 18 on its respective implant 10, in combination, draws the surrounding tissue wall en masse inward toward the clip element 26, to shape the hollow body organ or vessel. Conversely, the tension applied and maintained by the tether elements 18 on each implant 10, in combination, resists movement of the tissue wall en masse outward away from the clip element 26. The tension prevents distension of tissue wall beyond the volume created by the tissue support system 24. The tissue support system 24, however, desirably does not interfere with contraction of the tissue wall toward a lesser volume.
  • The length of each individual tether element 18 and the magnitude of the tension it applies to its respective implant 10 collectively dictate a maximum shape for the body organ. In this way, the system 24 supports and shapes tissue in a body organ.
  • The system 24 as just described can be established in various parts of the body and for various therapeutic purposes. Two embodiments will be described for the purpose of illustration. The first embodiment is directed to the treatment and/or repair of congestive heart failure. The second embodiment is directed to heart valve remodeling.
  • B. Systems and Methods for Supporting Tissue in a Heart Chamber
  • FIG. 6A shows a heart afflicted with congestive heart failure. The condition shown in FIG. 6A is characterized by an enlarged internal volume of the left ventricle. FIG. 6B shows the treatment and/or repair of the condition by the implantation of a system 24 of tethered implants 10 within the left ventricle. The tethers 18 of the implants 10 are placed and held in tension (shown by arrows in FIG. 6B) by a clip 26. Multiple clips 26 could be used, if desired. The tension applied by the system 24 shapes the left ventricle, pulling the chamber walls laterally closer together and thereby reducing the overall maximum internal volume. The tension prevents or restricts expansion of the left ventricle beyond the shape during ventricular diastole, which is better suited to efficient ventricular pumping. The support system 24, however, does not interfere with normal contraction of the left ventricle during ventricular systole.
  • FIGS. 7A to 7D show the intra-vascular deployment of the system 24 shown in FIG. 6B. Alternatively, the system 24 can be established using conventional open heart surgical techniques or by thoracoscopic surgery techniques.
  • In the intra-vascular approach shown in FIGS. 7A to 7D, a guide component 28 is delivered over a guide wire (not shown) through the aortic valve into the left ventricle. The guide component 28 can be delivered through the vasculature under fluoroscopic guidance, e.g., through either a retrograde arterial route (via, e.g., the femoral artery or subclavian artery) (as shown) or an antegrade venous then trans-septal route.
  • The guide component 28 can comprise, e.g., a guide sheath that desirably has a steerable or deflectable distal tip. The guide wire can be withdrawn after the guide component 28 is deployed and positioned, so that the applier instrument 20 can be introduced through the guide component 28, as FIG. 7A shows. FIG. 4B also shows the deployment of the applier instrument 20 through the guide component 28.
  • In this arrangement (see FIG. 4B), the applier instrument 20 comprises a catheter 30 that carries an implant drive mechanism 22 on its distal tip. The drive mechanism 22 carries at least one tethered implant 10. An motor 32 in a handle 34, operated by the physician, drives the mechanism 22 to rotate the implant 10. As a result, the implant 10 is caused to penetrate the myocardium (as FIG. 7A shows).
  • The implantation force of the drive mechanism 22 is desirably resolved in some manner to provide positional stability and resist unintended movement of the drive mechanism 22 relative to the implantation site. A resolution force is desirably applied to counteract and/or oppose the implantation force of the drive mechanism 22. It is desirable to resolve some or all or a substantial portion of the implantation force within the vessel lumen (or other hollow body organ) itself, and preferably as close to the implantation site as possible.
  • The tubular body of the guide component 28 and/or the shaft of the applier instrument 20 can be sized and configured to possess sufficient column strength to resolve some or all or at least a portion of the implantation force within the vessel lumen or hollow body organ. FIG. 7A shows the guide component 28 braced against a wall of the ventricle to apply a counterbalancing resolution force. In addition, or alternatively, the guide component 28 and/or the aopplier instrument 20 can include some form of stabilization means for applying a counteracting force at or near the drive mechanism 22. Various types of stabilization means are disclosed in co-pending U.S. patent application Ser. No. 10/669,881, filed Sep. 24, 2003, and entitled “Catheter-Based Fastener Implantation Apparatus and Methods with Implantation Force Resolution.”
  • The guide component 28 is reposition in succession to other intended myocardial delivery sites. At each site, the applier instrument 20 is actuated to place an implant 10. In this way (see FIG. 7B), a desired spacing of implants 10 (such as a radial or spiral-like pattern) is distributed within the left ventricle.
  • Once the desired number of implants 10 are deployed inside the left ventricle, the applier instrument 20 is withdrawn from the guide component 28. The tether elements 18 of the implants 10 are left gathered and channeled through the guide component 28, as FIG. 7B shows.
  • As FIG. 7C shows, a clip-applier instrument 36 is tracked through the guide component 28 and over the bundle of tether elements 18 into the left ventricle. The tether elements 18 act as a composite guide wire to guide the clip-applier instrument 36 into the left ventricle.
  • Once in the left ventricle, the clip-applier instrument 36 is held stationary, while the tether elements are pulled taut through the clip-applier instrument 36 (shown by arrow T is FIG. 7C). As the individual tether elements 18 grow taut, they apply tension on the individual implants 10, as FIG. 7C shows. This, in turn, pulls the walls of the left ventricle inward towards the clip-applier instrument 26 (as a comparison of the left ventricle shown in FIG. 7B to the left ventricle shown in FIG. 7C demonstrates). Once a desired ventricular volume is achieved (as determined, e.g., through fluoroscopy), the clip-applier instrument 36 applies a clip 26 to the tether elements, attaching the tether elements 18 together in tension (see FIG. 7D). The clip-applier 36 cuts the bundle of tether elements 18 proximal to the site where the clip 26 was applied. The clip-applier instrument 36 and loose tethers 18 are then withdrawn from the left ventricle through the guide component 28, and the guide component is withdrawn, as FIG. 7D shows.
  • The system 24 has been established to support the left ventricle to treat, in this instance, congestive heart failure.
  • It should be appreciated that one or more implants 10 of the system 24 can be electrically coupled to a device that can be operated to control muscular and/or electrical activity in heart tissue. Absent this intended effect, however, it is desired that the implants 10 are not inherently electrically conductive, so as not to interfere with electrical conduction within the heart.
  • C. Systems and Methods to Support Tissue at or Near a Heart Valve Annulus
  • FIG. 8A shows a heart afflicted with congestive heart failure. As shown in FIG. 8A this condition has resulted in an enlarged internal volume of the left ventricle, leading to a dilation or stretching the aortic heart valve annulus. As a result, the aortic valve leaflets do not properly coapt during ventricular systole. An undesired retrograde flow of blood from the left ventricle into the aorta can occur during ventricular systole.
  • FIG. 8B shows the treatment and/or repair of this condition by the implantation of a system 24 of tethered implants 10 in the left ventricle near the aortic valve annulus. The tethers 18 of the fasteners are placed and held in tension (shown by arrows in FIG. 8B) by a clip 26. Multiple clips 26 can be used, if desired. The tension applied by the system 24 reshapes the aortic valve annulus, pulling the leaflets closer together, so that coaptation during ventricular systole occurs, and retrograde flow is prevented or reduced.
  • FIGS. 9A to 9D show the intra-vascular deployment of the system 24 shown in FIG. 8B. Alternatively, the system 24 can be established using conventional open heart surgical techniques or by thoracoscopic surgery techniques.
  • The intra-vascular approach shown in FIGS. 9A to 9D is the essentially the same as that shown in FIGS. 7A to 7D, previously described. Under fluoroscopic guidance, the guide component 28 is delivered over a guide wire through either the aortic valve (via, e.g., the femoral artery or subclavian artery) into the left ventricle at or near the inferior region of the aortic valve annulus or an antegrade venous then trans-septal route. The guide wire is withdrawn, and the applier instrument 20 is introduced through the guide component 28, as FIG. 9A shows.
  • The guide component 28 is positioned in succession at intended implant delivery sites at or near the inferior region of the aortic valve annulus. At each site, the applier instrument 20 is actuated to place an implant 10. FIG. 9A shows the guide component 28 braced against a wall of the ventricle to apply a counterbalancing resolution force to the implantation force. In this way (see FIG. 9B), a desired pattern of implants 10 is distributed at or near the inferior region of the aortic valve annulus. The tether elements of the implants 10 are gathered and channeled through the guide component 28 to outside the body.
  • Once the desired number of implants 10 are deployed at or near the aortic valve annulus, the applier instrument 20 is withdrawn, and the clip-applier instrument 36 is tracked through the guide component 28 and over the bundle of tether elements 18 into the left ventricle (see FIG. 9C). The tether elements 18 act as guide wires to guide the clip-applier instrument 36 into the left ventricle.
  • Once the clip-applier instrument 36 is in place, the tether elements 18 are pulled taut. Growing taut, the tether elements 18 apply tension on the individual implants 10, as the arrows in FIG. 9C show. This, in turn, pulls the walls of the left ventricle in the region of the aortic valve annulus inward towards the clip-applier instrument 36. The aortic valve leaflets are drawn closer together, into a geometry better suited for coaptation. The clip-applier instrument 36 applies a clip 26 to the tether elements 18, attaching the tether elements together in tension (see FIG. 9D). The clip-applier 36 cuts the bundle of tether elements 18 proximal to the site where the clip 26 was applied, and the clip-applier instrument 36 and loose tethers 18 are withdrawn. The guide component is then withdrawn, as FIG. 9D shows.
  • The system 24 has been established to reshape the aortic valve annulus to treat, in this instance, congestive heart failure and/or retrograde flow through the aortic valve. The system 24 can also be used to treat retrograde flow through any other heart valve, e.g., the mitral valve.
  • It should be appreciated that one or more implants 10 of the system 24 can be electrically coupled to a device that can be operated to control muscular and/or electrical activity in heart tissue. Absent this intended effect, however, it is desired that the implants 10 are not inherently electrically conductive, so as not to interfere with electrical conduction within the heart.
  • II. Implants for Creating Tissue Folds
  • A. Overview
  • FIG. 10B shows a tissue folding system 38 comprising at least one tethered implant 10 shown in FIG. 4A. The implant 10 is used in combination with another implant 40, which can take the form of the implant shown in FIG. 4B, but need not include a tether element 18. The implants 10 and 40 are implanted in a tissue wall within a hollow body organ or vessel (shown to be within a left ventricle in FIG. 10B) in a spaced-apart relationship. The tether element 18 of the implant 10 is cinched through the implant 40 and held in tension by a clip element 42, to form a fold or tuck 44 in the tissue region between the implants 10 and 40. The presence of the fold 44 reduces the overall interior volume of the hollow body organ or vessel, as a comparison of the left ventricle shown in FIG. 10A—before establishment of the tissue folding system 38—and the left ventricle shown in FIG. 10B—after establishment of the tissue folding system 38—demonstrates. The number of implants 10 and 40 and resulting folds 44 formed can vary according to the size and geometry of the targeted tissue volume, as well as the volume reduction objectives.
  • The tissue folding system 38 as just described can be established in various parts of the body and for various therapeutic purposes.
  • B. Systems and Methods Defining Discrete Tissue Folds
  • The embodiment shown in FIG. 10B contemplates the establishment of one or more discrete folds 44, e.g., for the treatment and/or repair of congestive heart failure. The tissue folding system 38 can be implemented in various ways.
  • FIGS. 11A to 11D contemplate the intra-vascular deployment of the system 38 in a left ventricle, as generally shown in FIG. 10B. Alternatively, the system 28 can be established using conventional open heart surgical techniques or by thoracoscopic surgery techniques. The system 38 can be deployed in other hollow body organs or vessels within the body, either by open surgical techniques or intra-vascular access.
  • In the intra-vascular approach into the left ventricle, as shown in FIGS. 11A to 11D, an applier instrument 20 can be introduced through a guide component 28 through either the aorta in the manner shown in FIG. 7A (via, e.g., the femoral artery or subclavian artery) or an antegrade venous then trans-septal route. The applier instrument 20 deploys at least one tethered implant 10 (as FIG. 11A shows). The applier instrument 20 is withdrawn to receive the implant 40, and then redeployed to an adjacent tissue region, using the tether element 18 of the first implant 10 as a guide wire as FIG. 11B shows. The tether element 18 of the implant 10 is slidably trapped or otherwise threaded through the implant 40 as the implant 40 is deployed, as FIG. 11B also shows. The applier instrument 20 is withdrawn from the guide component 28, with the tether element 18 of the implant 10 channeled through the guide component 28.
  • As FIG. 11C shows, a clip-applier instrument 36 is tracked through the guide component 28 and over the tether element 18 to the tissue site. The clip-applier instrument 36 is held stationary, while the tether element 18 is pulled taut through the clip-applier instrument 36 (see FIG. 11C). The tether element 18 applies tension between the implants 10 and 40, drawing the implants 10 and 40 together to cinch the intermediate tissue. The intermediate tissue folds it upon itself, and the fold 44 is created, as FIG. 11C shows. The clip-applier instrument 36 applies a clip element 42, to maintain tension and the resulting fold 44 (see FIG. 11D). The clip applier 36 cuts the tether element 18 proximal to the site where the clip 42 was applied. The clip-applier instrument 36 is then withdrawn through the guide component 28, and the guide component is withdrawn, as FIG. 11D shows.
  • Alternatively, or in combination with the clip element 42, the implants 10 and 40 can include interlocking structural components 46 (see FIG. 12) that are brought into engagement by pulling the tether element 18 taut. In an alternative embodiment (not shown), a separate bridging element can be applied to interlock elements 10 and 40 after they are brought into close proximity by pulling the tether element taut. The engagement between the components 46 that holds the relative positions of the implants 10 and 40, to maintain the tissue tension and the resulting fold 44. In this arrangement, the implant 40 can be partially installed and tension applied to the tether element 18 to draw the implants 10 and 40 toward one another, to create the desired fold 44. Then installation of the implant 40 can be completed to bring the components 46 into interlocking engagement.
  • As shown in FIGS. 13A to 13C, the spacing between the implants 10 and 40, after tension is applied to the tether element 18, can be controlled by use of a flexible, collapsible tube 48 between the implants 10 and 40. In this arrangement, the length of the tube 48, when collapsed, is predetermined to reflect the desired spacing between the implants 10 and 40 when in tension. As FIG. 13A shows, the tube 48 is guided in an uncollapsed condition over the tether element 18 after deployment of the implant 10. The implant 40 is deployed by the applier instrument 20 in the manner previously described, placing the tube 48 (uncollapsed) between the implants 10 and 40, as FIG. 13B shows. Subsequent use of the clip-applier instrument, as previously described, to draw the tether element 18 taut, collapses the tube 48 to until its predetermined length is assumed—resisting any further cinching—at which point the clip element 42 is applied, resulting in the system 38 shown in FIG. 13C. Alternatively, a non-collapsible tube could be used as a spacer between the two implants 10 and 40.
  • In the foregoing embodiments, a single tether element 18 has been used to apply tension between the implant 10 that carries the tether element 18 and another implant 40 that does not. Alternatively, as shown in FIGS. 14A and 14B, two implants 10, each with its own tether element 18 can be deployed. In this embodiment, the clip-applier instrument 36 is guided over both tether elements 18, so that tension can be applied individually to each tether element 18. The clip-applier instrument 36 draws the tether elements 18 taut (as FIG. 14B shows), creating the fold 44. The clip-applier instrument 36 then applies the clip element 42, to hold the two individual tether elements 18 in tension, forming the system 38.
  • In any of the foregoing manners, the system 38 can be established to reduce the interior volume of a heart chamber to treat, in this instance, a left ventricle affected by congestive heart failure.
  • The tether element(s) 18 may be elastic and/or possess a spring constant and/or be shaped and/or be otherwise compliant in the region between the implants 10 and 40. This material characteristic can help minimize or dampen peak load conditions upon the system 38, particularly when the tissue region is dynamic, as is the case with cardiac tissue.
  • 1. Tissue Folding with Overlaying Patch Component
  • As shown in FIG. 15A, the tissue folding system 38 can include a patch component 50 secured by implants 56 to span the tissue fold 44. The patch component 50 distributes forces within the system 28 to maintain the fold 44.
  • The patch component 50, when installed, comprises a relatively planar frame, or a sheet of prosthetic material, or combinations thereof. The patch material is selected on the basis of its biocompatibility, durability, and flexible mechanical properties. The patch material can comprise a polymeric or metallic material, e.g., polyester, or ePTFE, or a malleable plastic or metal material, or a self-expanding plastic or metal material like Nitinol® wire. The patch material desirably possesses some elasticity, e.g., by using stretchable materials and/or weaves/knits, like Spandex™ material or elastic waist bands. The patch material also desirably possesses a resistance to expansion. The material may be drug coated or embedded with drugs, such as with heparin.
  • The patch component 50 is desirable sized and configured to permit non-invasive deployment of the prosthesis by an intra-vascular catheter. In this respect, the patch component 50 is desirably sized and configured to assume a compressed or collapsed, low profile condition, to permit its intra-vascular introduction into the hollow body organ by a catheter. The patch component 50 is likewise desirably sized and configured for expansion in situ from a collapsed condition into an expanded condition for contact with tissue overlaying the fold 44.
  • The patch component 50 carry radiopaque markers to help fluoroscopically position it. The markers can take the form, e.g. of marker bands, tight wound coils, or wire made from radiopaque materials such as platinum, platinum/iridium, or gold.
  • FIG. 15B shows a representative embodiment for delivering the patch component 50 by a catheter 58 deployed through intra-vascular access. The catheter 58 carries the patch component 50 in a collapsed condition. Once positioned over the site of the fold 44, the patch component 50 is released from the end of catheter 58 on outwardly tapered guide elements 60.
  • The guide elements 60 comprise wires with eyes 62. In the illustrated embodiment, the eyes 62 are secured to the patch component 50 by releasable suture 64. The suture 64 can, e.g., comprise a loop that is threaded through each eye 62 and the patch component 50. The ends of the suture loop extend out the proximal end of the catheter 58. Pulling on one end of the suture loop will withdraw the suture 64 from the eyes 62, thereby releasing the patch component 50.
  • The guide elements 60 (and/or the patch component 50 itself) are desirably biased to hold the patch component 50, once released, in an open and taut fashion, as FIG. 15B shows. The patch component 50 placed over the fold 44. The periphery of the patch component 50 is attached to tissue using the fasteners 56. As FIG. 15B shows, the applier instrument 20, previously described, may be deployed over the guide elements 60 to apply the fasteners 56 to the patch component 50. Alternatively, the applier instrument 29 may be deployed independent of the guide elements 60.
  • It should be appreciated that one or more implants 10 and/or 40 of the system 38, or the implants 56 associated with the patch component 50, can be electrically coupled to a device that can be operated to control muscular and/or electrical activity in heart tissue. Absent this intended effect, however, it is desired that the implants 10 and/or 40, or the patch component 50 are not inherently electrically conductive, so as not to interfere with electrical conduction within the heart.
  • C. Systems and Methods Defining Patterns of Tissue Folds
  • 1. Overview
  • As FIGS. 16A and 16B show, a tissue folding system 52 can comprise a plurality of folds 44 arranged in a pre-established pattern or array within a hollow body organ. The folds 44 are arranged in an annular pattern about the circumference of a tissue region. The folds 44 are formed by placement of at least one tethered implant 10 (as shown in FIG. 4A) in association with a plurality of other implants 40 (which need not be tethered). The tether element 18 cinches tissue between adjacent implants, and a clip element 54 holds tension in the tether element 18. As FIG. 16A shows, the resulting pattern of adjacent folds 44 creates a tissue region that is circumferentially drawn in, in purse string fashion. As FIG. 16B shows, the system 52 can be used to establish within a given hollow body organ a restriction that essentially isolates or seals one region of a hollow body from another region.
  • The system 52 as just described can be established in various parts of the body and for various therapeutic purposes. Two embodiments will be described for the purpose of illustration. The first embodiment is directed to isolation or sealing of an atrial appendage in the treatment of, e.g., atrial fibrillation. The second embodiment is directed to the repair of perforations, holes, or defects in tissue, e.g., atrial or ventricular septal defects.
  • 2. Appendage Isolation/Sealing
  • FIG. 17A shows for the purpose of illustration the two native anatomic parts of an atrium (here, the left atrium)—namely, the atrial appendage (also call the appendix auricilae) and the remainder of the atrium (also called the sinus). FIG. 17B shows a tissue folding system 52 that has been established within the atrium. The system 52 comprises a plurality of annular folds 44 (see FIG. 17C), which essentially isolates or seals the left atrial appendage from the atrial septum. In this arrangement, the system 52 can be used, e.g., to prevent the formation of blood stasis regions in an atrial appendage that is subject to dysfunction as a result of decreased contractility of the atrium following, e.g., treatment of atrial fibrillation.
  • As shown in FIGS. 17B and 17C, the system 52 comprises at least one tethered implant 10 used in association with a plurality of other implants 40 (which need not be tethered). The implants 10 and 40 are implanted at or near the relatively restricted, native junction between the atrial appendage and the atrial sinus. The implants 10 and 40 are implanted in a spaced-apart, annular relationship about the circumference of this junction.
  • The tether element 18 of the implant 10 is cinched through an adjacent implant 40, which, in turn, is cinched through the next adjacent implant 40, and so on. The cinching between adjacent implants creates a fold 44. The cinching between a sequence of adjacent annular implants creates a pattern of adjacent, folds 44 about the native junction.
  • The tether element 18—cinched sequentially about the implants 10 and 40—is held in tension by a clip element 54. The system 52 draws the junction together, thereby essentially closing the atrial appendage from blood flow communication with the remainder of the atrium. The number and pattern of implants 10 and 40 in the system 52 can vary according to the size and geometry of the targeted junction sought to be isolated and sealed.
  • The system 52 can be deployed to seal or otherwise isolate an atrial appendage, either by open surgical techniques or intra-vascular access, using the instruments and methodologies that have been previously described.
  • It should be appreciated that a patch component 50 like that shown in FIG. 15A could be deployed over a pattern of folds 44 formed by the system 52. It should also be appreciated that one or more implants 10 and/or 40 of the system 52 can be electrically coupled to a device that can be operated to control muscular and/or electrical activity in heart tissue. Absent this intended effect, however, it is desired that the implants 10 and/or 40 are not inherently electrically conductive, so as not to interfere with electrical conduction within the heart.
  • 3. Closing Perforations, Holes, or Defects
  • FIG. 18A shows for-the purpose of illustration a tissue region that has a perforation caused, e.g., by disease, injury, or genetic defect. FIG. 18B shows a tissue folding system 52 established at or near the perforation in the tissue region. The system 52 comprises a plurality of annular folds 44, which essentially draw tissue together in a purse-string effect to close the perforation. The system 52 can be used, e.g., to seal septal defects in the atrium or ventricle, or in other regions of the body where perforations, holes, or defects occur.
  • The system 52 shown in FIG. 18B is essentially the same as shown 52 in FIGS. 17B and 17C. The system 52 comprises at least one tethered implant 10 in association with a plurality of other implants 40. The implants 10 and 40 are implanted in a spaced-apart, circumferential relationship about the perforation. The tether element 18 of the implant 10 is cinched through an adjacent implant 40, which, in turn, is cinched through the next adjacent implant 40, and so on, creating a pattern of adjacent, folds 44 about the perforation. The tether element 18—cinched sequentially about the implants 10 and 40—is held in tension by a clip element 54. The system 52 draws tissue surrounding the perforation together, thereby closing it, or at least reducing its native diameter.
  • The number and pattern of implants 10 and 40 in the system 52 can vary according to the size and geometry of the targeted junction sought to be isolated and sealed. Furthermore, the system 52 can be deployed to seal a perforation, hole of defect in tissue either by open surgical techniques or intra-vascular access, using the instruments and methodologies previously described.
  • It should be appreciated that, given the dimensions of the perforation, hole, or defect, a discrete system 38 like that shown in FIGS. 10B could be used to draw tissue together in the region of the perforation, thereby repairing it. It should also be appreciated that a patch component 50 like that shown in FIG. 15A can be deployed over a tissue site repaired by the system 52 or 58.
