WO2000006027A9 - Heart stress reduction apparatus and method - Google Patents
Heart stress reduction apparatus and methodInfo
- Publication number
- WO2000006027A9 WO2000006027A9 PCT/US1999/016875 US9916875W WO0006027A9 WO 2000006027 A9 WO2000006027 A9 WO 2000006027A9 US 9916875 W US9916875 W US 9916875W WO 0006027 A9 WO0006027 A9 WO 0006027A9
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- heart
- splint
- left ventricle
- stress
- wrap
- Prior art date
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/24—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
- A61F2/2478—Passive devices for improving the function of the heart muscle, i.e. devices for reshaping the external surface of the heart, e.g. bags, strips or bands
- A61F2/2481—Devices outside the heart wall, e.g. bags, strips or bands
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/00234—Surgical instruments, devices or methods, e.g. tourniquets for minimally invasive surgery
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/24—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
- A61F2/2478—Passive devices for improving the function of the heart muscle, i.e. devices for reshaping the external surface of the heart, e.g. bags, strips or bands
- A61F2/2487—Devices within the heart chamber, e.g. splints
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/12—Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
- A61B17/122—Clamps or clips, e.g. for the umbilical cord
- A61B17/1227—Spring clips
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/00234—Surgical instruments, devices or methods, e.g. tourniquets for minimally invasive surgery
- A61B2017/00238—Type of minimally invasive operation
- A61B2017/00243—Type of minimally invasive operation cardiac
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/04—Surgical instruments, devices or methods, e.g. tourniquets for suturing wounds; Holders or packages for needles or suture materials
- A61B17/0401—Suture anchors, buttons or pledgets, i.e. means for attaching sutures to bone, cartilage or soft tissue; Instruments for applying or removing suture anchors
- A61B2017/0404—Buttons
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/04—Surgical instruments, devices or methods, e.g. tourniquets for suturing wounds; Holders or packages for needles or suture materials
- A61B17/0469—Suturing instruments for use in minimally invasive surgery, e.g. endoscopic surgery
- A61B2017/048—Suturing instruments for use in minimally invasive surgery, e.g. endoscopic surgery for reducing heart wall tension, e.g. sutures with a pad on each extremity
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/04—Surgical instruments, devices or methods, e.g. tourniquets for suturing wounds; Holders or packages for needles or suture materials
- A61B2017/0496—Surgical instruments, devices or methods, e.g. tourniquets for suturing wounds; Holders or packages for needles or suture materials for tensioning sutures
Definitions
- ventricular dilatation is generally the result of chronic volume overload or specific damage to the myocardium.
- cardiac output requirements for example, that of an athlete
- there is an adaptive process of ventricular dilation and myocyte hypertrophy In this way, the heart fully compensates for the increased cardiac output requirements.
- damage to the myocardium or chronic volume overload there are increased requirements put on the contracting myocardium to such a level that this compensated state is never achieved and the heart continues to dilate.
- the basic problem with a large dilated left ventricle is that there is a significant increase in wall tension and or stress both during diastolic filling and during systolic contraction.
- the adaptation of muscle hypertrophy (thickening) and ventricular dilatation maintain a fairly constant wall tension for systolic contraction.
- the ongoing dilatation is greater than the hypertrophy and the result is a rising wall tension requirement for systolic contraction. This is felt to be an ongoing insult to the muscle myocyte resulting in further muscle damage.
- the increase in wall stress is also true for diastolic filling.
- Prior art treatments for heart failure fall into three generally categories. The first being pharmacological, for example, diuretics. The second being assist systems, for example, pumps. Finally, surgical treatments have been experimented with, which are described in more detail below.
- diuretics have been used to reduce the workload of the heart by reducing blood volume and preload.
- preload is defined in several ways including left ventricular end diastolic pressure (LVEDP), or left ventricular end diastolic volume (LVEDV).
- LEDP left ventricular end diastolic pressure
- LVEDV left ventricular end diastolic volume
- the preferred definition is the length of stretch of the sarcomere at end diastole.
- Diuretics reduce extra cellular fluid which builds in congestive heart failure patients increasing preload conditions.
- Nitrates, arteriolar vasodilators, angiotensin converting enzyme inhibitors have been used to treat heart failure through the reduction of cardiac workload through the reduction of afterload.
- Afterload may be defined as the tension or stress required in the wall of the ventricle during ejection.
- Inotropes such as digoxin are cardiac glycosides and function to increase cardiac output by increasing the force and speed of cardiac muscle contraction.
- drug therapies offer some beneficial effects but do not stop the progression of the disease.
- Assist devices include, for example, mechanical pumps. Mechanical pumps reduce the load on the heart by performing all or part of the pumping function normally done by the heart. Currently, mechanical pumps are used to sustain the patient while a donor heart for transplantation becomes available for the patient.
- the devices and methods of the present invention can reduce heart wall stress throughout the cardiac cycle including end diastole and end systole. Alternatively, they can be used to reduce wall stress during the portions of the cardiac cycle not including end systole. Those devices which operate throughout the cardiac cycle are referred to herein as “full cycle splints”. Those devices which do not operate to reduce wall stress during end stage systole are referred to as "restrictive devices”. Restrictive devices include both “restrictive splints" which alter the geometric shape of the left ventricle, and “wraps" which merely limit the magnitude of the expansion of the left ventricle during diastolic filling without a substantial shape change.
- FIG. 1 is a vertical side view of a heart including a transventricular splint and band splint;
- Figure 2 is a horizontal cross section of the heart, splint and band splint of Figure
- Figure 5 is an idealized horizontal cross sectional left ventricle splinted to form three lobes
- Figure 8 is a vertical view of a heart including a transventricular splint and a partial band splint;
- Figure 9 is a horizontal cross sectional view of the heart, splint and band splint of Figure 8.
- Figure 11 is a view of the splint of Figure 10 at end diastole;
- Figure 12 is a horizontal cross section of the left ventricle including a full cycle transventricular splint and a restrictive transventricular splint at the beginning of diastolic filling;
- Figure 13 is a view of the splints of Figure 12 at end diastole;
- Figure 14 is a horizontal cross sectional view of the left ventricle including a restrictive splint at the beginning of diastolic filling;
- Figure 15 is a view of the splint of Figure 14 at end diastole;
- Figure 16 is a vertical view of the heart in phantom line including a band splint
- Figure 17 is an alternate embodiment of the band splint of Figure 16;
- Figure 18 is an alternate embodiment of the band splint of Figure 16;
- Figure 19 is an alternate embodiment of the band splint of Figure 16.