  • In one embodiment (see FIG. 28), the patch component 50 can be sized and configured to cover a discrete perforation, such as a septal defect in the heart, without association with a tissue folding system 52 or 58. In this arrangement (see FIG. 28), the patch component 50 includes, e.g., a body portion 66 and a stem portion 68. The stem portion 68, in use, occupies the perforation, hole, or defect (e.g., as shown in FIGS. 29A and 29B), to plug the site. The body portion 66 extends like “wings” from the stem portion 68 to contact and seat against wall tissue adjacent the site.
  • FIGS. 29A and 29B show the patch component 50 shown in FIG. 28 installed to cover a septal defect between the left and right ventricles of a heart. As FIGS. 29A and 29B show, fasteners 56 are desirably applied to anchor the body portion 66 to adjacent wall tissue. The patch component 50 shown in FIGS. 29A and 29B can be deployed to seal a perforation, hole of defect in tissue either by open surgical techniques or intra-vascular access, using the instruments and methodologies previously described.
  • In the foregoing indications in the heart, it is desired that the implants 10 and/or 40, and the patch component 50 and its associated fasteners 56, are not inherently electrically conductive, so as not to interfere with electrical conduction within the heart.
  • III. Prostheses for Externally Supporting Tissue in a Hollow Body Organ
  • A Overview
  • FIGS. 19A to 19F show various illustrative embodiments of a prosthesis 70 that is sized and configured for placement within an interior of a hollow body organ or around the exterior of a hollow body organ (see, e.g., FIGS. 20A and 20B, respectively). The prosthesis 70 has a body 72 that is preformed in a desired size and shape based upon the anatomy and morphology of the hollow body organ. When placed in or around a hollow body organ, the size and shape of the prosthesis body 72 constrains tissue, to regulate the maximum size and shape of the hollow body organ in a way that achieves a desired therapeutic result. However, the prosthesis body 72 desirably does not interfere with contraction of the hollow body organ to a lesser size and shape.
  • The body 72 can comprise a fully formed, three dimensional structure, as FIGS. 19A to 19D show. Alternatively, the body 72 can comprise component parts (A, B, C), as FIG. 19E shows, that are assembled in situ to form a composite body structure. The component parts A, B, and C may be assembled end-to-end in an adjacent relationship, or the component parts A, B, and C can be assembled in an overlapping relationship. In FIG. 19E, the component parts A, B, C comprise hoops, bowls, or truncated cylinders, which are assembled axially. Alternatively, as will be described in greater detail later, the components could comprise patch components (like that shown in FIG. 15A) that are assembled together, either end-to-end or in an overlaying relationship. Still alternatively, the body 72 can comprise a sheet-like structure, as shown in FIG. 19F, that is wrapped in situ to form a composite, three dimensional body structure. The body 72 could also include components that are coupled together with interconnecting hinges or springs. It should be appreciated that a multitude of structural configurations are possible.
  • In the illustrated embodiments, the body 72 is shown to include a prosthetic material 74. The prosthetic material 14 is selected on the basis of its biocompatibility, durability, and flexible mechanical properties. The material 74 can comprise, e.g., woven polyester or ePTFE. The prosthetic material 74 desirably possesses some elasticity, e.g., by using stretchable materials and/or weaves/knits, like Spandex™ material or elastic waist bands. The prosthetic material 74 also desirably possesses limited expansion or a resistance to expansion that can increase rapidly. The prosthetic material 74 may be drug coated or embedded with drugs on the inside surface, such as with heparin. Alternatively, the prosthetic material 74 may be relatively non-compliant, but can be compressed along with the rest of the prosthesis by crumpling, folding, etc. The prosthetic material 74 could also comprise a polymeric or metallic grid structure.
  • In the illustrated embodiments, the prosthetic material 74 is shown to be supported by a scaffold-like structure 76. It should be appreciated, however, that the prosthetic material 74 could be free of a scaffold-like structure 76, or, conversely, the scaffold-like structure 76 could be free of a prosthetic material 74.
  • The prosthetic material 74 and/or scaffold-like structure 76 are desirable sized and configured to permit non-invasive deployment of the prosthesis by an intra-vascular catheter. With this criteria in mind, the prosthetic material 74 and/or scaffold-like structure 76 are sized and configured to assume a compressed or collapsed, low profile condition, to permit their intra-vascular introduction into the hollow body organ by a catheter. Also with this criteria in mind, the prosthetic material 74 and/or scaffold-like structure 76 are sized and configured for expansion in situ from a collapsed condition into an expanded condition in contact with tissue in the targeted region.
  • In this respect, the scaffold-like structure 76, if present, can comprise, e.g., a malleable plastic or metal material that expands in the presence of an applied force. In this arrangement, the deployment catheter can include, e.g., an expandable body, such as a balloon, to apply the expansion force to the scaffold-like structure 76 in situ. Alternatively, the scaffold-like structure 76, if present, can comprise a self-expanding plastic or metal material (e.g., from Nitinol® wire) that can be compressed in the presence of a force, but self-expands upon removal of the compressive force. In this arrangement, the deployment catheter can include, e.g., a sleeve that can be manipulated to enclosed the scaffold-like structure 76 in a collapsed condition, thereby applying the compressive force, and to release the scaffold-like structure 76 when desired to allow the scaffold-like structure 76 to self-expand in situ.
  • The scaffold-like structure 76 can take various alternative forms, some of which are shown for the purpose of illustration. The scaffold-like structure 76 can include longitudinally extending spines, which form an umbrella-like structure shown in FIG. 19A. Alternatively, the scaffold-like structure 76 can comprise zigzag type stent rings (FIG. 19B), which can be independent or interconnected one with the other, or combinations thereof; or a helically wound stent support (FIG. 19C); or a woven or crisscrossing pattern. The scaffold-like structure 76 need not be present throughout the body 72; that is, the body 72 may include regions that include a scaffold-like structure 76 and regions that do not. The scaffold-like structure 76 can be, e.g., sewn onto prosthetic material 74. Other attachment means could be utilized to secure the scaffold-like structure 76 to the prosthetic material 74. These means include bonding; capturing the scaffold-like structure 76 between two layers of prosthetic material 74; and incorporating the scaffold-like structure 76 directly into the prosthetic material 74. The scaffold-like structure 76 can be present either inside the prosthesis body 72, or outside the prosthesis body 72, or within the prosthesis body 72, or combinations thereof. Desirably, the surface of the prosthesis 70 that is exposed to flow of blood or body fluids is relatively smooth to minimize turbulence.
  • The prosthesis body 72 can carry radiopaque markers to help fluoroscopically position the prosthesis. The markers can take the form, e.g. of marker bands, tight wound coils, or wire made from radiopaque materials such as platinum, platinum/iridium, or gold.
  • FIGS. 20A and 20B show the prosthesis 70 installed within a targeted hollow body organ (FIG. 20A) or about a targeted hollow body organ (FIG. 20B). At least part of the outer surface(s) of prosthesis can be coated with substances, such as glue or drugs, or structures, such as barbs or hooks, to promote adhesion or connection to the hollow body organ.
  • The structural strength of the prosthesis 70 resists distension of the tissue wall en masse beyond the maximum size and shaped imposed by the prosthesis body 72. In this way, the prosthesis body 72 dictates a maximum size and shape for the body organ. However, the prosthesis body 72 does not interfere with the contraction of the hollow body organ to a lesser size and shape.
  • Desirably, as FIGS. 20A and 20B show, the prosthesis body 72 accommodates the introduction of one or more fasteners 56 to anchor the prosthesis 70 in place. For this purpose, regions of the prosthesis body 72 can be specially sized and configured for the receipt and retention of fasteners. For example, the size and spacing of the scaffold-like structure 76 can be configured in the regions to specially accommodate the placement of fasteners 56; and/or woven fibers with an “X-pattern” or a “sinusoidal pattern” can be used in the region to specially accommodate placement of fasteners 56; and/or the prosthetic material can be folded-over to form multiple layers, to reinforce the prosthesis in the regions where fasteners 56 are placed; and/or denser weave patterns or stronger fibers can be used, selected from, e.g., Kevlar™ material or Vectran™ material or metallic wire woven alone or interwoven with typical polyester fibers in the regions were fasteners 56 are placed. It may also be desirable to fluoroscopically indicate the regions with auxiliary radiopaque markers on the prosthetic material 14, and/or scaffold-like structure 76 to aid in positioning the fasteners 56.
  • The fasteners 56 can be variously constructed. They can, e.g., comprise staples or (as shown) helical fasteners, like that shown in FIG. 4A, but without the tether element 18.
  • The prosthesis 70 as just described can be installed in various parts of the body and for various therapeutic purposes. Two embodiments will be described for the purpose of illustration. The first embodiment is directed to implantation within a heart chamber for treatment and/or repair of congestive heart failure. The second embodiment is directed to implantation in a heart valve annulus for heart valve remodeling.
  • B. Systems and Methods for Supporting Tissue in a Heart Chamber
  • FIG. 21 shows the prosthesis 70 as described installed in a left ventricle of a heart. The left ventricle has been enlarged due to the effects of congestive heart failure. As FIG. 21 shows, the prosthesis is desirably secured to the walls of the ventricle using fasteners 56.
  • The presence of the prosthesis 70 shapes the left ventricle in a desired fashion, pulling the chamber walls laterally closer together and thereby reducing the overall maximum internal volume. The presence of the prosthesis 70 resists further enlargement of the left ventricle during ventricular diastole and provides a shape is better suited to efficient ventricular pumping. However, the presence of the prosthesis 70 does not interfere with contraction of the left ventricle during ventricular systole.
  • In this embodiment, it is desired that the prosthesis 70 is not inherently electrically conductive, so as not to interfere with electrical conduction within the heart.
  • FIGS. 22A to 22D show the intra-vascular deployment of the prosthesis 70 shown in FIG. 21. Alternatively, the prosthesis 70 can be installed using conventional open heart surgical techniques or by thoracoscopic surgery techniques.
  • In the intra-vascular approach shown in FIGS. 22A to 22D, a first catheter 78 is navigated over a guide wire 80 through the aortic valve into the left ventricle (see FIG. 22A). The first catheter 78 can be delivered through the vasculature under fluoroscopic guidance, e.g., through either a retrograde arterial route (via, e.g., the femoral artery or subclavian artery) (as shown) or an antegrade venous then trans-septal route.
  • The first catheter 78 carries the prosthesis 70 in a radially reduced or collapsed configuration. Once inside the left ventricle (see FIG. 22B), the first catheter 70 releases the prosthesis 70, which eventually expands radially into the configuration shown in FIG. 21. The first catheter 78 is then withdrawn over the guide wire 80.
  • The guide component 28 (previously described is delivered over the guide wire 80 (which is then withdrawn) (see FIG. 22C) and maneuvered to each region where a fastener 56 is to be applied. The applier instrument 20 (previously described) is introduced through the guide component 28, as FIG. 22C shows and can also been seen in FIG. 4B. In this embodiment, the applier instrument 20 carries a helical fastener 56 generally of the type shown in FIG. 4A, but without a tether element 18. The applier instrument 20 rotates the fastener 56, causing it to penetrate the myocardium.
  • As FIG. 22D depicts, the guide component 28 is repositioned in succession to each intended attachment site for the fastener 56. At each site, the applier instrument 20 is actuated to place a fastener 56. FIGS. 22C and 22D show the guide component 28 braced against a wall of the ventricle to apply a counterbalancing resolution force to the implantation force. In this way, a desired pattern of fasteners 56 is applied, securing the prosthesis 70 to the left ventricle, as FIG. 21 shows. The applier instrument 20 and guide component 28 are then withdrawn.
  • The prosthesis 70 has been installed to shape the left ventricle to treat, in this instance, congestive heart failure.
  • In an alternative embodiment, the prosthesis 70 could be sized and configured to contain a fluid, e.g., saline or blood. For example, the prosthesis 70 can carry fluid receiving tubes or pockets. The delivery of fluid causes the tubes or pockets to expand, thereby enlarging the occupying volume of the prosthesis 70. As a result, the usable internal volume of the heart chamber is reduced.
  • FIG. 23 shows an alternative embodiment, in which the prosthesis 70 as described is installed around the exterior of the ventricles of a heart afflicted with congestive heart failure. The prosthesis 70 can be installed using conventional open heart surgical techniques or by thoracoscopic surgery techniques.
  • As shown in FIG. 23, the prosthesis 70 is desirably secured to the exterior walls of the ventricles using fasteners 56. The fasteners 56 are applied from within the heart, using the intra-vascular approach and technique just described. The presence of the prosthesis 70 shapes the ventricles, reducing their overall maximum internal volume. The presence of the prosthesis 70 also resists further enlargement of the ventricles and provides a shape is better suited to efficient ventricular pumping. The presence of the prosthesis 70, however, desirably does not interfere with contraction of the ventricles to a lesser volume.
  • FIGS. 24A and 24B show a prosthesis system 82 comprising an array of two or more patch components 50, as previously described with reference to FIG. 15A. In FIGS. 24A and 24B, the hollow body organ comprises a left ventricle of a heart, but it should be appreciated that the system 82 can be established in other body organs, as well. In this embodiment, each patch component 50 is individually attached by one or more fasteners 56 to a localized tissue region in the hollow body organ. The patch components 50 are shown to be placed in an overlapping array (see FIG. 24B), but the array need not be overlapping. FIG. 24A shows the guide component 28 braced against a wall of the ventricle to apply a counterbalancing resolution force to the implantation force. Using a plurality of patch components 50, the system 82 can form a composite prosthesis within the entire interior of the hollow body organ, or, alternatively, the system 82 can form a prosthesis that occupies only a portion of the entire interior to provide localized tissue shaping. While not shown, it should also be appreciated that the system 82 of patch components 50 can be installed on the exterior of the hollow body organ.
  • The system 82 comprising an array of discrete patch components 50 can shape all or a portion of the ventricles, resisting further enlargement of the ventricles and provides a shape is better suited to efficient ventricular pumping. The presence of the patch components 50, however, desirably does not interfere with contraction of the ventricles to a lesser volume.
  • The prostheses 70 and prosthesis system 82 shown and described in foregoing FIGS. 19 to 24 can be used alone or in combination with the tissue folding systems shown and described in FIGS. 10 to 15, as well as in combination with the tissue support systems described and shown in FIGS. 5 to 10. Furthermore, an implant 10 and/or 40, previously described, can be implanted in association with an individual patch component 50, with the patch component 50 in this arrangement serving to protect underlying tissue from abrasion and providing compliance between the implant 10/40 and tissue. Also, fasteners 56 used to secure a given prosthesis to any tissue wall (e.g., as shown in FIGS. 21 or 23) can be applied in association with an individual patch component 50, with the patch component 50 in this arrangement serving to protect the prosthesis 70 from abrasion due to the fastener 56, as well as providing compliance between the fastener 56 and the prosthesis 70.
  • C. Systems and Methods for Support Tissue at or Near a Heart Valve Annulus
  • FIG. 25 shows a prosthesis 70, in which the prosthesis body 72 is sized and configured as a ring, for placement in a heart valve annulus. The prosthesis body 72 can be in the form of a continuous ring or a discontinuous ring. In this way, the prosthesis body 72 is preformed in a desired size and shape to emulate the shape of a healthy, native annulus. The prosthesis body 72 thereby serves to shape an annulus that has experienced dilation, as well as resist future dilation. The prosthesis body 72 desirably shapes the annulus so that so that normal leaflet coaptation will occur, and/or so that retrograde flow through the valve is prevented or reduced.
  • In this embodiment, the body 72 includes a prosthetic material 74 that promotes tissue ingrowth, to aid in fixing the prosthesis 70 to tissue in or near the annulus. In this embodiment, it is desired that the material of the prosthesis body 72 is not inherently electrically conductive, so as not to interfere with electrical conduction within the heart.
  • As before described, the prosthesis body 72 in this embodiment is also desirable sized and configured to permit its non-invasive deployment by an intra-vascular catheter. Alternatively, however, the prosthesis body 72 can be installed using conventional open heart surgical techniques or by thoracoscopic surgery techniques.
  • In this arrangement, the prosthesis body 72 desirably includes eyelet regions 84 to receive fasteners 56, so that the prosthesis 70 can be secured to tissue in or near the targeted heart valve annulus.
  • FIG. 26A shows for purposes of illustration the prosthesis 70 installed in or near the annulus of a mitral valve. FIG. 26B shows for the purpose of illustration the prosthesis 70 installed in or near the annulus of an aortic valve. The prosthesis 70 may be attached either inside the ventricle in or near the aortic valve (as FIG. 26B shows) or outside the ventricle within the aorta in or near the aortic valve.
  • As FIG. 27 shows, the prosthesis body 72 can be delivered through intra-vascular access by a catheter 58 like that shown in FIG. 15B. The catheter 58 carries the prosthesis body 72 in a collapsed condition. Once positioned in the targeted heart annulus, the prosthesis body 72 can be released from the end of catheter 58 on guide elements 60. The guide elements 60 comprise wires with eyes 62, which are releasably secured to the eyelet regions 84 of the prosthesis body 72 by releasable sutures 64, as previously described. Once the prosthesis body is deployed and positioned, the prosthesis body can be attached to the annulus using the fasteners 56, and the sutures 64 then released to free the prosthesis body 72 from the catheter 58. As FIG. 15B shows, the applier instrument 20, previously described, may be deployed over the guide elements 60, or the applier instrument 20 may be deployed independent of the guide elements (as FIG. 27 shows) to apply the fasteners 56 to the eyelet regions.
  • The prosthesis 70 shown and described in foregoing FIGS. 25 to 27 can be used alone or in combination with the tissue support systems described and shown in FIGS. 8 and 9.
  • FIG. 32 shows a heart valve assembly 100 having a generally cylindrical shape formed by a collapsible scaffold-like structure 102. As shown, the scaffold-like structure 102 carries a prosthetic material 104, although the structure 102 can be free of a prosthetic material 104. As previously described with respect to the prosthesis 70, the prosthetic material 104 and/or scaffold-like structure 102 of the heart valve assembly 100 are sized and configured to assume a compressed or collapsed, low profile condition, to permit their intra-vascular introduction into a hollow body organ by a catheter. Also as previously discussed, the prosthetic material 104 and/or scaffold-like structure 102 are sized and configured for expansion, and preferably self-expansion, in situ from a collapsed condition into an expanded condition in contact with tissue in the targeted region. For example, the scaffold-like structure 102 can comprise a self-expanding plastic or metal material (e.g., from Nitinol® wire) that can be compressed in the presence of a force, but self-expands upon removal of the compressive force. As illustrated, the scaffold-like structure 102 comprises zigzag type stent rings.
  • The valve assembly 100 includes a flexible valve member 106. In the illustrated embodiment, the valve member comprises three, coapting leaflets 108, although the number of leaflets 108 can vary, e.g., between two and four.
  • In use (see FIG. 33), the valve assembly 100 is installed at or near a heart valve annulus. In FIG.33, the targeted heart valve annulus is the aortic valve. Desirably, as FIG. 33 shows, the valve assembly 100 accommodates the introduction of one or more fasteners 56 to anchor the assembly 100 in place either during or after its installation.
  • As previously described with respect to the prosthesis 70, regions of the scaffold-like structure 102 and/or prosthetic material 104 can be specially sized and configured for the receipt and retention of fasteners 56. The fasteners 56 can be variously constructed. They can, e.g., comprise staples or (as shown) helical fasteners, like that shown in FIG. 4A, but without the tether element 18.
  • The valve assembly 100 as just described can be installed in the region of a heart valve annulus by intra-vascular approach. However, it should be appreciated that the assembly 100 can be installed using an open surgical procedure.
  • Using an intra-vascular approach (see FIG. 34A), the assembly 100 may be deployed by first folding and/or compressing the assembly 100 into a lumen of a trans-vascular catheter 110 for delivery. The catheter 110 may be advanced through the vasculature into the heart through a retrograde arterial route (via, e.g., the femoral artery or subclavian artery) (as FIG. 34A shows) or an antegrade venous and then trans-septal route, if left heart access is needed from a peripheral vessel access. Use of a standard available guide wire 112 and/or guide sheath can assist the operator in delivering and deploying the catheter 110 into position.
  • The valve assembly 100 is then be pushed out of the lumen of the catheter 110 (as FIG. 34B shows). The assembly 100 self-expands into the desired shape and tension when released in situ (as FIG. 34C shows). After either partial or complete expansion of the valve assembly 100, the catheter 110 is withdrawn, and the guide component 28 (previously described) is delivered over the guide wire 112. The guide component 28 is maneuvered to each region where a fastener 56 is to be applied. The applier instrument 20 (previously described) is introduced through the guide component 28, as FIG. 34C shows.
  • The applier instrument 20 carries a helical fastener 56. The applier instrument 20 rotates the fastener 56, causing it to penetrate the myocardium. FIG. 34C shows the guide component 28 braced against a wall of the aorta to apply a counterbalancing resolution force to the implantation force. The guide component 28 is repositioned in succession to each intended attachment site for the fastener 56. At each site, the applier instrument 20 is actuated to place a fastener 56. In this way, a desired pattern of fasteners 56 is applied, securing the valve assembly 100 at or near the targeted heart valve annulus. The applier instrument 20 and guide component 28 are then withdrawn.
  • The valve assembly 100 has been installed to repair, or replace, or supplement a native heart valve.
  • The valve assembly 100 shown and described in foregoing FIGS. 32 to 34 can be used alone or in combination with the tissue support systems described and shown in FIGS. 8 and 9.
  • IV. Implants for Internally Supporting Tissue in a Hollow Body Organ
  • FIGS. 30A and 30B show an implant 86 sized and configured for placement in a hollow body organ. The implant 86 includes an elongated body 88 that can be made from a formed plastic or metal or ceramic material suited for implantation in the body.
  • The body 88 can possess a generally straight or linear configuration, as FIG. 30A shows. Alternatively, the body 88 can possess a curvilinear configuration, as FIG. 30B shows. As shown in FIGS. 30A and 30B, the body 88 possesses a helical coil configuration.
  • The body 88 includes a distal region 90. The distal region 90 is sized and configured to penetrate tissue.
  • The body 88 also includes a proximal region 92. As shown in FIGS. 30A and 30B, the proximal region 92 comprises an L-shaped leg. Like the L-shaped leg 16 shown in FIG. 4A, the L-shape leg 92 shown in FIGS. 30A and 30B desirably bisects the entire interior diameter of the coil body 88. As before described, the L-shaped leg 92 serves as a stop to prevent the coil body 88, when rotated, from penetrating too far into tissue. Furthermore, the rotatable implant drive mechanism 22 on the applier instrument 20 (shown in FIG. 4B) is sized and configured to engage the L-shaped leg 92 and impart rotation to the coil body 88 to achieve implantation in tissue.
  • The body 88 and its distal region 90 are sized and configured to be implanted within or partially within tissue in a hollow body organ. The linear body 88 shown in FIG. 30A can run either longitudinally or circumferentially within tissue, as FIG. 31 shows. The curvilinear body 88 shown in FIG. 30B exits tissue and then re-enters tissue in a serpentine path, as FIG. 31 also shows. When implanted, the implants 86 resist enlargement of the interior of a hollow body organ. However, the implants 86 desirably do not interfere with contraction of the hollow body organ to a lesser interior volume.
  • FIG. 31 shows the implants 86 implanted, for the purpose of illustration, in a left ventricle of a heart. The presence of the implants 86 prevents enlargement of the heart chamber due to, e.g., congestive heart failure. Of course, the implants 86 can be implanted in other hollow body organs and achieve a comparable therapeutic effect.
  • Like the implants 10 previously described, the implants 86 shown in FIGS. 30A and 30B can be installed by intra-vascular deployment using the instruments and techniques previously described. Alternatively, the implants 86 can be installed using conventional open heart surgical techniques or by thoracoscopic surgery techniques.
  • In the many catheter-based implantation techniques described above, the catheter used to place a given prosthesis in contact with tissue is usually manipulated to be detached from the prosthesis prior to the placement of fasteners. If desired, the catheter and prosthesis can remain coupled together during the fastening procedure. In this way, control of the prosthesis can be maintained up to and during the fastening procedure.
  • Other embodiments and uses of the invention will be apparent to those skilled in the art from consideration of the specification and practice of the invention disclosed herein. The specification and examples should be considered exemplary and merely descriptive of key technical; features and principles, and are not meant to be limiting. The true scope and spirit of the invention are defined by the following claims. As will be easily understood by those of ordinary skill in the art, variations and modifications of each of the disclosed embodiments can be easily made within the scope of this invention as defined by the following claims.

Claims (45)

  1. 1. A system for supporting tissue within a hollow body organ comprising
    a first implant sized and configured to penetrate a first region of tissue in the hollow body organ,
    a second implant sized and configured to penetrate a second region of tissue in the hollow body organ spatially distinct from the first region, and
    at least one tension element to apply tension on the first and second implants and thereby draw tissue inward, thereby defining a reduced interior volume within the hollow body organ.
  2. 2. A system according to claim 1
    wherein the tension element folds tissue between the first and second implants.
  3. 3. A system according to claim 2
    further including a patch element fastened to tissue and overlaying the fold between the first and second implants.
  4. 4. A system according to claim 1
    wherein the first and second implants are part of an array of implants that penetrates spatially distinct regions of tissue in the hollow body organ, and
    wherein the tension element applies tension on the array of implants and thereby draw tissue inward.
  5. 5. A system according to claim 1
    wherein at least one of the implants comprises a helical fastener.
  6. 6. A system according to claim 1
    wherein the tension element includes first and second tether elements joined, respectively, to the first and second implants, and
    at least one clip element gathering the first and second tether elements together in a taut condition.
  7. 7. A method of supporting tissue in a hollow body organ comprising the step of using a system as defined in claim 1.
  8. 8. A method of supporting tissue in a heart chamber comprising the step of using a system as defined in claim 1.
  9. 9. A method of supporting tissue in or near a heart valve annulus comprising the step of using a system as defined in claim 1.
  10. 10. A system for forming a tissue fold within a hollow body organ comprising
    a first implant sized and configured to penetrate a first region of tissue in the hollow body organ,
    a second implant sized and configured to penetrate a second region of tissue in the hollow body organ spatially distinct from the first region,
    at least one tension element extending between the first and second implants to apply tension on the first and second implants and thereby create a tissue fold between the first and second implants.
  11. 11. A system according to claim 10
    further including a patch element fastened to tissue and overlaying the tissue fold.
  12. 12. A system according to claim 10
    wherein the first and second implants are part of an array of implants that penetrates spatially distinct regions of tissue in the hollow body organ, and
    wherein the tension element extends among the array of implants to apply tension between adjacent implants and thereby create a pattern of tissue folds.
  13. 13. A system according to claim 12
    further including a patch element fastened to tissue and overlaying the pattern of tissue folds.
  14. 14. A system according to claim 10
    wherein at least one of the implants comprises a helical fastener.
  15. 15. A system according to claim 10
    wherein the tension element includes a tether element extending between the first and second implants in a taut condition.
  16. 16. A method of folding tissue in a hollow body organ comprising the step of using a system as defined in claim 10.
  17. 17. A method of folding tissue in a heart chamber comprising the step of using a system as defined in claim 10.
  18. 18. A method of folding tissue to close an atrial appendage comprising the step of using a system as defined in claim 10.
  19. 19. A method of folding tissue to close a perforation, hold, or defect comprising the step of using a system as defined in claim 10.
  20. 20. A system for supporting tissue in a hollow body organ comprising
    a prosthesis sized and configured for placement within an interior of the hollow body organ to regulate a size and/or shape of the hollow body organ, and
    at least one fastener securing the prosthesis to tissue in the hollow body organ.
  21. 21. A system according to claim 20
    wherein the fastener comprises a helical fastener.
  22. 22. A system according to claim 20
    wherein the prosthesis comprises an array of prosthetic patches.
  23. 23. A system according to claim 20
    wherein the prosthesis includes a formed body.
  24. 24. A system according to claim 20
    wherein the prosthesis includes an assembly of prosthesis sections.
  25. 25. A method of supporting tissue in a hollow body organ comprising the step of using a system as defined in claim 20.
  26. 26. A method of supporting tissue in a heart chamber comprising the step of using a system as defined in claim 20.
  27. 27. A method of supporting tissue in or near a heart valve annulus comprising the step of using a system as defined in claim 20.
  28. 28. A system for supporting tissue around a hollow body organ comprising
    a prosthesis sized and configured for placement on an exterior of the hollow body organ to regulate a size and/or shape of the hollow body organ, and
    at least one fastener securing the prosthesis to tissue on the hollow body organ.
  29. 29. A system according to claim 28
    wherein the fastener comprises a helical fastener.
  30. 30. A system according to claim 28
    wherein the prosthesis comprises an array of prosthetic patches.
  31. 31. A system according to claim 28
    wherein the prosthesis includes a formed body.
  32. 32. A system according to claim 28
    wherein the prosthesis includes an assembly of prosthesis sections.
  33. 33. A method of supporting tissue around a hollow body organ comprising the step of using a system as defined in claim 28.
  34. 34. A method of supporting tissue around a heart chamber comprising the step of using a system as defined in claim 28.
  35. 35. A system for supporting tissue within a hollow body organ comprising
    an elongated implant sized and configured to penetrate tissue and extend along a curvilinear path within or partially within a tissue wall to regulate a size and/or shape of the hollow body organ.
  36. 36. A system according to claim 35
    wherein the elongated implant comprises a helical shape.
  37. 37. A method of supporting tissue in a hollow body organ comprising the step of using a system as defined in claim 35.
  38. 38. A method of supporting tissue in a heart chamber comprising the step of using a system as defined in claim 35.
  39. 39. A system for reducing volume within a hollow body organ comprising
    a prosthesis sized and configured for placement within the hollow body organ, the prosthesis including an expandable segment to regulate a size and/or shape of the hollow body organ, and
    at least one fastener securing the prosthesis to tissue in the hollow body organ.
  40. 40. A system according to claim 39
    wherein the expandable segment is sized and configured to expand in response to receipt of fluid.
  41. 41. A method of reducing volume within a
    hollow body organ comprising the step of using a system as defined in claim 39.
  42. 42. A method of reducing volume within a heart chamber comprising the step of using a system as defined in claim 39.
  43. 43. A prosthesis for reducing volume within a hollow body organ comprising
    a prosthesis body sized and configured for placement within the hollow body organ, the prosthesis body including an expandable segment to regulate a size and/or shape of the hollow body organ, the expandable segment being sized and configured to expand in response to receipt of fluid.
  44. 44. A method of reducing volume within a hollow body organ comprising the step of using a prosthesis as defined in claim 43.
  45. 45. A method of reducing volume within a heart chamber comprising the step of using a prosthesis as defined in claim 43.
US10808216 2001-11-28 2004-03-24 Devices, systems, and methods for supporting tissue and/or structures within a hollow body organ Abandoned US20050177180A1 (en)

Priority Applications (3)

Application Number Priority Date Filing Date Title
US33393701 true 2001-11-28 2001-11-28
US10307226 US8075570B2 (en) 2001-11-28 2002-11-29 Intraluminal prosthesis attachment systems and methods
US10808216 US20050177180A1 (en) 2001-11-28 2004-03-24 Devices, systems, and methods for supporting tissue and/or structures within a hollow body organ

Applications Claiming Priority (9)

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US10808216 US20050177180A1 (en) 2001-11-28 2004-03-24 Devices, systems, and methods for supporting tissue and/or structures within a hollow body organ
CA 2558317 CA2558317A1 (en) 2004-03-24 2005-02-22 Devices, systems, and methods for supporting tissue and/or structures within a hollow body organ
CN 200580009570 CN100525719C (en) 2004-03-24 2005-02-22 Systems for supporting tissue and/or structures within a hollow body organ
CN 200910139527 CN101653365A (en) 2004-03-24 2005-02-22 Devices, systems, and methods for supporting tissue and/or structures within a hollow body organ
JP2007504965A JP2007530136A (en) 2004-03-24 2005-02-22 Device for supporting a tissue and / or structure of the hollow body organ, the system and method
PCT/US2005/005453 WO2005102181A1 (en) 2004-03-24 2005-02-22 Devices, systems, and methods for supporting tissue and/or structures within a hollow body organ
EP20050723408 EP1734872A4 (en) 2004-03-24 2005-02-22 Devices, systems, and methods for supporting tissue and/or structures within a hollow body organ
US11365056 US20060287661A1 (en) 2001-11-28 2006-03-01 Devices, systems, and methods for supporting tissue and/or structures within a hollow body organ
US13157242 US9023065B2 (en) 2001-11-28 2011-06-09 Devices, systems, and methods for supporting tissue and/or structures within a hollow body organ

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US11365056 Continuation US20060287661A1 (en) 2001-11-28 2006-03-01 Devices, systems, and methods for supporting tissue and/or structures within a hollow body organ

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US10808216 Abandoned US20050177180A1 (en) 2001-11-28 2004-03-24 Devices, systems, and methods for supporting tissue and/or structures within a hollow body organ
US11365056 Abandoned US20060287661A1 (en) 2001-11-28 2006-03-01 Devices, systems, and methods for supporting tissue and/or structures within a hollow body organ
US13157242 Active US9023065B2 (en) 2001-11-28 2011-06-09 Devices, systems, and methods for supporting tissue and/or structures within a hollow body organ

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US13157242 Active US9023065B2 (en) 2001-11-28 2011-06-09 Devices, systems, and methods for supporting tissue and/or structures within a hollow body organ