- Figure 20 is a vertical view of a heart including a partial circumferential strap
- Figure 21 is a horizontal cross sectional view of the heart and strap of Figure 20;
- Figure 22 is a vertical view of a heart including a vertical partial strap
- Figure 23 is a horizontal cross sectional view of a heart including a transventricular splint passing through the papillary muscles
- Figure 24 is a horizontal cross sectional view of a heart including a
- transventricular splint passing through the left ventricle to lateral the papillary muscles
- Figure 25 is a horizontal cross sectional view of the left ventricle including a plurality of transventricular splints
- Figure 26 is a vertical view of a heart in phantom line including a single element wrap including longitudinal axis securing points;
- Figure 27 is an alternate embodiment of the wrap of Figure 26;
- Figure 28 is an alternate embodiment of the wrap of Figure 26;
- Figure 29 is an alternate embodiment of the wrap of Figure 26;
- Figure 30 is a vertical view of the heart including a mesh wrap
- Figure 31 is a cross sectional view of a patient's torso and heart showing a band splint anchored to the patient's ribs;
- Figure 32 is a partial vertical view of the heart and band splint of Figure 31;
- Figure 33 is a partial vertical view of a failing heart
- Figure 34 is a cross sectional view of the heart of Figure 33;
- Figure 35 is a vertical view of the heart for decreasing the horizontal radius of the ventricles and increasing their vertical length
- Figure 36 is an exaggerated vertical view of the heart of Figure 33 elongated by the device of Figure 35;
- Figure 37 is a view of the cross section of Figure 34 showing the decrease in radius of the ventricles;
- Figure 38 is a horizontal cross sectional view of the heart showing the left and right ventricles and a splint disposed within the myocardium;
- Figure 39 is a vertical cross section of the left ventricle showing a splint within the myocardium
- Figure 40 is a partial cross section of the left ventricle showing a splint extending through a portion of the myocardium;
- Figure 41 is a partial vertical view of a heart showing the splint of Figure 40 extending horizontally through the myocardium;
- Figure 42 is a horizontal cross sectional view of the left and right ventricles including reinforcement loops;
- Figure 43 is an alternate embodiment of the reinforcing loops of Figure 43;
- Figure 44 shows a vertical view of the heart including the reinforcement loops of Figure 43 and a rigid shape changing member
- Figure 45 is a vertical cross sectional view of a heart showing a ring around the chordae.
- the present invention is directed at reducing wall stress in a failing heart.
- Diastolic wall stress is considered to be an initiator of muscle damage and chamber enlargement. For this reason, it is desirable to reduce diastolic wall stress to prevent the progression of the disease.
- the significant impact of stress occurs at all stages and functional levels of heart failure, however, independent of the original causes.
- mechanical stress can lead to symptomatic heart failure marked by an enlarged heart with decreased left ventricle function.
- mechanical stress on the heart wall increases proportionally to the increasing radius of the heart in accordance with LaPlace's Law. It can thus be appreciated that as stress increases in symptomatic heart failure, those factors that contributed to increasing stress also increase.
- the progression of the disease accelerates to late stage heart failure, end stage heart failure and death unless the disease is treated.
- the present invention pertains to devices and methods for directly and passively changing chamber geometry to lower wall stress.
- the devices and methods of the present invention also lend themselves to application in the case of a decrease in cardiac function caused by, for example, acute myocardial infarction.
- the device's disclosed herein for changing chamber geometry are referred to as "splints".
- wraps which can be placed around the heart can limit muscle stress without the chamber shape change. When a wrap is used, wall stress is merely transferred to the wrap, while the generally globular shape of the heart is maintained.
- a wrap could be used in conjunction with a splint to modulate heart wall stress reduction at various stages of the cardiac cycle.
- the present invention includes a number of splint embodiments. Splints and wraps can be classified by where in the cardiac cycle they engage the heart wall, i.e., mechanically limit the size of the left ventricle in the case of wraps and change the geometry of the ventricle in the case of splints.
- the splint can be termed a "restrictive splint”. If the splint or wrap is engaged throughout the cardiac cycle, both during diastolic filling and systolic contraction and ejection, the splint can be termed a "full cycle splint".
- the wrap will generally be a restrictive device which begins to engage during diastolic filling to increase the elastance (reduces compliance) of the chamber. If a wrap is made from elastic material it may engage full cycle, but the force required to elongate the wrap will increase as diastolic filling progresses, preload strain will be reduced without an improvement in systolic contraction.
- Figure 1 is a view of a heart A in a normal, generally vertical orientation.
- a wrap 11 surrounds heart A and a transventricular splint 12 extends through the heart and includes an anchor or anchor pad 13 disposed on opposite sides of the heart.
- Figure 2 is a horizontal cross sectional view of heart A taken through wrap 11 and splint 12.
- Splint 12 includes a tension member 15 extending through left ventricle B.
- Anchor pads 13 are disposed at each end of tension member 15.
- Right ventricle C is to the left of left ventricle B.
- wrap 11 and splint 12 are shown engaged with heart A.
- heart A is shown spaced from wrap 11 except at anchor pads 13.
- heart A is thus at a point in the cardiac cycle where the muscles are shortening during systole, or have yet to stretch sufficiently during diastolic expansion to reach wrap 11. Accordingly, wrap 11 can be considered a restrictive device as it does not engage the heart full cycle.
- wrap 11 is in contact with heart A at pads 13, only the splint is providing a compressive force to change the shape of the heart and limiting the stress of the heart in Figure 2.
- transventricular splint 12 is a full cycle device as the cross section of left ventricle B does not have the generally
- transventricular splint 12 can be used without wrap 11.
- wrap 11 could be secured to heart A by sutures or other means than splint 12, in which case wrap 11 would be merely a restrictive device.
- wrap 11 extends vertically along heart A a sufficient amount, as heart A expands and engages wrap 11, the portion of left ventricle B disposed above or below wrap 11 could expand substantially further than that portion of the left ventricle wall restrained by wrap 11. In such a case, left ventricle B could have a bi-lobed shape in a vertical cross section.
- the wrap 11 would not be merely limiting the size of the left ventricle, but rather inducing a shape change in the left ventricle.
- the element 11 would not be a wrap, but rather a splint which could be referred to as a "band splint”.
- Each of the splints, wraps and other devices disclosed in this application preferably do not substantially deform during the cardiac cycle such that the magnitude of the resistance to the expansion or contraction of the heart provided by these devices is reduced by substantial deflection. It is, however, contemplated that devices which deflect or elongate elastically under load are within the scope of the present invention, though not preferred.
- the materials from which each device are formed must be biocompatible and are preferably configured to be substantially atraumatic.
- Figure 3 is a plot of sarcomere, i.e., heart wall muscle, stress in (g/cm 2 ) versus strain throughout a normal cardiac cycle N, and a failing heart cardiac cycle F.
- the cardiac cycles or loops shown on Figure 3 are bounded by the normal contractility curve N c and failing heart contractility curve F c above and to the left, and the diastolic filling curve 12 toward the bottom and right.
- Contractility is a measure of muscle stress at an attainable systolic stress at a given elongation or strain.
- the diastolic filling curve 12 is a plot of the stress in the muscle tissue at a given elongation or strain when the muscle is at rest.