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Cited By (131)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20030105384A1 (en) * 1999-08-09 2003-06-05 Sharkey Hugh R. Method of improving cardiac function using a porous membrane
US20030141933A1 (en) * 2002-01-28 2003-07-31 Ultrarf, Inc. N-way RF power amplifier with increased backoff power and power added efficiency
US20060135970A1 (en) * 2004-11-15 2006-06-22 Laurent Schaller Catheter-based tissue remodeling devices and methods
US20060247764A1 (en) * 2005-04-27 2006-11-02 Bioventrix, A Chf Technologies Company, Inc. A Carlifornia Corporation System and method for sizing a heart for treating congestive heart failure
US20060264980A1 (en) * 1999-08-09 2006-11-23 Alexander Khairkhahan System for improving cardiac function
US20060281965A1 (en) * 2005-06-10 2006-12-14 Alexander Khairkhahan Peripheral seal for a ventricular partitioning device
US20070066863A1 (en) * 2005-08-31 2007-03-22 Medtronic Vascular, Inc. Device for treating mitral valve regurgitation
US20070112425A1 (en) * 2005-04-22 2007-05-17 Laurent Schaller Catheter-based tissue remodeling devices and methods
WO2007084411A2 (en) * 2006-01-13 2007-07-26 Erickson Ty B Needle driver and assembly
US20070244556A1 (en) * 2006-04-12 2007-10-18 Medtronic Vascular, Inc. Annuloplasty Device Having a Helical Anchor and Methods for its Use
US20070244555A1 (en) * 2006-04-12 2007-10-18 Medtronic Vascular, Inc. Annuloplasty Device Having a Helical Anchor and Methods for its Use
US20080051626A1 (en) * 2006-08-28 2008-02-28 Olympus Medical Systems Corp. Fistulectomy method between first duct and second duct, ultrasonic endoscope, catheter with balloon, magnet retaining device, and magnet set
US20080177132A1 (en) * 2006-11-06 2008-07-24 Caldera Medical, Inc. Implants And Procedures For Treatment Of Pelvic Floor Disorders
US20080188874A1 (en) * 2005-09-09 2008-08-07 University Of South Florida Laparoscopic hernia mesh spreader
US20080249541A1 (en) * 2007-04-04 2008-10-09 Stokes Michael J Device for plicating and fastening gastric tissue
US20080249560A1 (en) * 2007-04-04 2008-10-09 Stokes Michael J Method for plicating and fastening gastric tissue
US20080249539A1 (en) * 2007-04-04 2008-10-09 Stokes Michael J Device for plicating and fastening gastric tissue
US20080249561A1 (en) * 2007-04-04 2008-10-09 Stokes Michael J Method for plicating and fastening gastric tissue
US20080249542A1 (en) * 2007-04-04 2008-10-09 Stokes Michael J Device for plicating and fastening gastric tissue
US20080249540A1 (en) * 2007-04-04 2008-10-09 Stokes Michael J Method for plicating and fastening gastric tissue
US20080288060A1 (en) * 2004-07-06 2008-11-20 Baker Medical Research Institute Treating Valvular Insufficiency
US20080293996A1 (en) * 2006-02-06 2008-11-27 Evans Michael A Systems and methods for volume reduction
US20080312750A1 (en) * 2006-10-04 2008-12-18 Michael Laufer Methods and devices for reconfiguring a body organ
US20090112232A1 (en) * 2007-10-31 2009-04-30 Lawrence Crainich Method for Deploying A Device For Gastric Volume Reduction
WO2009055015A1 (en) * 2007-10-25 2009-04-30 Synecor, Llc Implantable device for delivery of therapeutic agents
US20090112303A1 (en) * 2001-11-28 2009-04-30 Lee Bolduc Devices, systems, and methods for endovascular staple and/or prosthesis delivery and implantation
US20090118762A1 (en) * 2007-10-31 2009-05-07 Lawrence Crainch Disposable cartridge for use in a gastric volume reduction procedure
US20090259304A1 (en) * 2008-04-15 2009-10-15 Medtronic Vascular, Inc. Devices and Methods for Treating Valvular Regurgitation
US20100030328A1 (en) * 2008-04-18 2010-02-04 Medtronic, Inc. Apparatus for Treating a Heart Valve, in Particular a Mitral Valve
US7674222B2 (en) 1999-08-09 2010-03-09 Cardiokinetix, Inc. Cardiac device and methods of use thereof
US20100185278A1 (en) * 2009-01-21 2010-07-22 Tendyne Medical Apical Papillary Msucle Attachment for Left Ventricular Reduction
US7762943B2 (en) 2004-03-03 2010-07-27 Cardiokinetix, Inc. Inflatable ventricular partitioning device
US20100191046A1 (en) * 2009-01-05 2010-07-29 Caldera Medical, Inc. Implants And Procedures For Supporting Anatomical Structures
US20100262167A1 (en) * 2009-04-09 2010-10-14 Medtronic, Inc. Medical Clip with Radial Tines, System and Method of Using Same
US20100298929A1 (en) * 2005-02-07 2010-11-25 Thornton Troy L Methods, systems and devices for cardiac valve repair
US7862500B2 (en) 2002-08-01 2011-01-04 Cardiokinetix, Inc. Multiple partitioning devices for heart treatment
US20110036888A1 (en) * 2009-08-14 2011-02-17 Tyco Healthcare Group Lp Tissue fastening system for a medical device
US7897086B2 (en) 2004-08-05 2011-03-01 Cardiokinetix, Inc. Method of making a laminar ventricular partitioning device
US20110082538A1 (en) * 2009-10-01 2011-04-07 Jonathan Dahlgren Medical device, kit and method for constricting tissue or a bodily orifice, for example, a mitral valve
US20110087203A1 (en) * 2006-08-02 2011-04-14 Kardium Inc. System for improving diastolic dysfunction
WO2011047201A2 (en) * 2009-10-14 2011-04-21 Tendyne Medical, Inc. Devices and methods for treatment of cardiomyopathy
US7942927B2 (en) 2004-03-15 2011-05-17 Baker Medical Research Institute Treating valve failure
US7972370B2 (en) 2008-04-24 2011-07-05 Medtronic Vascular, Inc. Stent graft system and method of use
US20110208298A1 (en) * 2010-02-24 2011-08-25 Medtronic Ventor Technologies Ltd Mitral Prosthesis and Methods for Implantation
US20120172931A1 (en) * 2009-06-21 2012-07-05 Aesthetics Point Ltd. implanted medical device useful for cosmetic surgery
US8246671B2 (en) 1999-08-09 2012-08-21 Cardiokinetix, Inc. Retrievable cardiac devices
US8337524B2 (en) 2006-02-21 2012-12-25 Kardium Inc. Method and device for closing holes in tissue
US8357195B2 (en) 2010-04-15 2013-01-22 Medtronic, Inc. Catheter based annuloplasty system and method
US8377114B2 (en) 1999-08-09 2013-02-19 Cardiokinetix, Inc. Sealing and filling ventricular partitioning devices to improve cardiac function
US8398537B2 (en) 2005-06-10 2013-03-19 Cardiokinetix, Inc. Peripheral seal for a ventricular partitioning device
US20130110230A1 (en) * 2007-02-14 2013-05-02 Edwards Lifesciences Corporation Suture and method for repairing a heart
US20130116780A1 (en) * 2011-11-04 2013-05-09 Valtech Cardio, Ltd. Implant having multiple rotational assemblies
US8449605B2 (en) 2006-06-28 2013-05-28 Kardium Inc. Method for anchoring a mitral valve
US8454656B2 (en) 2011-03-01 2013-06-04 Medtronic Ventor Technologies Ltd. Self-suturing anchors
US8518063B2 (en) 2001-04-24 2013-08-27 Russell A. Houser Arteriotomy closure devices and techniques
US8529430B2 (en) 2002-08-01 2013-09-10 Cardiokinetix, Inc. Therapeutic methods and devices following myocardial infarction
US8685044B2 (en) 2001-11-28 2014-04-01 Aptus Endosystems, Inc. Systems and methods for attaching a prosthesis with a body lumen or hollow organ
US20140114390A1 (en) * 2010-01-22 2014-04-24 4Tech Inc. Tricuspid valve repair using tension
US8790242B2 (en) 2009-10-26 2014-07-29 Cardiokinetix, Inc. Ventricular volume reduction
US8926695B2 (en) 2006-12-05 2015-01-06 Valtech Cardio, Ltd. Segmented ring placement
US8940002B2 (en) 2010-09-30 2015-01-27 Kardium Inc. Tissue anchor system
US8961541B2 (en) 2007-12-03 2015-02-24 Cardio Vascular Technologies Inc. Vascular closure devices, systems, and methods of use
US20150081014A1 (en) * 2006-12-05 2015-03-19 Valtech Cardio, Ltd. Implant and anchor placement
US8992567B1 (en) 2001-04-24 2015-03-31 Cardiovascular Technologies Inc. Compressible, deformable, or deflectable tissue closure devices and method of manufacture
US9023065B2 (en) 2001-11-28 2015-05-05 Aptus Endosystems, Inc. Devices, systems, and methods for supporting tissue and/or structures within a hollow body organ
US9023067B2 (en) 2009-07-10 2015-05-05 Educational Foundation Jichi Medical University Surgical system for stoma closure in biological duct
WO2015069947A1 (en) * 2012-11-07 2015-05-14 Nasser Rafiee Devices, systems and methods for repairing lumenal systems
US9050066B2 (en) 2010-06-07 2015-06-09 Kardium Inc. Closing openings in anatomical tissue
US9072511B2 (en) 2011-03-25 2015-07-07 Kardium Inc. Medical kit for constricting tissue or a bodily orifice, for example, a mitral valve
US9078660B2 (en) 2000-08-09 2015-07-14 Cardiokinetix, Inc. Devices and methods for delivering an endocardial device
US9078749B2 (en) 2007-09-13 2015-07-14 Georg Lutter Truncated cone heart valve stent
US9119719B2 (en) 2009-05-07 2015-09-01 Valtech Cardio, Ltd. Annuloplasty ring with intra-ring anchoring
EP2525725A4 (en) * 2010-01-20 2015-10-07 New Hope Ventures Lp Tissue repair implant and delivery device and method
US9277994B2 (en) 2008-12-22 2016-03-08 Valtech Cardio, Ltd. Implantation of repair chords in the heart
US9320591B2 (en) 2001-11-28 2016-04-26 Medtronic Vascular, Inc. Devices, systems, and methods for prosthesis delivery and implantation, including the use of a fastener tool
US9320589B2 (en) 2001-11-28 2016-04-26 Medtronic Vascular, Inc. Endovascular aneurysm repair system
US9320503B2 (en) 2001-11-28 2016-04-26 Medtronic Vascular, Inc. Devices, system, and methods for guiding an operative tool into an interior body region
US9332992B2 (en) 2004-08-05 2016-05-10 Cardiokinetix, Inc. Method for making a laminar ventricular partitioning device
US9332993B2 (en) 2004-08-05 2016-05-10 Cardiokinetix, Inc. Devices and methods for delivering an endocardial device
US9345460B2 (en) 2001-04-24 2016-05-24 Cardiovascular Technologies, Inc. Tissue closure devices, device and systems for delivery, kits and methods therefor
US9375218B2 (en) 2006-05-03 2016-06-28 Datascope Corp. Systems and methods of tissue closure
US9414921B2 (en) 2009-10-29 2016-08-16 Valtech Cardio, Ltd. Tissue anchor for annuloplasty device
US9445898B2 (en) 2011-03-01 2016-09-20 Medtronic Ventor Technologies Ltd. Mitral valve repair
US9474606B2 (en) 2009-05-04 2016-10-25 Valtech Cardio, Ltd. Over-wire implant contraction methods
US9480559B2 (en) 2011-08-11 2016-11-01 Tendyne Holdings, Inc. Prosthetic valves and related inventions
US9486306B2 (en) 2013-04-02 2016-11-08 Tendyne Holdings, Inc. Inflatable annular sealing device for prosthetic mitral valve
US9526611B2 (en) 2013-10-29 2016-12-27 Tendyne Holdings, Inc. Apparatus and methods for delivery of transcatheter prosthetic valves
US9526613B2 (en) 2005-03-17 2016-12-27 Valtech Cardio Ltd. Mitral valve treatment techniques
US9561104B2 (en) 2009-02-17 2017-02-07 Valtech Cardio, Ltd. Actively-engageable movement-restriction mechanism for use with an annuloplasty structure
US9597181B2 (en) 2013-06-25 2017-03-21 Tendyne Holdings, Inc. Thrombus management and structural compliance features for prosthetic heart valves
US20170079797A1 (en) * 2010-01-22 2017-03-23 4 Tech Inc. Tricuspid valve repair using tension
US9610159B2 (en) 2013-05-30 2017-04-04 Tendyne Holdings, Inc. Structural members for prosthetic mitral valves
US9610162B2 (en) 2013-12-26 2017-04-04 Valtech Cardio, Ltd. Implantation of flexible implant
US20170095333A1 (en) * 2006-10-04 2017-04-06 Edwards Lifesciences Corporation Method and apparatus for reshaping a ventricle
US9622861B2 (en) 2009-12-02 2017-04-18 Valtech Cardio, Ltd. Tool for actuating an adjusting mechanism
US9655709B2 (en) 2013-09-26 2017-05-23 Covidien Lp Mesh deployment devices and kits
US9662209B2 (en) 2008-12-22 2017-05-30 Valtech Cardio, Ltd. Contractible annuloplasty structures
US9675454B2 (en) 2012-07-30 2017-06-13 Tendyne Holdings, Inc. Delivery systems and methods for transcatheter prosthetic valves
US9693865B2 (en) 2013-01-09 2017-07-04 4 Tech Inc. Soft tissue depth-finding tool
US9694121B2 (en) 1999-08-09 2017-07-04 Cardiokinetix, Inc. Systems and methods for improving cardiac function
US9713530B2 (en) 2008-12-22 2017-07-25 Valtech Cardio, Ltd. Adjustable annuloplasty devices and adjustment mechanisms therefor
US9724192B2 (en) 2011-11-08 2017-08-08 Valtech Cardio, Ltd. Controlled steering functionality for implant-delivery tool
US9730793B2 (en) 2012-12-06 2017-08-15 Valtech Cardio, Ltd. Techniques for guide-wire based advancement of a tool
US9744038B2 (en) 2008-05-13 2017-08-29 Kardium Inc. Medical device for constricting tissue or a bodily orifice, for example a mitral valve
US9795480B2 (en) 2010-08-24 2017-10-24 Millipede, Inc. Reconfiguring tissue features of a heart annulus
US9795482B2 (en) 2010-04-27 2017-10-24 Medtronic, Inc. Prosthetic heart valve devices and methods of valve repair
US9801720B2 (en) 2014-06-19 2017-10-31 4Tech Inc. Cardiac tissue cinching
US9827092B2 (en) 2011-12-16 2017-11-28 Tendyne Holdings, Inc. Tethers for prosthetic mitral valve
US9848983B2 (en) 2015-02-13 2017-12-26 Millipede, Inc. Valve replacement using rotational anchors
US9877833B1 (en) 2016-12-30 2018-01-30 Pipeline Medical Technologies, Inc. Method and apparatus for transvascular implantation of neo chordae tendinae
US9883943B2 (en) 2006-12-05 2018-02-06 Valtech Cardio, Ltd. Implantation of repair devices in the heart
US9895221B2 (en) 2012-07-28 2018-02-20 Tendyne Holdings, Inc. Multi-component designs for heart valve retrieval device, sealing structures and stent assembly
US9907547B2 (en) 2014-12-02 2018-03-06 4Tech Inc. Off-center tissue anchors
US9907681B2 (en) 2013-03-14 2018-03-06 4Tech Inc. Stent with tether interface
US9913706B2 (en) 2014-07-17 2018-03-13 Millipede, Inc. Adjustable endolumenal implant for reshaping the mitral valve annulus
US9918840B2 (en) 2011-06-23 2018-03-20 Valtech Cardio, Ltd. Closed band for percutaneous annuloplasty
US9949828B2 (en) 2012-10-23 2018-04-24 Valtech Cardio, Ltd. Controlled steering functionality for implant-delivery tool
US20180116797A9 (en) * 2009-10-29 2018-05-03 Valtech Cardio, Ltd. Tissue anchor for annuloplasty device
US9968454B2 (en) 2009-10-29 2018-05-15 Valtech Cardio, Ltd. Techniques for guide-wire based advancement of artificial chordae
US9968452B2 (en) 2009-05-04 2018-05-15 Valtech Cardio, Ltd. Annuloplasty ring delivery cathethers
US9968353B2 (en) 2001-06-04 2018-05-15 Medtronic Vascular, Inc. Catheter based fastener implantation apparatus and methods
US9980708B2 (en) 2010-01-20 2018-05-29 Micro Interventional Devices, Inc. Tissue closure device and method
US9986993B2 (en) 2014-02-11 2018-06-05 Tendyne Holdings, Inc. Adjustable tether and epicardial pad system for prosthetic heart valve
US10022114B2 (en) 2013-10-30 2018-07-17 4Tech Inc. Percutaneous tether locking
US10039643B2 (en) 2013-10-30 2018-08-07 4Tech Inc. Multiple anchoring-point tension system
US10045765B2 (en) 2014-03-27 2018-08-14 Transmural Systems Llc Devices and methods for closure of transvascular or transcameral access ports
US10052095B2 (en) 2013-10-30 2018-08-21 4Tech Inc. Multiple anchoring-point tension system
US10058323B2 (en) 2010-01-22 2018-08-28 4 Tech Inc. Tricuspid valve repair using tension
US10058315B2 (en) 2014-03-27 2018-08-28 Transmural Systems Llc Devices and methods for closure of transvascular or transcameral access ports
US10058314B2 (en) 2010-01-20 2018-08-28 Micro Interventional Devices, Inc. Tissue closure device and method
US10064696B2 (en) 2000-08-09 2018-09-04 Edwards Lifesciences Corporation Devices and methods for delivering an endocardial device

Families Citing this family (74)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6626899B2 (en) 1999-06-25 2003-09-30 Nidus Medical, Llc Apparatus and methods for treating tissue
US7666193B2 (en) 2002-06-13 2010-02-23 Guided Delivery Sytems, Inc. Delivery devices and methods for heart valve repair
US7883538B2 (en) 2002-06-13 2011-02-08 Guided Delivery Systems Inc. Methods and devices for termination
US20060122633A1 (en) 2002-06-13 2006-06-08 John To Methods and devices for termination
US7753858B2 (en) 2002-06-13 2010-07-13 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
US8641727B2 (en) 2002-06-13 2014-02-04 Guided Delivery Systems, Inc. Devices and methods for heart valve repair
US9949829B2 (en) 2002-06-13 2018-04-24 Ancora Heart, Inc. Delivery devices and methods for heart valve repair
US7753924B2 (en) 2003-09-04 2010-07-13 Guided Delivery Systems, Inc. Delivery devices and methods for heart valve repair
US7758637B2 (en) 2003-02-06 2010-07-20 Guided Delivery Systems, Inc. Delivery devices and methods for heart valve repair
US8287555B2 (en) 2003-02-06 2012-10-16 Guided Delivery Systems, Inc. Devices and methods for heart valve repair
ES2370246T3 (en) 2003-06-13 2011-12-13 Tyco Healthcare Group Lp Interconnecting multiple elements surgical instrument and resorbable screw fastener.
US8926637B2 (en) 2003-06-13 2015-01-06 Covidien Lp Multiple member interconnect for surgical instrument and absorbable screw fastener
JP4673305B2 (en) * 2003-08-11 2011-04-20 ウィルソン−クック・メディカル・インコーポレーテッドWilson−Cook Medical Incorporated A surgical implant
US7753922B2 (en) 2003-09-04 2010-07-13 Guided Delivery Systems, Inc. Devices and methods for cardiac annulus stabilization and treatment
US7976539B2 (en) 2004-03-05 2011-07-12 Hansen Medical, Inc. System and method for denaturing and fixing collagenous tissue
ES2425948T3 (en) 2005-11-14 2013-10-18 Covidien Lp Delivery system for ostial stent locations within a conduit
US7632308B2 (en) 2005-11-23 2009-12-15 Didier Loulmet Methods, devices, and kits for treating mitral valve prolapse
WO2007136532A3 (en) * 2006-05-03 2008-03-13 St Jude Medical Soft body tissue remodeling methods and apparatus
US9119633B2 (en) 2006-06-28 2015-09-01 Kardium Inc. Apparatus and method for intra-cardiac mapping and ablation
US10028783B2 (en) 2006-06-28 2018-07-24 Kardium Inc. Apparatus and method for intra-cardiac mapping and ablation
US8920411B2 (en) 2006-06-28 2014-12-30 Kardium Inc. Apparatus and method for intra-cardiac mapping and ablation
JP5522664B2 (en) 2006-09-08 2014-06-18 カーディオポリマーズ, インコーポレイテッド Intramyocardial patterning for resizing and reshaping of the entire cardiac
US8388680B2 (en) 2006-10-18 2013-03-05 Guided Delivery Systems, Inc. Methods and devices for catheter advancement and delivery of substances therethrough
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
JP5282185B2 (en) * 2007-08-31 2013-09-04 株式会社バイタル Ventricle affected part prosthesis and ventricular affected part prosthesis treatment set
US8906011B2 (en) 2007-11-16 2014-12-09 Kardium Inc. Medical device for use in bodily lumens, for example an atrium
EP2082690B1 (en) * 2008-01-24 2012-06-20 Kardium, Inc. Medical device to assist diastolic function and prevent ventricular enlargement
US8790367B2 (en) 2008-02-06 2014-07-29 Guided Delivery Systems Inc. Multi-window guide tunnel
WO2009101617A3 (en) 2008-02-11 2010-01-14 Corassist Cardiovascular Ltd. Ventricular function assisting devices and methods of use thereof
US8801665B2 (en) 2008-04-10 2014-08-12 Henry Ford Health System Apparatus and method for controlled depth of injection into myocardial tissue
US20100121437A1 (en) 2008-04-16 2010-05-13 Cardiovascular Technologies, Llc Transvalvular intraannular band and chordae cutting for ischemic and dilated cardiomyopathy
JP5774594B2 (en) 2009-10-14 2015-09-09 ハート・リペアー・テクノロジーズ・インコーポレーテッド Percutaneous valve port ring in the band for mitral valve repair
US20100121435A1 (en) 2008-04-16 2010-05-13 Cardiovascular Technologies, Llc Percutaneous transvalvular intrannular band for mitral valve repair
US20100131057A1 (en) 2008-04-16 2010-05-27 Cardiovascular Technologies, Llc Transvalvular intraannular band for aortic valve repair
US8795298B2 (en) 2008-10-10 2014-08-05 Guided Delivery Systems Inc. Tether tensioning devices and related methods
EP2349019A4 (en) 2008-10-10 2016-06-15 Guided Delivery Systems Inc Termination devices and related methods
US20110011917A1 (en) * 2008-12-31 2011-01-20 Hansen Medical, Inc. Methods, devices, and kits for treating valve prolapse
US20100198192A1 (en) 2009-01-20 2010-08-05 Eugene Serina Anchor deployment devices and related methods
US8277502B2 (en) * 2009-10-29 2012-10-02 Valtech Cardio, Ltd. Tissue anchor for annuloplasty device
US8940042B2 (en) * 2009-10-29 2015-01-27 Valtech Cardio, Ltd. Apparatus for guide-wire based advancement of a rotation assembly
EP2498685B1 (en) 2009-11-09 2014-06-18 Entourage Medical Technologies, Inc. System for providing access and closure to tissue
US20150359627A1 (en) * 2010-01-20 2015-12-17 Micro Interventional Devices, Inc. System and Method for Heart Valve Anchoring
US8961596B2 (en) 2010-01-22 2015-02-24 4Tech Inc. Method and apparatus for tricuspid valve repair using tension
CA2842288A1 (en) 2011-07-21 2013-01-24 4Tech Inc. Method and apparatus for tricuspid valve repair using tension
WO2011156714A3 (en) * 2010-06-10 2012-02-02 Chambers Dr Jeffrey W Systems for preventing formation of blood clots in the left atrium
US9161778B2 (en) 2010-06-11 2015-10-20 Entourage Medical Technologies, Inc. System and method for transapical access and closure
US9044267B2 (en) 2010-06-11 2015-06-02 Entourage Medical Technologies, Inc. System and method for transapical access and closure
WO2012031204A3 (en) 2010-09-03 2012-04-26 Guided Delivery Systems Inc. Devices and methods for anchoring tissue
US20120089159A1 (en) 2010-09-20 2012-04-12 Shluzas Alan E System for tensioning a surgical closure
WO2012040643A3 (en) * 2010-09-23 2012-06-14 Colibri Heart Valve Llc Percutaneously deliverable heart or blood vessel valve with frame having abluminally situated tissue membrane
US8942829B2 (en) 2011-01-20 2015-01-27 Medtronic, Inc. Trans-septal lead anchoring
US9480525B2 (en) 2011-01-21 2016-11-01 Kardium, Inc. High-density electrode-based medical device system
USD777926S1 (en) 2012-01-20 2017-01-31 Kardium Inc. Intra-cardiac procedure device
US9452016B2 (en) 2011-01-21 2016-09-27 Kardium Inc. Catheter system
USD777925S1 (en) 2012-01-20 2017-01-31 Kardium Inc. Intra-cardiac procedure device
CA2764494A1 (en) 2011-01-21 2012-07-21 Kardium Inc. Enhanced medical device for use in bodily cavities, for example an atrium
US9427225B2 (en) 2011-03-25 2016-08-30 Smith & Nephew, Inc. Tissue lifting
CN103491901B (en) * 2011-04-04 2016-04-20 特拉维夫医学中心医学研究,基础设施及健康服务基金 Apparatus and method of heart valve repair
US8940044B2 (en) 2011-06-23 2015-01-27 Valtech Cardio, Ltd. Closure element for use with an annuloplasty structure
US8926697B2 (en) 2011-06-23 2015-01-06 Valtech Cardio, Ltd. Closed band for percutaneous annuloplasty
US9198592B2 (en) 2012-05-21 2015-12-01 Kardium Inc. Systems and methods for activating transducers
US9011423B2 (en) 2012-05-21 2015-04-21 Kardium, Inc. Systems and methods for selecting, activating, or selecting and activating transducers
US8961594B2 (en) 2012-05-31 2015-02-24 4Tech Inc. Heart valve repair system
US9867620B2 (en) 2013-03-14 2018-01-16 Covidien Lp Articulation joint for apparatus for endoscopic procedures
DE102013208038B4 (en) * 2013-05-02 2016-09-08 Michael Siegenthaler Catheter based ventricular assist device
US9668730B2 (en) 2013-06-28 2017-06-06 Covidien Lp Articulating apparatus for endoscopic procedures with timing system
US9351728B2 (en) 2013-06-28 2016-05-31 Covidien Lp Articulating apparatus for endoscopic procedures
JP2016537162A (en) 2013-10-29 2016-12-01 アントラージュ メディカル テクノロジーズ,インコーポレイテッドEntourage Medical Technologies,Inc. System for providing surgical access
CN104055603B (en) * 2014-07-07 2017-02-01 宁波健世生物科技有限公司 Heart valve implantation instrument with a new type of apparatus anchor
CN104706444B (en) * 2015-03-03 2017-07-18 上海形状记忆合金材料有限公司 Left ventricular volume reduction means
CA2978599A1 (en) 2015-03-05 2016-09-09 Ancora Heart, Inc. Devices and methods of visualizing and determining depth of penetration in cardiac tissue
US10028733B2 (en) 2015-05-28 2018-07-24 National University Of Ireland, Galway Fistula treatment device
US20170135817A1 (en) * 2015-11-17 2017-05-18 Edwards Lifesciences Corporation Systems and devices for setting an anchor

Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5192314A (en) * 1991-12-12 1993-03-09 Daskalakis Michael K Synthetic intraventricular implants and method of inserting
US5865791A (en) * 1995-06-07 1999-02-02 E.P. Technologies Inc. Atrial appendage stasis reduction procedure and devices