- N An arbitrary beginning of the normal cardiac cycle N can be chosen at end diastole 14, where the left ventricle is full, the aortic valve is closed. Just after end diastole 14, systole begins, the sarcomere muscles become active and the mitral valve closes, increasing muscle stress without substantially shortening (sometimes referred to as "isovolumic contraction"). Stress increases until the aortic valve opens at 16. Isotonic shortening begins and stress decreases and the muscles shorten until end systole 18, where the blood has been ejected from the left ventricle and the aortic valve closes.
- N s The total muscle shortening and lengthening during the normal cycle N is N s .
- An analogous cycle F also occurs in a failing heart. As the left ventricle has dilated, in accordance with LaPlace's Law, the larger radius of a dilated left ventricle causes stress to increase at a given blood pressure. Consequently, a failing heart must compensate to maintain the blood pressure.
- the compensation for the increased stress is reflected in the shift to the right of failing heart cardiac cycle F relative to the normal cycle N.
- the stress at end diastole 22 is elevated over the stress at end diastole 14 of the normal heart.
- a similar increase can be seen for the point at which the aortic valve opens 24, end systole 26 and the beginning of diastolic filling 28 relative to the analogous points for the normal cycle N.
- Muscle shortening and elongation F s throughout the cycle is also reduced in view of the relative steepening of the diastolic curve 12 to the right and the flatter contractility curve F c relative to the normal contractility N c .
- the effect on mechanical muscle stress and strain caused by the use of the devices and methods of the present invention can be illustrated.
- Restrictive devices begin to engage during diastolic filling, which in the case of a failing heart occurs along diastolic filling curve 12 between point 28 and 22.
- Restrictive devices do not engage at end systole 26.
- the acute effect of placement of a restrictive device is to reduce muscle stress at end diastole relative to the stress at point 22, and shift the line 22-24 to the left reducing muscle shortening and elongation F s .
- the cardiac cycle will still operate between the failing heart contractility curve F c and the diastolic filling curve 12. If chronic muscle contractility increases such that the muscle contractility curve F c shifts back toward the normal heart contractility curve N c as a consequence of the stress reduction, the stress/strain curve F of the cardiac cycle will shift to the left reducing mechanical stress still further.
- Figure 4 shows an idealized horizontal cross section of a left ventricle 30 subdivided into two symmetrical lobes 32 and 34 having an arc passing through an angle
- Lobes 32 and 34 can be formed using a splint, such as
- transventricular splint 12 shown in Figures 1 and 2.
- Lobes 32 and 34 are joined at points
- Points 36 and 38 are separated by a distance I.
- Figure 5 is an idealized horizontal cross section of a left ventricle 40 subdivided into three generally equal sized lobes 42, 44 and 46. Each lobe has an equal radius and
- a plurality of transventricular splints such as splint 12 as
- the horizontal cross sections 30 and 40 will have a generally circular shape, i.e., a non-splinted shape at end systole.
- the radius of the circular shape will continue to increase until the splint engages.
- the lobed shape will begin to form.
- the radius will continue to increase as diastolic filling proceeds.
- radius R will decrease as diastolic filling proceeds. The radius will continue to decrease unless or until the pressure in the heart causes the heart to
- wrap is substantially inelastic, as pressure increases in the chamber during diastolic filling, stress in the heart wall muscle will increase until the wrap fully engages and substantially all additional muscle elongating load created by increased chamber pressure will be shifted to the wrap. No further elongation of the chamber muscles disposed in a horizontal cross section through the wrap and the chamber will occur. Thus, inelastic wraps will halt additional preload muscle strain (end diastolic muscle stretch).
- the type of shape change illustrated in Figures 4 and 5 is of substantial significance for restrictive splints. It is undesirable in the case of restrictive splints, to excessively limit preload muscle strain.
- the Frank-Starling Curve demonstrates the dependence and need for variable preload muscle strain on overall heart pumping performance. During a person's normal activities, their body may need increased blood perfusion, for example, during exertion. In response to increased blood perfusion through a person's tissue, the heart will compensate for the additional demand by increasing stroke volume and/or heart rate. When stroke volume is increased, the patient's normal preload strain is also increased. That is, the lines 14-16 and 22-24 of the normal and failing hearts, respectively, will shift to the right. An inelastic wrap will, at engagement, substantially stop this shift.
- the magnitude of shape change in the case of full cycle splinting becomes very important as full cycle splinting generally reduces chamber volume more than restrictive splinting.
- the type of shape change is also important to allow for variable preload strain.
- Both restrictive device and full cycle splints reduce chamber volume as they reduce the cross sectional area of the chamber during the cardiac cycle.
- the magnitude of the shape change can vary from very slight at end diastole, such that chamber volume is only slightly reduced from the unsplinted end diastolic volume, to an extreme reduction in volume, for example, complete bifurcation by transventricular splint.
- the magnitude of the shape change is preferably modulated to reduce muscle stress while not overly reducing chamber volume.
- the reduction of chamber volume is compensated for by increased contractile shortening, which in turn leads to an increased ejection fraction, i.e., the ratio of the stroke volume to chamber volume.
- ejection fraction i.e., the ratio of the stroke volume to chamber volume.
- FIG 6 is a vertical view of a heart A similar to that shown in Figure 1. Rather than having a single band splints surrounding heart A, there are two band splints 51 affixed to the heart by two transventricular splints 52. Splints 52 include oppositely disposed anchors or anchor pads 53.
- Figure 7 is a horizontal cross sectional view of heart A of Figure 6, wraps 51 and splint 52. Splints 52 include a tension member 54 disposed through left ventricle B. Pads 53 are disposed on the opposite ends of tension members 54. Right ventricle C is shown to the left of left ventricle B. Splints 52 can be restrictive or full cycle splints.
- Band Splints 51 are shown as restrictive band splints as in Figure 6, heart A is shown engaged with the band splints 51 , where as in Figure 7, heart A has contracted to move away from band splints 51.
- Wraps 51 and splints 52 should be made from biocompatible materials.
- Band Splints 51 are preferably made from a pliable fabric or other material which resists elongation under normal operating loads. Band splints 51 can, however, be made from an elastic material which elongates during the cardiac cycle.
- Tension members 54 also preferably resist elongation under normal operating loads. Tension members 54 can, however, be made from an elastic material which elongates during the cardiac cycle.
- Figure 8 is a vertical view of heart A, partial wrap 61 and transventricular splint 62.
- Transventricular splint 62 includes anchor pads 63.
- Figure 9 is a horizontal cross sectional view of heart A, partial band splint 61 and splint 62.
- Splint 62 is essentially similar to wrap or band splint 12 shown in Figure 1 and 2.
- Partial band splint 61 is also essentially similar to wrap or band splint 11 shown in Figures 1 and 2 except that band splint 61 only surrounds a portion of heart A. This portion is shown in Figures 8 and 9 to the left including a portion of left ventricle B.