Family Cites Families (280)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2033039A (en) 1935-05-22 1936-03-03 Arthur A Limpert Double point rotary pin
US3499222A (en) 1965-08-17 1970-03-10 Leonard I Linkow Intra-osseous pins and posts and their use and techniques thereof
US3686740A (en) 1970-06-19 1972-08-29 Donald P Shiley Method of assemblying a sutureless heart valve
US3799172A (en) 1972-09-25 1974-03-26 R Szpur Retention catheter
FR2299548A1 (en) 1975-01-30 1976-08-27 Melin Raymond Wire attachment element for corrugated cardboard cartons - has corkscrew form with bevelled end and insertion tool with chuck to match
US4140126A (en) 1977-02-18 1979-02-20 Choudhury M Hasan Method for performing aneurysm repair
US4255820A (en) 1979-07-24 1981-03-17 Rothermel Joel E Artificial ligaments
US4307722A (en) 1979-08-14 1981-12-29 Evans Joseph M Dilators for arterial dilation
US4899747A (en) * 1981-12-10 1990-02-13 Garren Lloyd R Method and appartus for treating obesity
DE3333427C2 (en) 1983-09-16 1991-05-08 Karl M. Reich Maschinenfabrik Gmbh, 7440 Nuertingen, De
US5693083A (en) 1983-12-09 1997-12-02 Endovascular Technologies, Inc. Thoracic graft and delivery catheter
US5104399A (en) 1986-12-10 1992-04-14 Endovascular Technologies, Inc. Artificial graft and implantation method
US5669936A (en) 1983-12-09 1997-09-23 Endovascular Technologies, Inc. Endovascular grafting system and method for use therewith
US4586923A (en) 1984-06-25 1986-05-06 Cordis Corporation Curving tip catheter
US4580568A (en) 1984-10-01 1986-04-08 Cook, Incorporated Percutaneous endovascular stent and method for insertion thereof
US4694827A (en) * 1986-01-14 1987-09-22 Weiner Brian C Inflatable gastric device for treating obesity and method of using the same
US4822345A (en) 1986-08-14 1989-04-18 Danforth John W Controllable flexibility catheter
US4781682A (en) 1987-08-13 1988-11-01 Patel Piyush V Catheter having support flaps and method of inserting catheter
FR2624747A1 (en) 1987-12-18 1989-06-23 Delsanti Gerard removable endo-arterial devices intended to repairing detachments walls of the arteries
US4921484A (en) 1988-07-25 1990-05-01 Cordis Corporation Mesh balloon catheter device
US4990151A (en) 1988-09-28 1991-02-05 Medinvent S.A. Device for transluminal implantation or extraction
US4898577A (en) 1988-09-28 1990-02-06 Advanced Cardiovascular Systems, Inc. Guiding cathether with controllable distal tip
US5030204A (en) 1988-09-28 1991-07-09 Advanced Cardiovascular Systems, Inc. Guiding catheter with controllable distal tip
US5044519A (en) 1988-10-22 1991-09-03 Yoshitaka Aoyama Apparatus for feeding slender parts
US5480382A (en) 1989-01-09 1996-01-02 Pilot Cardiovascular Systems, Inc. Steerable medical device
US5053047A (en) 1989-05-16 1991-10-01 Inbae Yoon Suture devices particularly useful in endoscopic surgery and methods of suturing
US4994071A (en) 1989-05-22 1991-02-19 Cordis Corporation Bifurcating stent apparatus and method
US5207695A (en) 1989-06-19 1993-05-04 Trout Iii Hugh H Aortic graft, implantation device, and method for repairing aortic aneurysm
US5254088A (en) 1990-02-02 1993-10-19 Ep Technologies, Inc. Catheter steering mechanism
US5195968A (en) 1990-02-02 1993-03-23 Ingemar Lundquist Catheter steering mechanism
US5071407A (en) 1990-04-12 1991-12-10 Schneider (U.S.A.) Inc. Radially expandable fixation member
US5578071A (en) 1990-06-11 1996-11-26 Parodi; Juan C. Aortic graft
US5360443A (en) 1990-06-11 1994-11-01 Barone Hector D Aortic graft for repairing an abdominal aortic aneurysm
ES2085435T3 (en) 1990-10-09 1996-06-01 Cook Inc Percutaneous dilator device.
US5042707A (en) 1990-10-16 1991-08-27 Taheri Syde A Intravascular stapler, and method of operating same
EP0489937B1 (en) 1990-12-07 1995-06-21 Willy Rüsch Ag Medical instrument with steerable tip
CA2065634C (en) 1991-04-11 1997-06-03 Alec A. Piplani Endovascular graft having bifurcation and apparatus and method for deploying the same
US6682557B1 (en) 1991-04-11 2004-01-27 Endovascular Technologies, Inc. Bifurcated multicapsule intraluminal grafting system and method
US5185004A (en) 1991-06-03 1993-02-09 Danforth Biomedical, Inc. Turn-limiting proximal adaptor for steerable catheter systems
JPH07500023A (en) 1991-07-04 1995-01-05
US5766151A (en) 1991-07-16 1998-06-16 Heartport, Inc. Endovascular system for arresting the heart
US5456713A (en) 1991-10-25 1995-10-10 Cook Incorporated Expandable transluminal graft prosthesis for repairs of aneurysm and method for implanting
EP0539237A1 (en) 1991-10-25 1993-04-28 Cook Incorporated Expandable transluminal graft prosthesis for repair of aneurysm and method for implanting
US5693084A (en) 1991-10-25 1997-12-02 Cook Incorporated Expandable transluminal graft prosthesis for repair of aneurysm
US5387235A (en) 1991-10-25 1995-02-07 Cook Incorporated Expandable transluminal graft prosthesis for repair of aneurysm
US5383880A (en) 1992-01-17 1995-01-24 Ethicon, Inc. Endoscopic surgical system with sensing means
US5352197A (en) 1992-03-18 1994-10-04 The Spectranetics Corporation Turn limiter for a catheter with twistable tip
US5318525A (en) 1992-04-10 1994-06-07 Medtronic Cardiorhythm Steerable electrode catheter
US5330490A (en) 1992-04-10 1994-07-19 Wilk Peter J Endoscopic device, prosthesis and method for use in endovascular repair
US5290295A (en) 1992-07-15 1994-03-01 Querals & Fine, Inc. Insertion tool for an intraluminal graft procedure
US5707376A (en) 1992-08-06 1998-01-13 William Cook Europe A/S Stent introducer and method of use
US5702365A (en) 1992-09-08 1997-12-30 King; Toby St. John Daul-lumen catheter
US5334196A (en) 1992-10-05 1994-08-02 United States Surgical Corporation Endoscopic fastener remover
US5409498A (en) 1992-11-05 1995-04-25 Ethicon, Inc. Rotatable articulating endoscopic fastening instrument
US5364351A (en) 1992-11-13 1994-11-15 Ep Technologies, Inc. Catheter steering mechanism
US5320630A (en) 1993-02-23 1994-06-14 Munir Ahmed Endoscopic ligating instrument for applying elastic bands
US5480423A (en) 1993-05-20 1996-01-02 Boston Scientific Corporation Prosthesis delivery
US7060021B1 (en) * 1998-07-23 2006-06-13 Wilk Patent Development Corporation Method and device for improving cardiac function
US6572529B2 (en) * 1993-06-17 2003-06-03 Wilk Patent Development Corporation Intrapericardial assist method
US6258021B1 (en) * 1993-06-17 2001-07-10 Peter J. Wilk Intrapericardial assist method
US5734373A (en) 1993-07-16 1998-03-31 Immersion Human Interface Corporation Method and apparatus for controlling force feedback interface systems utilizing a host computer
US5474568A (en) 1993-10-08 1995-12-12 United States Surgical Corporation Instrument for closing trocar puncture wounds
US5639278A (en) 1993-10-21 1997-06-17 Corvita Corporation Expandable supportive bifurcated endoluminal grafts
US5855598A (en) 1993-10-21 1999-01-05 Corvita Corporation Expandable supportive branched endoluminal grafts
US5632772A (en) 1993-10-21 1997-05-27 Corvita Corporation Expandable supportive branched endoluminal grafts
DE69419877T2 (en) 1993-11-04 1999-12-16 Bard Inc C R Fixed vascular prosthesis
CA2139979A1 (en) 1994-01-13 1995-07-14 Daniel C. Rosenman Spiral surgical tack
US5609627A (en) 1994-02-09 1997-03-11 Boston Scientific Technology, Inc. Method for delivering a bifurcated endoluminal prosthesis
US6039749A (en) 1994-02-10 2000-03-21 Endovascular Systems, Inc. Method and apparatus for deploying non-circular stents and graftstent complexes
US6165210A (en) 1994-04-01 2000-12-26 Gore Enterprise Holdings, Inc. Self-expandable helical intravascular stent and stent-graft
US5470337A (en) 1994-05-17 1995-11-28 Moss; Gerald Surgical fastener
US5683451A (en) 1994-06-08 1997-11-04 Cardiovascular Concepts, Inc. Apparatus and methods for deployment release of intraluminal prostheses
US5824041A (en) 1994-06-08 1998-10-20 Medtronic, Inc. Apparatus and methods for placement and repositioning of intraluminal prostheses
US5522881A (en) 1994-06-28 1996-06-04 Meadox Medicals, Inc. Implantable tubular prosthesis having integral cuffs
US5582616A (en) 1994-08-05 1996-12-10 Origin Medsystems, Inc. Surgical helical fastener with applicator
US5972023A (en) 1994-08-15 1999-10-26 Eva Corporation Implantation device for an aortic graft method of treating aortic aneurysm
US5913894A (en) 1994-12-05 1999-06-22 Meadox Medicals, Inc. Solid woven tubular prosthesis
US5755770A (en) 1995-01-31 1998-05-26 Boston Scientific Corporatiion Endovascular aortic graft
US5634936A (en) * 1995-02-06 1997-06-03 Scimed Life Systems, Inc. Device for closing a septal defect
US5683449A (en) 1995-02-24 1997-11-04 Marcade; Jean Paul Modular bifurcated intraluminal grafts and methods for delivering and assembling same
US5976159A (en) 1995-02-24 1999-11-02 Heartport, Inc. Surgical clips and methods for tissue approximation
US5662675A (en) 1995-02-24 1997-09-02 Intervascular, Inc. Delivery catheter assembly
US5626613A (en) * 1995-05-04 1997-05-06 Arthrex, Inc. Corkscrew suture anchor and driver
US5534007A (en) 1995-05-18 1996-07-09 Scimed Life Systems, Inc. Stent deployment catheter with collapsible sheath
US5700269A (en) 1995-06-06 1997-12-23 Corvita Corporation Endoluminal prosthesis deployment device for use with prostheses of variable length and having retraction ability
US5800528A (en) * 1995-06-13 1998-09-01 Abiomed R & D, Inc. Passive girdle for heart ventricle for therapeutic aid to patients having ventricular dilatation
WO1997003616A1 (en) 1995-07-14 1997-02-06 Spiros Skardoutsos Angiosurgical device and vascular graft and vascular annulus for vessel-vascular graft binding
US5713907A (en) 1995-07-20 1998-02-03 Endotex Interventional Systems, Inc. Apparatus and method for dilating a lumen and for inserting an intraluminal graft
US5662683A (en) 1995-08-22 1997-09-02 Ortho Helix Limited Open helical organic tissue anchor and method of facilitating healing
US6193745B1 (en) 1995-10-03 2001-02-27 Medtronic, Inc. Modular intraluminal prosteheses construction and methods
US5824037A (en) 1995-10-03 1998-10-20 Medtronic, Inc. Modular intraluminal prostheses construction and methods
US6287315B1 (en) 1995-10-30 2001-09-11 World Medical Manufacturing Corporation Apparatus for delivering an endoluminal prosthesis
US5591195A (en) 1995-10-30 1997-01-07 Taheri; Syde Apparatus and method for engrafting a blood vessel
US5628788A (en) 1995-11-07 1997-05-13 Corvita Corporation Self-expanding endoluminal stent-graft
US6576009B2 (en) 1995-12-01 2003-06-10 Medtronic Ave, Inc. Bifurcated intraluminal prostheses construction and methods
DE19681246T1 (en) 1995-12-25 1998-01-22 Matsushita Electric Works Ltd An apparatus for effecting a relaxation
US5749921A (en) 1996-02-20 1998-05-12 Medtronic, Inc. Apparatus and methods for compression of endoluminal prostheses
US5762458A (en) 1996-02-20 1998-06-09 Computer Motion, Inc. Method and apparatus for performing minimally invasive cardiac procedures
US6402780B2 (en) 1996-02-23 2002-06-11 Cardiovascular Technologies, L.L.C. Means and method of replacing a heart valve in a minimally invasive manner
US6258119B1 (en) 1996-11-07 2001-07-10 Myocardial Stents, Inc. Implant device for trans myocardial revascularization
US5782844A (en) 1996-03-05 1998-07-21 Inbae Yoon Suture spring device applicator
US5843160A (en) 1996-04-01 1998-12-01 Rhodes; Valentine J. Prostheses for aneurysmal and/or occlusive disease at a bifurcation in a vessel, duct, or lumen
US5824042A (en) 1996-04-05 1998-10-20 Medtronic, Inc. Endoluminal prostheses having position indicating markers
US6949116B2 (en) * 1996-05-08 2005-09-27 Carag Ag Device for plugging an opening such as in a wall of a hollow or tubular organ including biodegradable elements
US5769884A (en) 1996-06-27 1998-06-23 Cordis Corporation Controlled porosity endovascular implant
US5797933A (en) 1996-07-16 1998-08-25 Heartport, Inc. Coronary shunt and method of use
US5702408A (en) 1996-07-17 1997-12-30 Ethicon Endo-Surgery, Inc. Articulating surgical instrument
US5676697A (en) 1996-07-29 1997-10-14 Cardiovascular Dynamics, Inc. Two-piece, bifurcated intraluminal graft for repair of aneurysm
US6482224B1 (en) 1996-08-22 2002-11-19 The Trustees Of Columbia University In The City Of New York Endovascular flexible stapling device
US6984241B2 (en) 1996-09-13 2006-01-10 Tendon Technology, Ltd. Apparatus and methods for tendon or ligament repair
EP0934024B1 (en) 1996-09-20 2006-08-30 United States Surgical Corporation Coil fastener applier
US5830221A (en) * 1996-09-20 1998-11-03 United States Surgical Corporation Coil fastener applier
US5702343A (en) 1996-10-02 1997-12-30 Acorn Medical, Inc. Cardiac reinforcement device
US5861003A (en) * 1996-10-23 1999-01-19 The Cleveland Clinic Foundation Apparatus and method for occluding a defect or aperture within body surface
US6286514B1 (en) 1996-11-05 2001-09-11 Jerome Lemelson System and method for treating select tissue in a living being
US5921979A (en) * 1996-12-18 1999-07-13 Guidant Corporation Apparatus and method for tissue and organ stabilization
US5776142A (en) 1996-12-19 1998-07-07 Medtronic, Inc. Controllable stent delivery system and method
US6352561B1 (en) 1996-12-23 2002-03-05 W. L. Gore & Associates Implant deployment apparatus
US6050936A (en) * 1997-01-02 2000-04-18 Myocor, Inc. Heart wall tension reduction apparatus
US6406420B1 (en) * 1997-01-02 2002-06-18 Myocor, Inc. Methods and devices for improving cardiac function in hearts
US5968053A (en) 1997-01-31 1999-10-19 Cardiac Assist Technologies, Inc. Method and apparatus for implanting a graft in a vessel of a patient
US5855565A (en) 1997-02-21 1999-01-05 Bar-Cohen; Yaniv Cardiovascular mechanically expanding catheter
US5830229A (en) 1997-03-07 1998-11-03 Micro Therapeutics Inc. Hoop stent
US6086582A (en) 1997-03-13 2000-07-11 Altman; Peter A. Cardiac drug delivery system
US6048360A (en) 1997-03-18 2000-04-11 Endotex Interventional Systems, Inc. Methods of making and using coiled sheet graft for single and bifurcated lumens
US6024703A (en) 1997-05-07 2000-02-15 Eclipse Surgical Technologies, Inc. Ultrasound device for axial ranging
WO1998053761A1 (en) 1997-05-26 1998-12-03 William A. Cook Australia Pty. Ltd. A prosthesis and a method and means of deploying a prosthesis
US5906641A (en) 1997-05-27 1999-05-25 Schneider (Usa) Inc Bifurcated stent graft
US5993466A (en) 1997-06-17 1999-11-30 Yoon; Inbae Suturing instrument with multiple rotatably mounted spreadable needle holders
US5997556A (en) 1997-06-30 1999-12-07 Eva Corporation Surgical fastener
US6520974B2 (en) 1997-06-30 2003-02-18 Eva Corporation Surgical fastener
US6248118B1 (en) 1997-06-30 2001-06-19 Eva Corporation Heat activated surgical fastener
US6270516B1 (en) 1997-06-30 2001-08-07 Eva Corporation Repair apparatus for use in surgical procedures
US5957940A (en) 1997-06-30 1999-09-28 Eva Corporation Fasteners for use in the surgical repair of aneurysms
US5944750A (en) 1997-06-30 1999-08-31 Eva Corporation Method and apparatus for the surgical repair of aneurysms
US5904713A (en) 1997-07-14 1999-05-18 Datascope Investment Corp. Invertible bifurcated stent/graft and method of deployment
US5906619A (en) 1997-07-24 1999-05-25 Medtronic, Inc. Disposable delivery device for endoluminal prostheses
DE19731834A1 (en) 1997-07-24 1999-06-17 Ernst Peter Prof Dr M Strecker implanter
US6070589A (en) 1997-08-01 2000-06-06 Teramed, Inc. Methods for deploying bypass graft stents
EP1009332A2 (en) * 1997-09-04 2000-06-21 Endocore, Inc. Artificial chordae replacement
US6306164B1 (en) 1997-09-05 2001-10-23 C. R. Bard, Inc. Short body endoprosthesis
US5984955A (en) 1997-09-11 1999-11-16 Wisselink; Willem System and method for endoluminal grafting of bifurcated or branched vessels
US6179809B1 (en) 1997-09-24 2001-01-30 Eclipse Surgical Technologies, Inc. Drug delivery catheter with tip alignment
US5972003A (en) 1997-10-01 1999-10-26 Sherwood Services Ag Single-free ligation clip module