- Figure 10 is a horizontal cross sectional view of left ventricle B and right ventricle
- a splint 70 is shown disposed on heart A.
- Splint 70 includes a frame having two heart engaging anchors or pads 72 disposed at its opposite ends.
- a third heart engaging pad 73 is disposed along frame 70 approximately midway between pads 72.
- Pads 72 are shown engaged with heart A to change the shape of ventricle B in Figure 10.
- Pads 73 are not engaged with heart A in Figure 10.
- Figure 11 is the same horizontal cross sectional view as Figure 10 except that heart A has to contact pad 73 to create a further shape change of left ventricle B.
- Frame 70 is preferably rigid enough that pads 72 could be disposed on the heart for full cycle splinting and sufficiently adjustable that pads 72 could be spaced further apart for restrictive splinting.
- Pad 73 accomplishes restrictive splinting.
- Frame 71, pads 72 and 73 of splint 70 are made of a biocompatible material.
- Pads 72 and 73 are preferably substantially atraumatic.
- FIG 12 is a horizontal cross sectional view of the left ventricle B of heart A.
- a transventricular splint 80 having a tension member 81 and oppositely disposed anchor pads 82 is shown extending across left ventricle B.
- Another transventricular splint 83 having a tension member 84 and oppositely disposed anchor pads 85 extends generally perpendicularly to splint 80, across left ventricle B.
- splint 83 is engaging heart A to deform left ventricle B.
- Splint 80 includes a tension member 81 made of a flexible filament, line or the like which is shown in a relaxed state in Figure 12.
- tension member 81 is shown in an elongated, taunt configuration as heart A has expanded into engagement with pads 82.
- Transventricular splints 80 and 83 can be made as described above with respect to the transventricular splint of Figures 1 and 2.
- Tension member 81 may be elastic or inelastic.
- Figure 14 is a horizontal cross section of left ventricle B of heart A including a transventricular splint 90.
- Splint 90 includes a tension member 91 including three branches extending to atraumatic anchors or anchor pads 92. Similarly to tension member 81 of Figure 12, tension member 90 is shown in a relaxed state.
- Splint 90 can be made in a similar way as splint 80 of Figures 12 and 13.
- FIG 15 is the same horizontal cross section of heart A as shown in Figure 14 except that heart A has expanded to engage atraumatic pads 92 of splint 90. Tension member 91 is now drawn taunt to form a three lobed cross sectional configuration of left ventricle B.
- FIG 16 is a vertical view of heart A shown in phantom line. Shown disposed about the ventricles of heart A is a basket-like band splint 100.
- Band splint 100 includes a horizontal encircling band 101 around an upper region of the ventricles and four bands 102 which extend downward toward the apex of heart A. It can be appreciated that bands 102 can act as splints to form four lobes in heart A in a horizontal plane. Depending on the placement of bands 102 around heart A, lobes could be created only in the left ventricle or in the left ventricle and/or other chambers of the heart.
- Band 102 is joined at the apex Band 101 and band 102 can be made from a webbing, fabric or other biocompatible material.
- band splint 100 substantially elongated elastically under normal operating loads, it could be friction fit to heart A and act full cycle, limiting muscle stress at end diastole as well end systole. Band splint 100 could be sutured into place or otherwise held on heart A and act as a restrictive device. If band 101 were securely fastened to heart A, bands 102 could limit the vertical elongation of heart A during diastolic filling.
- FIG 17 is an alternate embodiment 110 of the band splint of Figure 16.
- Band splint 110 includes a horizontally heart encircling band 111 and four bands 113 extending downward from band 111. Bands 113, however, unlike bands 102 of band splint 100 do not extend to the apex of heart A, but rather to a second horizontally heart encircling band 112. Band splint 110 could be made of the same materials as band splint 100. Band splint 110 can also be used in a manner similar to band splint 100 except that band splint 110 would limit the vertical elongation of the ventricles less than band splint 100.
- FIG 18 is yet another alternate embodiment 120 of the wrap of Figure 16.
- Band splint 120 closely resembles alternate embodiment 110 of Figure 17, except that rather than having four vertically extending web members, band splint 120 mcludes two substantially rigid members 123 interconnecting two horizontally encircling web members 121 and 122.
- Figure 19 is yet another alternate embodiment 130 of the band splint of Figure 16.
- band splint 130 includes a horizontally encircling member 131 and four downwardly extending members 132. At a location proximate of the apex of heart A, members 132 are joined by a ring 133. Members 132 extend through ring 133. Ring 133 can be used to adjust the length of members 132 between band 131 and ring 133. Ring 133 can be formed from metallic material and crimped inwardly to fix its position along members 132. Other means of holding ring 133 in position would be readily apparent to those skilled in the art.
- FIG 20 is a vertical view of heart A including a partial band splint 140 secured around a substantial portion of left ventricle B.
- Band splint 140 includes a vertically elongating anchor member 141 which sutures 142 can encircle to anchor member 141 to heart A.
- a band 143 extends generally horizontally from anchor member 141 to an opposite anchor 141.
- band 143 can be seen in its entirety in Figure 21 which is a horizontal cross sectional view of heart A through band 143, left ventricle B and right ventricle C.
- Figure 21 is a horizontal cross sectional view of heart A through band 143, left ventricle B and right ventricle C.
- heart A is shown engaged with band 143
- band 143 is shown spaced from heart A.
- wrap 140 would be acting as a restrictive device.
- band splint 140 were made from a material that substantially deforms elastically under normal loads, band splint 140 could also be secured sufficiently snuggly to heart A to act as a full cycle device.
- band 143 of band splint 140 is formed from a webbing or substantially inelastic fabric.
- Figure 22 is a vertical view of heart A including band splint 140 disposed vertically on left ventricle B. In this position, band splint 140 can limit the vertical elongation of left ventricle B during diastolic filling.
- Figure 23 is a horizontal cross section of heart A through left ventricle B, right ventricle C and the papillary muscles D of left ventricle B.
- a transventricular splint 150 including an elongate tension member 151 and oppositely disposed anchor pads 152 extends through left ventricle B and papillary muscles D. Splint 150 could be similar to splint 12 of Figure 1 and 2.
- Figure 24 is a horizontal cross section similar to that of Figure 23. In Figure 24, however, transventricular splint 150 is shown avoiding papillary muscles D.
- Figure 25 is a horizontal cross section of left ventricle B of heart A. Here three splints 150 have been placed to form six lobes. Three of the lobes 153 have an arc length
- each lobe 153 Disposed between each lobe 153 are three
- lobes 154 which have an arc length which passes through an angle less than ⁇ .
- FIG. 26 is a vertical view of heart A including a wrap 160.
- Wrap 160 can include a single thread or line 161 encircling the heart several times. After line 161 encircles heart A, line 161 can be threaded through a bar 162, including a plurality of eyelets 163 spaced along its length in pairs. Bar 162 is preferably rigid enough to substantially maintain the distance between eyelets 163 under normal operating loads.
- line 161 When line 161 is placed in heart A, one end of line 161 can be tied to bar 162 at 164. Line 161 can then encircle the heart and be drawn through eyelet 162 adjacent the begii-ning of line 161 at 164. Line 161 can then be drawn through one eyelet 163 of a lower pair of eyelets to encircle the heart again. This process continues until line 161 is tied to an eyelet 163 at 165. It can be appreciated that wrap 160 could be used as a restrictive or full cycle device depending on the diameter of loop formed by line 161.
- Figure 27 is an alternate embodiment 170 of the wrap of Figure 26.
- Wrap 170 includes two vertically extending bars 172 having eyelets 173 through which line 171 is threaded.
- Line 171 can be tied to one of the bars 172 at 174 and 175.
- Figure 28 is a vertical view of heart A including yet another embodiment 180 of the wrap of Figure 26.
- Wrap 180 includes a line 181 encircling heart A a plurality of times. Rather than having a single vertically extending bar 162 to position line 180 on heart A, wrap 180 includes a plurality of horizontal bars 182 including a pair of eyelets 183.
- One end of line 181 is tied to an upper bar 182 at 184 and the opposite end of line 181 is tied to a lower bar 182 at 185. Between 184 and 185, line 181 is threaded through eyelets 182 to form the heart encircling pattern shown in Figure 28.
- Figure 29 is a vertical view of heart A including yet another alternate embodiment 190 of the wrap of Figure 26.
- Wrap 190 closely resembles 180 of Figure 28.
- Line 181 has, however, been threaded through eyelets 183 of bars 182 in a pattern which, unlike that of Figure 28, bars 182 are disposed at various selected locations around the circumference of heart A.
- Figure 30 is a vertical view of heart A including a wrap 200.
- Wrap 200 is substantially similar to wrap 11 of Figures 1 and 2, except that wrap 200 extends vertically a greater distance than wrap 11. Wrap 200 is not shown with a transventricular splint. It can be appreciated that wrap 200 could be used as restrictive or full cycle device.
- Figure 33 is a vertical view of heart A having a Wj.
- Figure 34 is an idealized horizontal cross sectional view of heart A of Figure 33.
- Heart A includes left ventricle B and right ventricle C.
- Left ventricle B has a radius Rj.
- Figure 36 is a vertical view of an elongate heart A having a horizontal width W less than Wj.
- Figure 37 is a horizontal cross section of the heart A of Figure 36 including left ventricle B and right ventricle C.
- the radius R 2 of left ventricle B is less than Ri of Figure 34.
- elongate bar 224 is sized such that device 220 does not engage at end diastole, but rather anchor pad 228 first engages during systolic contraction, device 220 can fall into a third class of device neither full cycle nor restrictive. Such a device would reduce wall stress during a portion of systolic contraction including end systole, but not reduce wall stress during end diastole, thus maintaining maximum preload.
- Tube 231 is preferably highly flexible, yet durable enough to prevent thread 232 from "cheese cutting" through the myocardium of heart A.
- Tube 231 and line 232 are preferably formed from biocompatible atraumatic materials which do not substantially elongate under the influence of forces encountered during expansion and contraction of heart A.
- tube 231 and line 232 could be made from materials which readily elongate under the influence of the forces encountered during the cardiac cycle. It can be appreciated that device 230 could be used as a full cycle device or restrictive device.
- Figure 39 is a vertical cross sectional view of heart A including left ventricle B.
- a substantially V-shaped or U-shaped member having arms 241 is shown substantially advanced into the myocardium of heart A.
- Device 240 includes an apex 242 disposed adjacent the apex of heart A.
- the spacing of arms 241 from each other is preferably such that device 240 can form lobes in horizontal cross sections of left ventricle B.
- Device 240 is preferably formed from biocompatible materials which preferably do not deform substantially under the influence of the forces encountered during the cardiac cycle. It can be appreciated that device 240 could be used as a restrictive or full cycle device.
- Figure 41 is a vertical view of heart A including device 250.
- Splint 250 can act as a full cycle device or a restrictive device, to shorten a portion of the left ventricle heart
- FIG 42 is a horizontal cross sectional view of heart A including left ventricle B and C.
- a device 260 including a thread or line 261 is disposed transventricularly and transmyocardially through heart A.
- a portion of line 261 is disposed outside of heart A.
- Opposite ends of line 261 are connected at 262.
- Those portions of line 261 outside heart A form loops 263.
- the size of loops 263 are exaggerated for purposes of illustration. It is assumed that heart A in the process of diastolic filling in Figure 42, and loops 263 are sufficiently small, eventually heart A will engage loops 263. In such a configuration, device 260 is used as a restrictive device. Loops 263 could be sized, however, such that they engage full cycle.
- Line 261 is preferably made from atraumatic biocompatible material.
- the diameter of line 261 is preferably sufficiently great that cutting of heart A does not occur during diastolic filling.
- Figure 43 is a horizontal cross sectional view of heart A including left ventricle B and right ventricle C and an alternate embodiment 270 of the device of Figure 42.
- Device 270 includes a line 271 which does not extend transventricularly but extends through the myocardium of heart A to form four loops 273.
- Device 270 can be formed from material similar to that used to form device 260. Additionally, device 270 can be made to function as a restrictive device or full cycle device in a manner similar to that of device 260. Line 261 and line 267 could be disposed within a tube such as tube 231 of Figure
- FIG 44 is a vertical view of heart A including three devices 270 disposed at three spaced elevations.
- An elongate generally rigid bar 274 is disposed through loops 273 to distribute the load on heart A from loops 273 across a larger area than lines 271 can alone.
- Figure 45 is a vertical cross section of heart A showing left ventricle B including papillary muscles D and chordae H. Joining chordae H is a ring 290.
- Ring 290 is preferably strong and rigid enough to hold chordae H, papillary muscles D and consequently the wall of left ventricle B inward during diastolic expansion. It can be appreciated that loop 290 could be configured to operate as a full cycle or a restrictive device. Preferably loop 229 is formed from an atraumatic biocompatible material.