US5980548A (en) 1997-10-29 1999-11-09 Kensey Nash Corporation Transmyocardial revascularization system
US6626919B1 (en) 1997-12-29 2003-09-30 Lee L. Swanstrom Method and apparatus for attaching or locking an implant to an anatomic vessel or hollow organ wall
US6395019B2 (en) 1998-02-09 2002-05-28 Trivascular, Inc. Endovascular graft
US6083167A (en) 1998-02-10 2000-07-04 Emory University Systems and methods for providing radiation therapy and catheter guides
US7214230B2 (en) * 1998-02-24 2007-05-08 Hansen Medical, Inc. Flexible instrument
CA2265136C (en) * 1998-03-13 2008-09-09 Juan Carlos Parodi Endovascular device for application of prostheses with sutures
US7591842B2 (en) 1998-03-13 2009-09-22 Aptus Endosystems, Inc. Endovascular prosthesis with suture holder
CA2265131C (en) 1998-03-13 2009-12-22 Juan Carlos Parodi Endovascular prothesis with suture holder
US6074418A (en) 1998-04-20 2000-06-13 St. Jude Medical, Inc. Driver tool for heart valve prosthesis fasteners
US6309403B1 (en) 1998-06-01 2001-10-30 Board Of Trustees Operating Michigan State University Dexterous articulated linkage for surgical applications
US6174323B1 (en) * 1998-06-05 2001-01-16 Broncus Technologies, Inc. Method and assembly for lung volume reduction
CA2272458C (en) 1998-06-25 2008-03-18 Leslie Laszlo Kerek Hoodless electrical socket connector
US6547821B1 (en) * 1998-07-16 2003-04-15 Cardiothoracic Systems, Inc. Surgical procedures and devices for increasing cardiac output of the heart
US6145509A (en) 1998-07-24 2000-11-14 Eva Corporation Depth sensor device for use in a surgical procedure
US6217597B1 (en) 1998-07-24 2001-04-17 Eva Corporation Surgical cutting device and method of using the same
US6544253B1 (en) 1998-07-24 2003-04-08 Eva Corporation Surgical support device and method of using the same
US6077214A (en) * 1998-07-29 2000-06-20 Myocor, Inc. Stress reduction apparatus and method
US6027462A (en) 1998-07-30 2000-02-22 Medtronic, Inc. Method and apparatus for deflecting a screw-in-lead
US7491232B2 (en) 1998-09-18 2009-02-17 Aptus Endosystems, Inc. Catheter-based fastener implantation apparatus and methods with implantation force resolution
US7637932B2 (en) 2001-11-28 2009-12-29 Aptus Endosystems, Inc. Devices, systems, and methods for prosthesis delivery and implantation
US20090112302A1 (en) 2001-11-28 2009-04-30 Josh Stafford Devices, systems, and methods for endovascular staple and/or prosthesis delivery and implantation
US20090138072A1 (en) 2001-11-28 2009-05-28 Michael William Gendreau Devices, systems, and methods for endovascular staple and/or prosthesis delivery and implantation
WO2000016701A1 (en) 1998-09-18 2000-03-30 United States Surgical Corporation Endovascular fastener applicator
US20110087320A1 (en) 2001-11-28 2011-04-14 Aptus Endosystems, Inc. Devices, Systems, and Methods for Prosthesis Delivery and Implantation, Including a Prosthesis Assembly
US9320503B2 (en) 2001-11-28 2016-04-26 Medtronic Vascular, Inc. Devices, system, and methods for guiding an operative tool into an interior body region
US6203550B1 (en) 1998-09-30 2001-03-20 Medtronic, Inc. Disposable delivery device for endoluminal prostheses
EP1117341B1 (en) 1998-09-30 2004-12-29 Bard Peripheral Vascular, Inc. Delivery mechanism for implantable stent
US6273909B1 (en) 1998-10-05 2001-08-14 Teramed Inc. Endovascular graft system
US6152144A (en) * 1998-11-06 2000-11-28 Appriva Medical, Inc. Method and device for left atrial appendage occlusion
JP2000164285A (en) 1998-11-25 2000-06-16 Yazaki Corp Connector having front holder
US6283999B1 (en) 1999-01-29 2001-09-04 Depuy Orthopaedics, Inc. Shoulder prothesis with humeral fracture stem
US6398803B1 (en) 1999-02-02 2002-06-04 Impra, Inc., A Subsidiary Of C.R. Bard, Inc. Partial encapsulation of stents
US6197049B1 (en) 1999-02-17 2001-03-06 Endologix, Inc. Articulating bifurcation graft
US7563267B2 (en) 1999-04-09 2009-07-21 Evalve, Inc. Fixation device and methods for engaging tissue
WO2000060995A9 (en) * 1999-04-09 2002-06-13 Evalve Inc Methods and apparatus for cardiac valve repair
WO2000064357A1 (en) 1999-04-23 2000-11-02 United States Surgical Corporation Second generation coil fastener applier with memory ring
US6287335B1 (en) 1999-04-26 2001-09-11 William J. Drasler Intravascular folded tubular endoprosthesis
US6589279B1 (en) * 1999-04-28 2003-07-08 St. Jude Medical, Inc. Efficient implantation of heart valve prostheses
US6468260B1 (en) 1999-05-07 2002-10-22 Biosense Webster, Inc. Single gear drive bidirectional control handle for steerable catheter
US6986784B1 (en) 1999-05-14 2006-01-17 C. R. Bard, Inc. Implant anchor systems
US6146339A (en) 1999-05-24 2000-11-14 Advanced Cardiovascular Systems Guide wire with operator controllable tip stiffness
US6398802B1 (en) 1999-06-21 2002-06-04 Scimed Life Systems, Inc. Low profile delivery system for stent and graft deployment
US6626899B2 (en) * 1999-06-25 2003-09-30 Nidus Medical, Llc Apparatus and methods for treating tissue
DE60006348T2 (en) 1999-07-16 2004-12-02 Cook Inc., Bloomington Stent for verhedderfreien unfolding
EP1207812A4 (en) * 1999-08-04 2007-06-20 Bard Inc C R Implant and agent delivery device
US20030109770A1 (en) 1999-08-09 2003-06-12 Sharkey Hugh R. Device with a porous membrane for improving cardiac function
US6409757B1 (en) 1999-09-15 2002-06-25 Eva Corporation Method and apparatus for supporting a graft assembly
JP2003509175A (en) * 1999-09-20 2003-03-11 アプリヴァ メディカル、 インク. Method and device for closing the Kan腔 body
US6231561B1 (en) * 1999-09-20 2001-05-15 Appriva Medical, Inc. Method and apparatus for closing a body lumen
US6675037B1 (en) 1999-09-29 2004-01-06 Regents Of The University Of Minnesota MRI-guided interventional mammary procedures
US6652555B1 (en) * 1999-10-27 2003-11-25 Atritech, Inc. Barrier device for covering the ostium of left atrial appendage
US6689150B1 (en) * 1999-10-27 2004-02-10 Atritech, Inc. Filter apparatus for ostium of left atrial appendage
US6423059B1 (en) 1999-11-16 2002-07-23 Sulzer Medica Usa Inc. Radio frequency ablation apparatus with remotely articulating and self-locking electrode wand
US8579966B2 (en) * 1999-11-17 2013-11-12 Medtronic Corevalve Llc Prosthetic valve for transluminal delivery
CA2402504A1 (en) * 2000-03-10 2001-09-20 Paracor Surgical, Inc. Expandable cardiac harness for treating congestive heart failure
US6293906B1 (en) * 2000-01-14 2001-09-25 Acorn Cardiovascular, Inc. Delivery of cardiac constraint jacket
CA2400196A1 (en) 2000-02-15 2001-08-23 Eva Corporation Delivery catheter assembly and method of securing a surgical component to a vessel during a surgical procedure
US6319278B1 (en) 2000-03-03 2001-11-20 Stephen F. Quinn Low profile device for the treatment of vascular abnormalities
JP5108999B2 (en) 2000-03-14 2012-12-26 クック メディカル テクノロジーズ エルエルシーCook Medical Technologies Llc Stent graft member
ES2618782T3 (en) 2000-04-13 2017-06-22 Cube S.R.L. endoventricular device for the treatment and correction of cardiomyopathies
US6454796B1 (en) 2000-05-05 2002-09-24 Endovascular Technologies, Inc. Vascular graft
US6425856B1 (en) * 2000-05-10 2002-07-30 Acorn Cardiovascular, Inc. Cardiac disease treatment and device
US6209550B1 (en) * 2000-06-20 2001-04-03 Walter J. Powell, Jr. Flossing tool
DE10034105C1 (en) 2000-07-13 2002-04-04 Karlsruhe Forschzent Spring tension effector for minimal invasive surgery has pivot device for instrument head controlled via parallel spring band strips coupled to pivot setting mechanism
EP1303231B1 (en) 2000-07-25 2004-10-27 Werner Brenner Vascular anchoring device
US6343605B1 (en) * 2000-08-08 2002-02-05 Scimed Life Systems, Inc. Percutaneous transluminal myocardial implantation device and method
WO2002017796A1 (en) 2000-09-01 2002-03-07 Advanced Vascular Technologies, Llc Vascular bypass grafting instrument and method
US6616684B1 (en) * 2000-10-06 2003-09-09 Myocor, Inc. Endovascular splinting devices and methods
US6730119B1 (en) 2000-10-06 2004-05-04 Board Of Regents Of The University Of Texas System Percutaneous implantation of partially covered stents in aneurysmally dilated arterial segments with subsequent embolization and obliteration of the aneurysm cavity
US6663588B2 (en) 2000-11-29 2003-12-16 C.R. Bard, Inc. Active counterforce handle for use in bidirectional deflectable tip instruments
JP3506676B2 (en) 2001-01-25 2004-03-15 Necエレクトロニクス株式会社 Semiconductor device
US6994093B2 (en) * 2001-02-28 2006-02-07 Chase Medical, L.P. Ventricular restoration shaping apparatus and method of use
US20040138734A1 (en) 2001-04-11 2004-07-15 Trivascular, Inc. Delivery system and method for bifurcated graft
US6926732B2 (en) 2001-06-01 2005-08-09 Ams Research Corporation Stent delivery device and method
FR2826863B1 (en) 2001-07-04 2003-09-26 Jacques Seguin An assembly for the introduction of a prosthetic valve in a body conduit
US6675809B2 (en) * 2001-08-27 2004-01-13 Richard S. Stack Satiation devices and methods
US20040243170A1 (en) * 2001-09-05 2004-12-02 Mitta Suresh Method and device for percutaneous surgical ventricular repair
EP1424958A2 (en) * 2001-09-10 2004-06-09 Paracor Medical, Inc. Cardiac harness
US6685620B2 (en) * 2001-09-25 2004-02-03 The Foundry Inc. Ventricular infarct assist device and methods for using it
US7060023B2 (en) * 2001-09-25 2006-06-13 The Foundry Inc. Pericardium reinforcing devices and methods of using them
US7144363B2 (en) * 2001-10-16 2006-12-05 Extensia Medical, Inc. Systems for heart treatment
US20030074055A1 (en) 2001-10-17 2003-04-17 Haverkost Patrick A. Method and system for fixation of endoluminal devices
US20070073389A1 (en) 2001-11-28 2007-03-29 Aptus Endosystems, Inc. Endovascular aneurysm devices, systems, and methods
CN101352375A (en) 2001-11-28 2009-01-28 阿普特斯内系统公司 Endovascular aneurysm repair system
US8075570B2 (en) 2001-11-28 2011-12-13 Aptus Endosystems, Inc. Intraluminal prosthesis attachment systems and methods
US20050177180A1 (en) 2001-11-28 2005-08-11 Aptus Endosystems, Inc. Devices, systems, and methods for supporting tissue and/or structures within a hollow body organ
GB2417208B (en) 2001-11-28 2006-06-28 Aptus Endosystems Inc Intraluminal prosthesis attachment systems
US8231639B2 (en) 2001-11-28 2012-07-31 Aptus Endosystems, Inc. Systems and methods for attaching a prosthesis within a body lumen or hollow organ
CN101360466A (en) 2005-10-20 2009-02-04 阿普特斯内系统公司 Devices, systems, and methods for prosthesis delivery and implantation, including a prosthesis assembly
EP2349086B1 (en) 2008-10-16 2017-03-22 Medtronic Vascular, Inc. Devices and systems for endovascular staple and/or prosthesis delivery and implantation
EP2349087A4 (en) 2008-10-16 2016-09-14 Medtronic Vascular Inc Devices, systems, and methods for endovascular staple and/or prosthesis delivery and implantation
US6929661B2 (en) 2001-11-28 2005-08-16 Aptus Endosystems, Inc. Multi-lumen prosthesis systems and methods
CN101466316B (en) 2005-10-20 2012-06-27 阿普特斯内系统公司 Devices systems and methods for prosthesis delivery and implantation including the use of a fastener tool
US7128754B2 (en) 2001-11-28 2006-10-31 Aptus Endosystems, Inc. Catheter-based fastener implantation apparatus and methods
CN102188296A (en) 2005-10-20 2011-09-21 阿普特斯内系统公司 Devices, systems, and methods for prosthesis delivery and implantation
WO2010044854A1 (en) 2008-10-16 2010-04-22 Aptus Endosystems, Inc. Devices, systems, and methods for endovascular staple and/or prosthesis delivery and implantation
CA2464048C (en) 2001-11-28 2010-06-15 Lee Bolduc Endovascular aneurysm repair system
US20050070992A1 (en) 2001-11-28 2005-03-31 Aptus Endosystems, Inc. Prosthesis systems and methods sized and configured for the receipt and retention of fasteners
US6719174B1 (en) 2001-12-26 2004-04-13 Anorad Corporation Rotary and/or linear actuator system for controlling operation of an associated tool
US6764510B2 (en) * 2002-01-09 2004-07-20 Myocor, Inc. Devices and methods for heart valve treatment
EP1471844A2 (en) 2002-01-16 2004-11-03 Eva Corporation Catheter hand-piece apparatus and method of using the same
WO2003079935A1 (en) 2002-03-18 2003-10-02 Eva Corporation Method and apparatus to attach an unsupported surgical component
US7077850B2 (en) * 2002-05-01 2006-07-18 Scimed Life Systems, Inc. Tissue fastening devices and related insertion tools and methods
WO2003101518A1 (en) 2002-05-29 2003-12-11 William A. Cook Australia Pty. Ltd. Trigger wire system for a prosthesis deployment device
US7264632B2 (en) 2002-06-07 2007-09-04 Medtronic Vascular, Inc. Controlled deployment delivery system
US6986775B2 (en) * 2002-06-13 2006-01-17 Guided Delivery Systems, Inc. Devices and methods for heart valve repair
US7166122B2 (en) 2002-06-27 2007-01-23 Boston Scientific Scimed, Inc. Anchor assemblies in stretch-resistant vaso-occlusive coils
JP4109030B2 (en) 2002-07-19 2008-06-25 オリンパス株式会社 Clip apparatus of living tissue
US6746460B2 (en) * 2002-08-07 2004-06-08 Satiety, Inc. Intra-gastric fastening devices
US20040044364A1 (en) * 2002-08-29 2004-03-04 Devries Robert Tissue fasteners and related deployment systems and methods
US7033384B2 (en) * 2002-08-30 2006-04-25 Satiety, Inc. Stented anchoring of gastric space-occupying devices
WO2004021872A3 (en) 2002-09-06 2004-12-02 Bard Inc C R Tissue capturing devices
US7070591B2 (en) 2002-09-17 2006-07-04 Transoma Medical, Inc. Vascular access port with physiological sensor
JP4648704B2 (en) 2002-09-30 2011-03-09 ボード・オブ・リージエンツ,ザ・ユニバーシテイ・オブ・テキサス・システム The stent delivery system and how to use them.
US7335213B1 (en) * 2002-11-15 2008-02-26 Abbott Cardiovascular Systems Inc. Apparatus and methods for heart valve repair
US7485143B2 (en) 2002-11-15 2009-02-03 Abbott Cardiovascular Systems Inc. Apparatuses and methods for heart valve repair
US7404824B1 (en) * 2002-11-15 2008-07-29 Advanced Cardiovascular Systems, Inc. Valve aptation assist device
US7037343B2 (en) * 2002-12-23 2006-05-02 Python, Inc. Stomach prosthesis
US7611528B2 (en) 2003-01-24 2009-11-03 Medtronic Vascular, Inc. Stent-graft delivery system
US20040254594A1 (en) 2003-01-24 2004-12-16 Arthur Alfaro Cardiac defect occlusion device
WO2004082538A2 (en) * 2003-03-18 2004-09-30 St. Jude Medical, Inc. Body tissue remodeling apparatus
US7159593B2 (en) * 2003-04-17 2007-01-09 3F Therapeutics, Inc. Methods for reduction of pressure effects of cardiac tricuspid valve regurgitation
US7537592B2 (en) * 2003-06-20 2009-05-26 Plc Medical Systems, Inc. Endovascular tissue removal device
US7179225B2 (en) 2003-08-26 2007-02-20 Shluzas Alan E Access systems and methods for minimally invasive surgery
US7753922B2 (en) * 2003-09-04 2010-07-13 Guided Delivery Systems, Inc. Devices and methods for cardiac annulus stabilization and treatment
EP1682045A2 (en) 2003-10-23 2006-07-26 Peacock, James C., III Stent-graft assembly formed in-situ
US7147657B2 (en) 2003-10-23 2006-12-12 Aptus Endosystems, Inc. Prosthesis delivery systems and methods
US7155295B2 (en) * 2003-11-07 2006-12-26 Paracor Medical, Inc. Cardiac harness for treating congestive heart failure and for defibrillating and/or pacing/sensing
US20050154401A1 (en) 2004-01-08 2005-07-14 Scimed Life Systems, Inc. Suturing device for implantable device
FR2865926B1 (en) 2004-02-11 2006-05-12 Perouse Laboratoires tubular prosthesis.
US7762943B2 (en) * 2004-03-03 2010-07-27 Cardiokinetix, Inc. Inflatable ventricular partitioning device
US7761138B2 (en) 2004-03-12 2010-07-20 Boston Scientific Scimed, Inc. MRI and X-ray visualization
US7306623B2 (en) 2005-01-13 2007-12-11 Medtronic Vascular, Inc. Branch vessel graft design and deployment method
US8702744B2 (en) 2005-05-09 2014-04-22 Nexeon Medsystems, Inc. Apparatus and methods for renal stenting
CN101208551B (en) 2005-07-29 2011-04-13 株式会社开滋Sct Spool
KR101639084B1 (en) 2008-07-08 2016-07-12 니혼 고쥰도가가쿠 가부시키가이샤 Catalyst-imparting liquid for palladium plating