Abstract
Description
Claims
Priority Applications (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
AU52309/99A AU5230999A (en) | 1998-07-29 | 1999-07-27 | Stress reduction apparatus and method |
EP99937484A EP1143859A2 (en) | 1998-07-29 | 1999-07-27 | Heart stress reduction apparatus and method |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US09/124,321 US6077214A (en) | 1998-07-29 | 1998-07-29 | Stress reduction apparatus and method |
US09/124,321 | 1998-07-29 |
Publications (3)
Publication Number | Publication Date |
---|---|
WO2000006027A2 WO2000006027A2 (en) | 2000-02-10 |
WO2000006027A9 true WO2000006027A9 (en) | 2000-08-03 |
WO2000006027A3 WO2000006027A3 (en) | 2001-11-08 |
Family
ID=22414177
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US1999/016875 WO2000006027A2 (en) | 1998-07-29 | 1999-07-27 | Heart stress reduction apparatus and method |
Country Status (4)
Country | Link |
---|---|
US (5) | US6077214A (en) |
EP (1) | EP1143859A2 (en) |
AU (1) | AU5230999A (en) |
WO (1) | WO2000006027A2 (en) |
Cited By (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9005109B2 (en) | 2000-05-10 | 2015-04-14 | Mardil, Inc. | Cardiac disease treatment and device |
US9149602B2 (en) | 2005-04-22 | 2015-10-06 | Advanced Cardiovascular Systems, Inc. | Dual needle delivery system |
US9370425B2 (en) | 2012-10-12 | 2016-06-21 | Mardil, Inc. | Cardiac treatment system and method |
Families Citing this family (395)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6572529B2 (en) * | 1993-06-17 | 2003-06-03 | Wilk Patent Development Corporation | Intrapericardial assist method |
US6592619B2 (en) | 1996-01-02 | 2003-07-15 | University Of Cincinnati | Heart wall actuation device for the natural heart |
US6520904B1 (en) | 1996-01-02 | 2003-02-18 | The University Of Cincinnati | Device and method for restructuring heart chamber geometry |
US5957977A (en) | 1996-01-02 | 1999-09-28 | University Of Cincinnati | Activation device for the natural heart including internal and external support structures |
US6123662A (en) * | 1998-07-13 | 2000-09-26 | Acorn Cardiovascular, Inc. | Cardiac disease treatment and device |
US6050936A (en) | 1997-01-02 | 2000-04-18 | Myocor, Inc. | Heart wall tension reduction apparatus |
US6045497A (en) | 1997-01-02 | 2000-04-04 | Myocor, Inc. | Heart wall tension reduction apparatus and method |
US20030045771A1 (en) * | 1997-01-02 | 2003-03-06 | Schweich Cyril J. | Heart wall tension reduction devices and methods |
US6406420B1 (en) | 1997-01-02 | 2002-06-18 | Myocor, Inc. | Methods and devices for improving cardiac function in hearts |
US6077214A (en) * | 1998-07-29 | 2000-06-20 | Myocor, Inc. | Stress reduction apparatus and method |
US6183411B1 (en) | 1998-09-21 | 2001-02-06 | Myocor, Inc. | External stress reduction device and method |
US7883539B2 (en) * | 1997-01-02 | 2011-02-08 | Edwards Lifesciences Llc | Heart wall tension reduction apparatus and method |
EP0991373B1 (en) | 1997-06-21 | 2004-09-15 | Acorn Cardiovascular, Inc. | Bag for at least partially enveloping a heart |
WO1999000059A1 (en) * | 1997-06-27 | 1999-01-07 | The Trustees Of Columbia University In The City Of New York | Method and apparatus for circulatory valve repair |
FR2768324B1 (en) | 1997-09-12 | 1999-12-10 | Jacques Seguin | SURGICAL INSTRUMENT FOR PERCUTANEOUSLY FIXING TWO AREAS OF SOFT TISSUE, NORMALLY MUTUALLY REMOTE, TO ONE ANOTHER |
US6332893B1 (en) | 1997-12-17 | 2001-12-25 | Myocor, Inc. | Valve to myocardium tension members device and method |
US6190408B1 (en) | 1998-03-05 | 2001-02-20 | The University Of Cincinnati | Device and method for restructuring the heart chamber geometry |
US7491232B2 (en) * | 1998-09-18 | 2009-02-17 | Aptus Endosystems, Inc. | Catheter-based fastener implantation apparatus and methods with implantation force resolution |
US6260552B1 (en) | 1998-07-29 | 2001-07-17 | Myocor, Inc. | Transventricular implant tools and devices |
US6685627B2 (en) | 1998-10-09 | 2004-02-03 | Swaminathan Jayaraman | Modification of properties and geometry of heart tissue to influence heart function |
US8715156B2 (en) * | 1998-10-09 | 2014-05-06 | Swaminathan Jayaraman | Modification of properties and geometry of heart tissue to influence function |
US6587734B2 (en) | 1998-11-04 | 2003-07-01 | Acorn Cardiovascular, Inc. | Cardio therapeutic heart sack |
US6169922B1 (en) | 1998-11-18 | 2001-01-02 | Acorn Cardiovascular, Inc. | Defibrillating cardiac jacket with interwoven electrode grids |
US7811296B2 (en) | 1999-04-09 | 2010-10-12 | Evalve, Inc. | Fixation devices for variation in engagement of tissue |
US7226467B2 (en) | 1999-04-09 | 2007-06-05 | Evalve, Inc. | Fixation device delivery catheter, systems and methods of use |
CA2620783C (en) | 1999-04-09 | 2011-04-05 | Evalve, Inc. | Methods and apparatus for cardiac valve repair |
US6752813B2 (en) | 1999-04-09 | 2004-06-22 | Evalve, Inc. | Methods and devices for capturing and fixing leaflets in valve repair |
US10327743B2 (en) * | 1999-04-09 | 2019-06-25 | Evalve, Inc. | Device and methods for endoscopic annuloplasty |
US20040044350A1 (en) | 1999-04-09 | 2004-03-04 | Evalve, Inc. | Steerable access sheath and methods of use |
US8216256B2 (en) | 1999-04-09 | 2012-07-10 | Evalve, Inc. | Detachment mechanism for implantable fixation devices |
US7604646B2 (en) | 1999-04-09 | 2009-10-20 | Evalve, Inc. | Locking mechanisms for fixation devices and methods of engaging tissue |
US7955340B2 (en) | 1999-06-25 | 2011-06-07 | Usgi Medical, Inc. | Apparatus and methods for forming and securing gastrointestinal tissue folds |
US7416554B2 (en) | 2002-12-11 | 2008-08-26 | Usgi Medical Inc | Apparatus and methods for forming and securing gastrointestinal tissue folds |
US7637905B2 (en) | 2003-01-15 | 2009-12-29 | Usgi Medical, Inc. | Endoluminal tool deployment system |
US7618426B2 (en) | 2002-12-11 | 2009-11-17 | Usgi Medical, Inc. | Apparatus and methods for forming gastrointestinal tissue approximations |
SE514718C2 (en) | 1999-06-29 | 2001-04-09 | Jan Otto Solem | Apparatus for treating defective closure of the mitral valve apparatus |
US7192442B2 (en) * | 1999-06-30 | 2007-03-20 | Edwards Lifesciences Ag | Method and device for treatment of mitral insufficiency |
US6997951B2 (en) * | 1999-06-30 | 2006-02-14 | Edwards Lifesciences Ag | Method and device for treatment of mitral insufficiency |
US6241654B1 (en) * | 1999-07-07 | 2001-06-05 | Acorn Cardiovasculr, Inc. | Cardiac reinforcement devices and methods |
US20060229491A1 (en) * | 2002-08-01 | 2006-10-12 | Cardiokinetix, Inc. | Method for treating myocardial rupture |
US7887477B2 (en) * | 1999-08-09 | 2011-02-15 | Cardiokinetix, Inc. | Method of improving cardiac function using a porous membrane |
US7279007B2 (en) * | 1999-08-09 | 2007-10-09 | Cardioklnetix, Inc. | Method 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 |
US8500795B2 (en) | 1999-08-09 | 2013-08-06 | Cardiokinetix, Inc. | Retrievable devices for improving cardiac function |
US7674222B2 (en) | 1999-08-09 | 2010-03-09 | Cardiokinetix, Inc. | Cardiac device and methods of use thereof |
US10307147B2 (en) | 1999-08-09 | 2019-06-04 | Edwards Lifesciences Corporation | System for improving cardiac function by sealing a partitioning membrane within a ventricle |
US9694121B2 (en) | 1999-08-09 | 2017-07-04 | Cardiokinetix, Inc. | Systems and methods for improving cardiac function |
US7582051B2 (en) * | 2005-06-10 | 2009-09-01 | Cardiokinetix, Inc. | Peripheral seal for a ventricular partitioning device |
US8257428B2 (en) * | 1999-08-09 | 2012-09-04 | Cardiokinetix, Inc. | System for improving cardiac function |
US8529430B2 (en) | 2002-08-01 | 2013-09-10 | Cardiokinetix, Inc. | Therapeutic methods and devices following myocardial infarction |
US7972337B2 (en) | 2005-12-28 | 2011-07-05 | Intrinsic Therapeutics, Inc. | Devices and methods for bone anchoring |
WO2004100841A1 (en) | 1999-08-18 | 2004-11-25 | Intrinsic Therapeutics, Inc. | Devices and method for augmenting a vertebral disc nucleus |
WO2009033100A1 (en) * | 2007-09-07 | 2009-03-12 | Intrinsic Therapeutics, Inc. | Bone anchoring systems |
US7998213B2 (en) | 1999-08-18 | 2011-08-16 | Intrinsic Therapeutics, Inc. | Intervertebral disc herniation repair |
JP4247519B2 (en) * | 1999-08-18 | 2009-04-02 | イントリンジック セラピューティックス インコーポレイテッド | Apparatus and method for nucleus augmentation and retention |
US7717961B2 (en) * | 1999-08-18 | 2010-05-18 | Intrinsic Therapeutics, Inc. | Apparatus delivery in an intervertebral disc |
US8323341B2 (en) | 2007-09-07 | 2012-12-04 | Intrinsic Therapeutics, Inc. | Impaction grafting for vertebral fusion |
US6328689B1 (en) | 2000-03-23 | 2001-12-11 | Spiration, Inc., | Lung constriction apparatus and method |
US6174279B1 (en) * | 1999-09-21 | 2001-01-16 | Acorn Cardiovascular, Inc. | Cardiac constraint with tension indicator |
US6702732B1 (en) * | 1999-12-22 | 2004-03-09 | Paracor Surgical, Inc. | Expandable cardiac harness for treating congestive heart failure |
EP1113497A3 (en) * | 1999-12-29 | 2006-01-25 | Texas Instruments Incorporated | Semiconductor package with conductor impedance selected during assembly |
US6402781B1 (en) * | 2000-01-31 | 2002-06-11 | Mitralife | Percutaneous mitral annuloplasty and cardiac reinforcement |
US6989028B2 (en) | 2000-01-31 | 2006-01-24 | Edwards Lifesciences Ag | Medical system and method for remodeling an extravascular tissue structure |
US7507252B2 (en) * | 2000-01-31 | 2009-03-24 | Edwards Lifesciences Ag | Adjustable transluminal annuloplasty system |
DE60124872T2 (en) | 2000-03-10 | 2007-06-14 | Paracor Medical, Inc., Los Altos | EXPANDABLE HEARTS BAG FOR THE TREATMENT OF CONGESTIVE HEART FAILURE |
US6537198B1 (en) * | 2000-03-21 | 2003-03-25 | Myocor, Inc. | Splint assembly for improving cardiac function in hearts, and method for implanting the splint assembly |
ITPC20000013A1 (en) * | 2000-04-13 | 2000-07-13 | Paolo Ferrazzi | INTROVENTRICULAR DEVICE AND RELATED METHOD FOR THE TREATMENT AND CORRECTION OF MYOCARDIOPATHIES. |
AU2001265264A1 (en) * | 2000-05-31 | 2001-12-11 | Cardioclasp, Inc. | Devices and methods for assisting natural heart function |
US6730016B1 (en) | 2000-06-12 | 2004-05-04 | Acorn Cardiovascular, Inc. | Cardiac disease treatment and device |
US7618364B2 (en) * | 2000-06-12 | 2009-11-17 | Acorn Cardiovascular, Inc. | Cardiac wall tension relief device and method |
US6902522B1 (en) | 2000-06-12 | 2005-06-07 | Acorn Cardiovascular, Inc. | Cardiac disease treatment and device |
US6951534B2 (en) | 2000-06-13 | 2005-10-04 | Acorn Cardiovascular, Inc. | Cardiac support device |
US6482146B1 (en) * | 2000-06-13 | 2002-11-19 | Acorn Cardiovascular, Inc. | Cardiac disease treatment and device |
US10064696B2 (en) | 2000-08-09 | 2018-09-04 | Edwards Lifesciences Corporation | Devices and methods for delivering an endocardial device |
US20060030881A1 (en) | 2004-08-05 | 2006-02-09 | Cardiokinetix, Inc. | Ventricular partitioning device |
US9078660B2 (en) | 2000-08-09 | 2015-07-14 | Cardiokinetix, Inc. | Devices and methods for delivering an endocardial device |
US9332992B2 (en) | 2004-08-05 | 2016-05-10 | Cardiokinetix, Inc. | Method for making a laminar ventricular partitioning device |
US7762943B2 (en) * | 2004-03-03 | 2010-07-27 | Cardiokinetix, Inc. | Inflatable ventricular partitioning device |
US8398537B2 (en) * | 2005-06-10 | 2013-03-19 | Cardiokinetix, Inc. | Peripheral seal for a ventricular partitioning device |
US7862500B2 (en) * | 2002-08-01 | 2011-01-04 | Cardiokinetix, Inc. | Multiple partitioning devices for heart treatment |
US7399271B2 (en) * | 2004-01-09 | 2008-07-15 | Cardiokinetix, Inc. | Ventricular partitioning device |
US9332993B2 (en) | 2004-08-05 | 2016-05-10 | Cardiokinetix, Inc. | Devices and methods for delivering an endocardial device |