Patent Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5192314A (en) * 1991-12-12 1993-03-09 Daskalakis Michael K Synthetic intraventricular implants and method of inserting
US5865791A (en) * 1995-06-07 1999-02-02 E.P. Technologies Inc. Atrial appendage stasis reduction procedure and devices

Cited By (224)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8657873B2 (en) 1999-08-09 2014-02-25 Cardiokinetix, Inc. System for improving cardiac function
US20030109770A1 (en) * 1999-08-09 2003-06-12 Sharkey Hugh R. Device with a porous membrane for improving cardiac function
US9017394B2 (en) 1999-08-09 2015-04-28 Cardiokinetix, Inc. Retrievable cardiac devices
US20030105384A1 (en) * 1999-08-09 2003-06-05 Sharkey Hugh R. Method of improving cardiac function using a porous membrane
US9872767B2 (en) 1999-08-09 2018-01-23 Edwards Lifesciences Corporation Retrievable cardiac devices
US8747454B2 (en) 1999-08-09 2014-06-10 Cardiokinetix, Inc. System for improving cardiac function
US8377114B2 (en) 1999-08-09 2013-02-19 Cardiokinetix, Inc. Sealing and filling ventricular partitioning devices to improve cardiac function
US20060264980A1 (en) * 1999-08-09 2006-11-23 Alexander Khairkhahan System for improving cardiac function
US8257428B2 (en) 1999-08-09 2012-09-04 Cardiokinetix, Inc. System for improving cardiac function
US8672827B2 (en) 1999-08-09 2014-03-18 Cardiokinetix, Inc. Cardiac device and methods of use thereof
US8246671B2 (en) 1999-08-09 2012-08-21 Cardiokinetix, Inc. Retrievable cardiac devices
US9694121B2 (en) 1999-08-09 2017-07-04 Cardiokinetix, Inc. Systems and methods for improving cardiac function
US7887477B2 (en) 1999-08-09 2011-02-15 Cardiokinetix, Inc. Method of improving cardiac function using a porous membrane
US8500795B2 (en) 1999-08-09 2013-08-06 Cardiokinetix, Inc. Retrievable devices for improving cardiac function
US8500790B2 (en) 1999-08-09 2013-08-06 Cardiokinetix, Inc. Retrievable cardiac devices
US7674222B2 (en) 1999-08-09 2010-03-09 Cardiokinetix, Inc. Cardiac device and methods of use thereof
US8192478B2 (en) 1999-08-09 2012-06-05 Cardiokinetix, Inc. System for improving cardiac function
US8388672B2 (en) 1999-08-09 2013-03-05 Cardiokinetix, Inc. System for improving cardiac function by sealing a partitioning membrane within a ventricle
US9078660B2 (en) 2000-08-09 2015-07-14 Cardiokinetix, Inc. Devices and methods for delivering an endocardial device
US10064696B2 (en) 2000-08-09 2018-09-04 Edwards Lifesciences Corporation Devices and methods for delivering an endocardial device
US8518063B2 (en) 2001-04-24 2013-08-27 Russell A. Houser Arteriotomy closure devices and techniques
US8992567B1 (en) 2001-04-24 2015-03-31 Cardiovascular Technologies Inc. Compressible, deformable, or deflectable tissue closure devices and method of manufacture
US9345460B2 (en) 2001-04-24 2016-05-24 Cardiovascular Technologies, Inc. Tissue closure devices, device and systems for delivery, kits and methods therefor
US9968353B2 (en) 2001-06-04 2018-05-15 Medtronic Vascular, Inc. Catheter based fastener implantation apparatus and methods
US9808250B2 (en) 2001-11-28 2017-11-07 Medtronic Vascular, Inc. Systems and methods for attaching a prosthesis within a body lumen or hollow organ
US9744021B2 (en) 2001-11-28 2017-08-29 Medtronic Vascular, Inc. Devices, systems, and methods for prosthesis delivery and implantation, including the use of a fastener tool
US9320589B2 (en) 2001-11-28 2016-04-26 Medtronic Vascular, Inc. Endovascular aneurysm repair system
US9320503B2 (en) 2001-11-28 2016-04-26 Medtronic Vascular, Inc. Devices, system, and methods for guiding an operative tool into an interior body region
US9023065B2 (en) 2001-11-28 2015-05-05 Aptus Endosystems, Inc. Devices, systems, and methods for supporting tissue and/or structures within a hollow body organ
US8685044B2 (en) 2001-11-28 2014-04-01 Aptus Endosystems, Inc. Systems and methods for attaching a prosthesis with a body lumen or hollow organ
US9320591B2 (en) 2001-11-28 2016-04-26 Medtronic Vascular, Inc. Devices, systems, and methods for prosthesis delivery and implantation, including the use of a fastener tool
US20090112303A1 (en) * 2001-11-28 2009-04-30 Lee Bolduc Devices, systems, and methods for endovascular staple and/or prosthesis delivery and implantation
US20030141933A1 (en) * 2002-01-28 2003-07-31 Ultrarf, Inc. N-way RF power amplifier with increased backoff power and power added efficiency
US9592123B2 (en) 2002-08-01 2017-03-14 Cardiokinetix, Inc. Therapeutic methods and devices following myocardial infarction
US8827892B2 (en) 2002-08-01 2014-09-09 Cardiokinetix, Inc. Therapeutic methods and devices following myocardial infarction
US7862500B2 (en) 2002-08-01 2011-01-04 Cardiokinetix, Inc. Multiple partitioning devices for heart treatment
US8529430B2 (en) 2002-08-01 2013-09-10 Cardiokinetix, Inc. Therapeutic methods and devices following myocardial infarction
US7762943B2 (en) 2004-03-03 2010-07-27 Cardiokinetix, Inc. Inflatable ventricular partitioning device
US7976455B2 (en) 2004-03-03 2011-07-12 Cardiokinetix, Inc. Inflatable ventricular partitioning device
US7942927B2 (en) 2004-03-15 2011-05-17 Baker Medical Research Institute Treating valve failure
US20080288060A1 (en) * 2004-07-06 2008-11-20 Baker Medical Research Institute Treating Valvular Insufficiency
US9332992B2 (en) 2004-08-05 2016-05-10 Cardiokinetix, Inc. Method for making a laminar ventricular partitioning device
US9332993B2 (en) 2004-08-05 2016-05-10 Cardiokinetix, Inc. Devices and methods for delivering an endocardial device
US7897086B2 (en) 2004-08-05 2011-03-01 Cardiokinetix, Inc. Method of making a laminar ventricular partitioning device
US20060135968A1 (en) * 2004-11-15 2006-06-22 Laurent Schaller Catheter-based tissue remodeling devices and methods
US20060135966A1 (en) * 2004-11-15 2006-06-22 Laurent Schaller Catheter-based tissue remodeling devices and methods
US7374530B2 (en) 2004-11-15 2008-05-20 Benvenue Medical Inc. Catheter-based tissue remodeling devices and methods
US20060135970A1 (en) * 2004-11-15 2006-06-22 Laurent Schaller Catheter-based tissue remodeling devices and methods
US7452325B2 (en) * 2004-11-15 2008-11-18 Benvenue Medical Inc. Catheter-based tissue remodeling devices and methods
US8391996B2 (en) 2004-11-15 2013-03-05 Benvenue Medical, Inc. Catheter-based tissue remodeling devices and methods
US20100298929A1 (en) * 2005-02-07 2010-11-25 Thornton Troy L Methods, systems and devices for cardiac valve repair
US9526613B2 (en) 2005-03-17 2016-12-27 Valtech Cardio Ltd. Mitral valve treatment techniques
US9107658B2 (en) * 2005-04-22 2015-08-18 Benvenue Medical, Inc. Catheter-based tissue remodeling devices and methods
US8333777B2 (en) * 2005-04-22 2012-12-18 Benvenue Medical, Inc. Catheter-based tissue remodeling devices and methods
US20070112425A1 (en) * 2005-04-22 2007-05-17 Laurent Schaller Catheter-based tissue remodeling devices and methods
US20130103055A1 (en) * 2005-04-22 2013-04-25 Benvenue Medical, Inc. Catheter-based tissue remodeling devices and methods
US20060247764A1 (en) * 2005-04-27 2006-11-02 Bioventrix, A Chf Technologies Company, Inc. A Carlifornia Corporation System and method for sizing a heart for treating congestive heart failure
US8398537B2 (en) 2005-06-10 2013-03-19 Cardiokinetix, Inc. Peripheral seal for a ventricular partitioning device
US20060281965A1 (en) * 2005-06-10 2006-12-14 Alexander Khairkhahan Peripheral seal for a ventricular partitioning device
US20070066863A1 (en) * 2005-08-31 2007-03-22 Medtronic Vascular, Inc. Device for treating mitral valve regurgitation
US20080188874A1 (en) * 2005-09-09 2008-08-07 University Of South Florida Laparoscopic hernia mesh spreader
US8097008B2 (en) * 2005-09-09 2012-01-17 University Of South Florida Laparoscopic hernia mesh spreader
WO2007084411A2 (en) * 2006-01-13 2007-07-26 Erickson Ty B Needle driver and assembly
WO2007084411A3 (en) * 2006-01-13 2007-09-27 Ty B Erickson Needle driver and assembly
US7938767B2 (en) 2006-02-06 2011-05-10 Northwind Ventures Systems and methods for volume reduction
US20110178362A1 (en) * 2006-02-06 2011-07-21 Evans Michael A Systems and methods for volume reduction
US20080293996A1 (en) * 2006-02-06 2008-11-27 Evans Michael A Systems and methods for volume reduction
US8337524B2 (en) 2006-02-21 2012-12-25 Kardium Inc. Method and device for closing holes in tissue
US9572557B2 (en) 2006-02-21 2017-02-21 Kardium Inc. Method and device for closing holes in tissue
US20070244556A1 (en) * 2006-04-12 2007-10-18 Medtronic Vascular, Inc. Annuloplasty Device Having a Helical Anchor and Methods for its Use
WO2007121314A2 (en) * 2006-04-12 2007-10-25 Medtronic Vascular, Inc. Annuloplasty device having a helical anchor and methods for its use
WO2007121314A3 (en) * 2006-04-12 2008-02-07 Medtronic Vascular Inc Annuloplasty device having a helical anchor and methods for its use
US20070244555A1 (en) * 2006-04-12 2007-10-18 Medtronic Vascular, Inc. Annuloplasty Device Having a Helical Anchor and Methods for its Use
US20070244553A1 (en) * 2006-04-12 2007-10-18 Medtronic Vascular, Inc. Annuloplasty Device Having a Helical Anchor and Methods for its Use
JP2009538638A (en) * 2006-04-12 2009-11-12 メドトロニック ヴァスキュラー インコーポレイテッド Annuloplasty apparatus and methods of use thereof with a helical anchor
US8454683B2 (en) 2006-04-12 2013-06-04 Medtronic Vascular, Inc. Annuloplasty device having a helical anchor and methods for its use
US9375218B2 (en) 2006-05-03 2016-06-28 Datascope Corp. Systems and methods of tissue closure
US9192468B2 (en) 2006-06-28 2015-11-24 Kardium Inc. Method for anchoring a mitral valve
US8672998B2 (en) 2006-06-28 2014-03-18 Kardium Inc. Method for anchoring a mitral valve
US8449605B2 (en) 2006-06-28 2013-05-28 Kardium Inc. Method for anchoring a mitral valve
US20110087203A1 (en) * 2006-08-02 2011-04-14 Kardium Inc. System for improving diastolic dysfunction
US20100099947A1 (en) * 2006-08-28 2010-04-22 Olympus Medical Systems Corp. Fistulectomy method of forming a fistula between a first duct and a second duct
US8876699B2 (en) 2006-08-28 2014-11-04 Olympus Medical Systems Corp. Fistulectomy method of forming a fistula between a first duct and a second duct
US20080051626A1 (en) * 2006-08-28 2008-02-28 Olympus Medical Systems Corp. Fistulectomy method between first duct and second duct, ultrasonic endoscope, catheter with balloon, magnet retaining device, and magnet set
US20080312750A1 (en) * 2006-10-04 2008-12-18 Michael Laufer Methods and devices for reconfiguring a body organ
US8882789B2 (en) 2006-10-04 2014-11-11 Ethicon Endo-Surgery, Inc. Methods and systems for tissue manipulation
US20090018389A1 (en) * 2006-10-04 2009-01-15 Michael Laufer Methods and systems for tissue manipulation
US8926641B2 (en) * 2006-10-04 2015-01-06 Ethicon Endo-Surgery, Inc. Methods and devices for reconfiguring a body organ
US20170095333A1 (en) * 2006-10-04 2017-04-06 Edwards Lifesciences Corporation Method and apparatus for reshaping a ventricle
US8480558B2 (en) 2006-11-06 2013-07-09 Caldera Medical, Inc. Implants and procedures for treatment of pelvic floor disorders
US9554885B2 (en) 2006-11-06 2017-01-31 Caldera Medical, Inc. Implants and procedures for treatment of pelvic floor disorders
US20080177132A1 (en) * 2006-11-06 2008-07-24 Caldera Medical, Inc. Implants And Procedures For Treatment Of Pelvic Floor Disorders
US9149352B2 (en) 2006-11-06 2015-10-06 Caldera Medical, Inc. Implants and procedures for treatment of pelvic floor disorders
US9883943B2 (en) 2006-12-05 2018-02-06 Valtech Cardio, Ltd. Implantation of repair devices in the heart
US8926695B2 (en) 2006-12-05 2015-01-06 Valtech Cardio, Ltd. Segmented ring placement
US9351830B2 (en) * 2006-12-05 2016-05-31 Valtech Cardio, Ltd. Implant and anchor placement
US9872769B2 (en) 2006-12-05 2018-01-23 Valtech Cardio, Ltd. Implantation of repair devices in the heart
US20150081014A1 (en) * 2006-12-05 2015-03-19 Valtech Cardio, Ltd. Implant and anchor placement
US9974653B2 (en) 2006-12-05 2018-05-22 Valtech Cardio, Ltd. Implantation of repair devices in the heart
US9572667B2 (en) * 2007-02-14 2017-02-21 Edwards Lifesciences Corporation Suture and method for repairing a heart
US20130110230A1 (en) * 2007-02-14 2013-05-02 Edwards Lifesciences Corporation Suture and method for repairing a heart
US20170119368A1 (en) * 2007-02-14 2017-05-04 Edwards Lifesciences Corporation Suture and method for repairing a heart
US20080249539A1 (en) * 2007-04-04 2008-10-09 Stokes Michael J Device for plicating and fastening gastric tissue
US7815653B2 (en) 2007-04-04 2010-10-19 Ethicon Endo-Surgery, Inc. Method for plicating and fastening gastric tissue
US7722628B2 (en) 2007-04-04 2010-05-25 Ethicon Endo-Surgery, Inc. Device for plicating and fastening gastric tissue
US7803166B2 (en) 2007-04-04 2010-09-28 Ethicon Endo-Surgery, Inc. Method for plicating and fastening gastric tissue
US20080249560A1 (en) * 2007-04-04 2008-10-09 Stokes Michael J Method for plicating and fastening gastric tissue
US20080249561A1 (en) * 2007-04-04 2008-10-09 Stokes Michael J Method for plicating and fastening gastric tissue
US20080249541A1 (en) * 2007-04-04 2008-10-09 Stokes Michael J Device for plicating and fastening gastric tissue
US7799040B2 (en) 2007-04-04 2010-09-21 Ethicon Endo-Surgery, Inc. Device for plicating and fastening gastric tissue
US7951159B2 (en) 2007-04-04 2011-05-31 Ethicon Endo-Surgery, Inc. Method for plicating and fastening gastric tissue
US20080249542A1 (en) * 2007-04-04 2008-10-09 Stokes Michael J Device for plicating and fastening gastric tissue
US7803165B2 (en) 2007-04-04 2010-09-28 Ethicon Endo-Surgery, Inc. Device for plicating and fastening gastric tissue
US20080249540A1 (en) * 2007-04-04 2008-10-09 Stokes Michael J Method for plicating and fastening gastric tissue
US9730792B2 (en) 2007-09-13 2017-08-15 Georg Lutter Truncated cone heart valve stent
US9095433B2 (en) 2007-09-13 2015-08-04 Georg Lutter Truncated cone heart valve stent
US9254192B2 (en) 2007-09-13 2016-02-09 Georg Lutter Truncated cone heart valve stent
US9078749B2 (en) 2007-09-13 2015-07-14 Georg Lutter Truncated cone heart valve stent
WO2009055015A1 (en) * 2007-10-25 2009-04-30 Synecor, Llc Implantable device for delivery of therapeutic agents
US8496684B2 (en) 2007-10-31 2013-07-30 Ethicon Endo-Surgery, Inc. Method for deploying a device for gastric volume reduction
US20090118762A1 (en) * 2007-10-31 2009-05-07 Lawrence Crainch Disposable cartridge for use in a gastric volume reduction procedure
US20090112232A1 (en) * 2007-10-31 2009-04-30 Lawrence Crainich Method for Deploying A Device For Gastric Volume Reduction
US8961541B2 (en) 2007-12-03 2015-02-24 Cardio Vascular Technologies Inc. Vascular closure devices, systems, and methods of use
US9452048B2 (en) * 2008-04-15 2016-09-27 Medtronic Vascular, Inc. Devices and methods for treating valvular regurgitation
US20140309729A1 (en) * 2008-04-15 2014-10-16 Medtronic Vascular, Inc. Devices and Methods for Treating Valvular Regurgitation
US8795352B2 (en) * 2008-04-15 2014-08-05 Medtronic Vascular, Inc. Devices and methods for treating valvular regurgitation
US20090259304A1 (en) * 2008-04-15 2009-10-15 Medtronic Vascular, Inc. Devices and Methods for Treating Valvular Regurgitation
US20100030328A1 (en) * 2008-04-18 2010-02-04 Medtronic, Inc. Apparatus for Treating a Heart Valve, in Particular a Mitral Valve
US8632585B2 (en) 2008-04-18 2014-01-21 Medtronic Corevalve, Inc. Apparatus for treating a heart valve, in particular a mitral valve
US8262724B2 (en) 2008-04-18 2012-09-11 Medtronic Corevalve, Inc. Apparatus for treating a heart valve, in particular a mitral valve
US7972370B2 (en) 2008-04-24 2011-07-05 Medtronic Vascular, Inc. Stent graft system and method of use
US9744038B2 (en) 2008-05-13 2017-08-29 Kardium Inc. Medical device for constricting tissue or a bodily orifice, for example a mitral valve
US9192472B2 (en) 2008-06-16 2015-11-24 Valtec Cardio, Ltd. Annuloplasty devices and methods of delivery therefor
US9277994B2 (en) 2008-12-22 2016-03-08 Valtech Cardio, Ltd. Implantation of repair chords in the heart
US9713530B2 (en) 2008-12-22 2017-07-25 Valtech Cardio, Ltd. Adjustable annuloplasty devices and adjustment mechanisms therefor
US9636224B2 (en) 2008-12-22 2017-05-02 Valtech Cardio, Ltd. Deployment techniques for annuloplasty ring and over-wire rotation tool
US9662209B2 (en) 2008-12-22 2017-05-30 Valtech Cardio, Ltd. Contractible annuloplasty structures
US8758220B2 (en) 2009-01-05 2014-06-24 Caldera Medical, Inc. Implants and procedures for supporting anatomical structures for treating conditions such as pelvic organ prolapse
US20100191046A1 (en) * 2009-01-05 2010-07-29 Caldera Medical, Inc. Implants And Procedures For Supporting Anatomical Structures
US20100185278A1 (en) * 2009-01-21 2010-07-22 Tendyne Medical Apical Papillary Msucle Attachment for Left Ventricular Reduction
US9561104B2 (en) 2009-02-17 2017-02-07 Valtech Cardio, Ltd. Actively-engageable movement-restriction mechanism for use with an annuloplasty structure
US8518060B2 (en) * 2009-04-09 2013-08-27 Medtronic, Inc. Medical clip with radial tines, system and method of using same
US20100262167A1 (en) * 2009-04-09 2010-10-14 Medtronic, Inc. Medical Clip with Radial Tines, System and Method of Using Same
US9968452B2 (en) 2009-05-04 2018-05-15 Valtech Cardio, Ltd. Annuloplasty ring delivery cathethers
US9474606B2 (en) 2009-05-04 2016-10-25 Valtech Cardio, Ltd. Over-wire implant contraction methods
US9592122B2 (en) 2009-05-07 2017-03-14 Valtech Cardio, Ltd Annuloplasty ring with intra-ring anchoring
US9119719B2 (en) 2009-05-07 2015-09-01 Valtech Cardio, Ltd. Annuloplasty ring with intra-ring anchoring
US9937042B2 (en) 2009-05-07 2018-04-10 Valtech Cardio, Ltd. Multiple anchor delivery tool
US9050078B2 (en) * 2009-06-21 2015-06-09 Aesthetics Point Ltd. Implanted medical device useful for cosmetic surgery
US20120172931A1 (en) * 2009-06-21 2012-07-05 Aesthetics Point Ltd. implanted medical device useful for cosmetic surgery
US9023067B2 (en) 2009-07-10 2015-05-05 Educational Foundation Jichi Medical University Surgical system for stoma closure in biological duct
US8459524B2 (en) 2009-08-14 2013-06-11 Covidien Lp Tissue fastening system for a medical device
US20110036888A1 (en) * 2009-08-14 2011-02-17 Tyco Healthcare Group Lp Tissue fastening system for a medical device
US9539008B2 (en) 2009-08-14 2017-01-10 Covidien Lp Tissue fastening system for a medical device
US9867703B2 (en) 2009-10-01 2018-01-16 Kardium Inc. Medical device, kit and method for constricting tissue or a bodily orifice, for example, a mitral valve
US9204964B2 (en) 2009-10-01 2015-12-08 Kardium Inc. Medical device, kit and method for constricting tissue or a bodily orifice, for example, a mitral valve
US20110082538A1 (en) * 2009-10-01 2011-04-07 Jonathan Dahlgren Medical device, kit and method for constricting tissue or a bodily orifice, for example, a mitral valve
WO2011047201A3 (en) * 2009-10-14 2011-08-18 Tendyne Medical, Inc. Devices and methods for treatment of cardiomyopathy
WO2011047201A2 (en) * 2009-10-14 2011-04-21 Tendyne Medical, Inc. Devices and methods for treatment of cardiomyopathy
US9364327B2 (en) 2009-10-26 2016-06-14 Cardiokinetix, Inc. Ventricular volume reduction
US8790242B2 (en) 2009-10-26 2014-07-29 Cardiokinetix, Inc. Ventricular volume reduction
US10028835B2 (en) 2009-10-26 2018-07-24 Edwards Lifesciences Corporation Ventricular volume reduction
US9039597B2 (en) 2009-10-26 2015-05-26 Cardiokinetix, Inc. Ventricular volume reduction
US9414921B2 (en) 2009-10-29 2016-08-16 Valtech Cardio, Ltd. Tissue anchor for annuloplasty device
US9968454B2 (en) 2009-10-29 2018-05-15 Valtech Cardio, Ltd. Techniques for guide-wire based advancement of artificial chordae
US20180116797A9 (en) * 2009-10-29 2018-05-03 Valtech Cardio, Ltd. Tissue anchor for annuloplasty device
US9622861B2 (en) 2009-12-02 2017-04-18 Valtech Cardio, Ltd. Tool for actuating an adjusting mechanism
US9980708B2 (en) 2010-01-20 2018-05-29 Micro Interventional Devices, Inc. Tissue closure device and method
US10058314B2 (en) 2010-01-20 2018-08-28 Micro Interventional Devices, Inc. Tissue closure device and method
US9427220B2 (en) 2010-01-20 2016-08-30 Micro Interventional Devices, Inc. Tissue repair implant and delivery device and method
EP2525725A4 (en) * 2010-01-20 2015-10-07 New Hope Ventures Lp Tissue repair implant and delivery device and method
US10058323B2 (en) 2010-01-22 2018-08-28 4 Tech Inc. Tricuspid valve repair using tension
US20170079797A1 (en) * 2010-01-22 2017-03-23 4 Tech Inc. Tricuspid valve repair using tension
US20140114390A1 (en) * 2010-01-22 2014-04-24 4Tech Inc. Tricuspid valve repair using tension
US9307980B2 (en) * 2010-01-22 2016-04-12 4Tech Inc. Tricuspid valve repair using tension
US20110208298A1 (en) * 2010-02-24 2011-08-25 Medtronic Ventor Technologies Ltd Mitral Prosthesis and Methods for Implantation
US9072603B2 (en) 2010-02-24 2015-07-07 Medtronic Ventor Technologies, Ltd. Mitral prosthesis and methods for implantation
US20110208297A1 (en) * 2010-02-24 2011-08-25 Medtronic Ventor Technologies Ltd. Mitral Prosthesis and Methods for Implantation
US8357195B2 (en) 2010-04-15 2013-01-22 Medtronic, Inc. Catheter based annuloplasty system and method
US9795482B2 (en) 2010-04-27 2017-10-24 Medtronic, Inc. Prosthetic heart valve devices and methods of valve repair
US9918706B2 (en) 2010-06-07 2018-03-20 Kardium Inc. Closing openings in anatomical tissue
US9050066B2 (en) 2010-06-07 2015-06-09 Kardium Inc. Closing openings in anatomical tissue
US9795480B2 (en) 2010-08-24 2017-10-24 Millipede, Inc. Reconfiguring tissue features of a heart annulus
US8940002B2 (en) 2010-09-30 2015-01-27 Kardium Inc. Tissue anchor system
US9345470B2 (en) 2011-03-01 2016-05-24 Medtronic Ventor Technologies Ltd. Self-suturing anchors
US8454656B2 (en) 2011-03-01 2013-06-04 Medtronic Ventor Technologies Ltd. Self-suturing anchors
US9737397B2 (en) 2011-03-01 2017-08-22 Medtronic Ventor Technologies, Ltd. Mitral valve repair
US9445898B2 (en) 2011-03-01 2016-09-20 Medtronic Ventor Technologies Ltd. Mitral valve repair
US10058318B2 (en) 2011-03-25 2018-08-28 Kardium Inc. Medical kit for constricting tissue or a bodily orifice, for example, a mitral valve
US9072511B2 (en) 2011-03-25 2015-07-07 Kardium Inc. Medical kit for constricting tissue or a bodily orifice, for example, a mitral valve
US9918840B2 (en) 2011-06-23 2018-03-20 Valtech Cardio, Ltd. Closed band for percutaneous annuloplasty
US9833315B2 (en) 2011-08-11 2017-12-05 Tendyne Holdings, Inc. Prosthetic valves and related inventions
US9480559B2 (en) 2011-08-11 2016-11-01 Tendyne Holdings, Inc. Prosthetic valves and related inventions
US9265608B2 (en) 2011-11-04 2016-02-23 Valtech Cardio, Ltd. Implant having multiple rotational assemblies
US9775709B2 (en) 2011-11-04 2017-10-03 Valtech Cardio, Ltd. Implant having multiple adjustable mechanisms
US8858623B2 (en) * 2011-11-04 2014-10-14 Valtech Cardio, Ltd. Implant having multiple rotational assemblies
US20130116780A1 (en) * 2011-11-04 2013-05-09 Valtech Cardio, Ltd. Implant having multiple rotational assemblies
US9724192B2 (en) 2011-11-08 2017-08-08 Valtech Cardio, Ltd. Controlled steering functionality for implant-delivery tool
US9827092B2 (en) 2011-12-16 2017-11-28 Tendyne Holdings, Inc. Tethers for prosthetic mitral valve
US9895221B2 (en) 2012-07-28 2018-02-20 Tendyne Holdings, Inc. Multi-component designs for heart valve retrieval device, sealing structures and stent assembly
US9675454B2 (en) 2012-07-30 2017-06-13 Tendyne Holdings, Inc. Delivery systems and methods for transcatheter prosthetic valves
US9949828B2 (en) 2012-10-23 2018-04-24 Valtech Cardio, Ltd. Controlled steering functionality for implant-delivery tool
WO2015069947A1 (en) * 2012-11-07 2015-05-14 Nasser Rafiee Devices, systems and methods for repairing lumenal systems
US9730793B2 (en) 2012-12-06 2017-08-15 Valtech Cardio, Ltd. Techniques for guide-wire based advancement of a tool
US9693865B2 (en) 2013-01-09 2017-07-04 4 Tech Inc. Soft tissue depth-finding tool
US9788948B2 (en) 2013-01-09 2017-10-17 4 Tech Inc. Soft tissue anchors and implantation techniques
US9907681B2 (en) 2013-03-14 2018-03-06 4Tech Inc. Stent with tether interface
US9486306B2 (en) 2013-04-02 2016-11-08 Tendyne Holdings, Inc. Inflatable annular sealing device for prosthetic mitral valve
US9610159B2 (en) 2013-05-30 2017-04-04 Tendyne Holdings, Inc. Structural members for prosthetic mitral valves
US9597181B2 (en) 2013-06-25 2017-03-21 Tendyne Holdings, Inc. Thrombus management and structural compliance features for prosthetic heart valves
US9655709B2 (en) 2013-09-26 2017-05-23 Covidien Lp Mesh deployment devices and kits
US9526611B2 (en) 2013-10-29 2016-12-27 Tendyne Holdings, Inc. Apparatus and methods for delivery of transcatheter prosthetic valves
US10039643B2 (en) 2013-10-30 2018-08-07 4Tech Inc. Multiple anchoring-point tension system
US10022114B2 (en) 2013-10-30 2018-07-17 4Tech Inc. Percutaneous tether locking
US10052095B2 (en) 2013-10-30 2018-08-21 4Tech Inc. Multiple anchoring-point tension system
US9610162B2 (en) 2013-12-26 2017-04-04 Valtech Cardio, Ltd. Implantation of flexible implant
US9986993B2 (en) 2014-02-11 2018-06-05 Tendyne Holdings, Inc. Adjustable tether and epicardial pad system for prosthetic heart valve
US10045765B2 (en) 2014-03-27 2018-08-14 Transmural Systems Llc Devices and methods for closure of transvascular or transcameral access ports
US10058315B2 (en) 2014-03-27 2018-08-28 Transmural Systems Llc Devices and methods for closure of transvascular or transcameral access ports
US9801720B2 (en) 2014-06-19 2017-10-31 4Tech Inc. Cardiac tissue cinching
US9913706B2 (en) 2014-07-17 2018-03-13 Millipede, Inc. Adjustable endolumenal implant for reshaping the mitral valve annulus
US9907547B2 (en) 2014-12-02 2018-03-06 4Tech Inc. Off-center tissue anchors
US9848983B2 (en) 2015-02-13 2017-12-26 Millipede, Inc. Valve replacement using rotational anchors
US9877833B1 (en) 2016-12-30 2018-01-30 Pipeline Medical Technologies, Inc. Method and apparatus for transvascular implantation of neo chordae tendinae

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