US6572533B1 (en) * | 2000-08-17 | 2003-06-03 | Acorn Cardiovascular, Inc. | Cardiac disease treatment and device |
US6887192B1 (en) | 2000-09-08 | 2005-05-03 | Converge Medical, Inc. | Heart support to prevent ventricular remodeling |
US20050228422A1 (en) * | 2002-11-26 | 2005-10-13 | Ample Medical, Inc. | Devices, systems, and methods for reshaping a heart valve annulus, including the use of magnetic tools |
US20060106279A1 (en) | 2004-05-14 | 2006-05-18 | Ample Medical, Inc. | Devices, systems, and methods for reshaping a heart valve annulus, including the use of a bridge implant having an adjustable bridge stop |
US7527646B2 (en) * | 2000-09-20 | 2009-05-05 | Ample Medical, Inc. | Devices, systems, and methods for retaining a native heart valve leaflet |
US6893459B1 (en) * | 2000-09-20 | 2005-05-17 | Ample Medical, Inc. | Heart valve annulus device and method of using same |
US7381220B2 (en) | 2000-09-20 | 2008-06-03 | Ample Medical, Inc. | Devices, systems, and methods for supplementing, repairing, or replacing a native heart valve leaflet |
US20090287179A1 (en) | 2003-10-01 | 2009-11-19 | Ample Medical, Inc. | Devices, systems, and methods for reshaping a heart valve annulus, including the use of magnetic tools |
US8784482B2 (en) * | 2000-09-20 | 2014-07-22 | Mvrx, Inc. | Method of reshaping a heart valve annulus using an intravascular device |
US20050222489A1 (en) * | 2003-10-01 | 2005-10-06 | Ample Medical, Inc. | Devices, systems, and methods for reshaping a heart valve annulus, including the use of a bridge implant |
US20060106278A1 (en) * | 2004-05-14 | 2006-05-18 | Ample Medical, Inc. | Devices, systems, and methods for reshaping a heart valve annulus, including the use of an adjustable bridge implant system |
US20080091264A1 (en) | 2002-11-26 | 2008-04-17 | Ample Medical, Inc. | Devices, systems, and methods for reshaping a heart valve annulus, including the use of magnetic tools |
US8956407B2 (en) * | 2000-09-20 | 2015-02-17 | Mvrx, Inc. | Methods for reshaping a heart valve annulus using a tensioning implant |
US6808483B1 (en) | 2000-10-03 | 2004-10-26 | Paul A. Spence | Implantable heart assist devices and methods |
US6723038B1 (en) | 2000-10-06 | 2004-04-20 | Myocor, Inc. | Methods and devices for improving mitral valve function |
US6616684B1 (en) * | 2000-10-06 | 2003-09-09 | Myocor, Inc. | Endovascular splinting devices and methods |
US6564094B2 (en) | 2000-12-22 | 2003-05-13 | Acorn Cardiovascular, Inc. | Cardiac disease treatment and device |
US7510576B2 (en) * | 2001-01-30 | 2009-03-31 | Edwards Lifesciences Ag | Transluminal mitral annuloplasty |
US6810882B2 (en) | 2001-01-30 | 2004-11-02 | Ev3 Santa Rosa, Inc. | Transluminal mitral annuloplasty |
US20030181940A1 (en) * | 2001-02-28 | 2003-09-25 | Gregory Murphy | Ventricular restoration shaping apparatus and method of use |
US6622730B2 (en) | 2001-03-30 | 2003-09-23 | Myocor, Inc. | Device for marking and aligning positions on the heart |
US6923646B2 (en) * | 2001-04-18 | 2005-08-02 | Air Techniques, Inc. | Process and apparatus for treating an exhaust stream from a dental operatory |
US8202315B2 (en) | 2001-04-24 | 2012-06-19 | Mitralign, Inc. | Catheter-based annuloplasty using ventricularly positioned catheter |
US20020188170A1 (en) * | 2001-04-27 | 2002-12-12 | Santamore William P. | Prevention of myocardial infarction induced ventricular expansion and remodeling |
US7311731B2 (en) * | 2001-04-27 | 2007-12-25 | Richard C. Satterfield | Prevention of myocardial infarction induced ventricular expansion and remodeling |
AU2011213723B2 (en) * | 2001-04-27 | 2015-02-05 | Satterfield, Richard | Prevention of myocardial infarction induced ventricular expansion and remodeling |
IL159816A0 (en) * | 2001-07-16 | 2004-06-20 | Corassist Cardiovascular Ltd | In-vivo method and device for improving diastolic function of the left ventricle |
US7485088B2 (en) * | 2001-09-05 | 2009-02-03 | Chase Medical L.P. | Method and device for percutaneous surgical ventricular repair |
US20060025800A1 (en) * | 2001-09-05 | 2006-02-02 | Mitta Suresh | Method and device for surgical ventricular repair |
US20040243170A1 (en) * | 2001-09-05 | 2004-12-02 | Mitta Suresh | Method and device for percutaneous surgical ventricular repair |
DK1423066T3 (en) | 2001-09-07 | 2008-11-17 | Mardil Inc | Method and apparatus for external cardiac stabilization |
US6723041B2 (en) | 2001-09-10 | 2004-04-20 | Lilip Lau | Device for treating heart failure |
US20030050648A1 (en) | 2001-09-11 | 2003-03-13 | Spiration, Inc. | Removable lung reduction devices, systems, and methods |
US6695769B2 (en) * | 2001-09-25 | 2004-02-24 | The Foundry, Inc. | Passive ventricular support devices and methods of using them |
US7060023B2 (en) | 2001-09-25 | 2006-06-13 | The Foundry Inc. | Pericardium reinforcing devices and methods of using them |
US6685620B2 (en) | 2001-09-25 | 2004-02-03 | The Foundry Inc. | Ventricular infarct assist device and methods for using it |
JP4458845B2 (en) * | 2001-10-01 | 2010-04-28 | アンプル メディカル,インコーポレイテッド | Medical device |
US6632239B2 (en) * | 2001-10-02 | 2003-10-14 | Spiration, Inc. | Constriction device including reinforced suture holes |
US6589161B2 (en) * | 2001-10-18 | 2003-07-08 | Spiration, Inc. | Constriction device including tear resistant structures |
US6592594B2 (en) | 2001-10-25 | 2003-07-15 | Spiration, Inc. | Bronchial obstruction device deployment system and method |
US6575971B2 (en) | 2001-11-15 | 2003-06-10 | Quantum Cor, Inc. | Cardiac valve leaflet stapler device and methods thereof |
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 |
US20110087320A1 (en) * | 2001-11-28 | 2011-04-14 | Aptus Endosystems, Inc. | Devices, Systems, and Methods for Prosthesis Delivery and Implantation, Including a Prosthesis Assembly |
US20090099650A1 (en) * | 2001-11-28 | 2009-04-16 | Lee Bolduc | Devices, systems, and methods for endovascular staple and/or prosthesis delivery and implantation |
US20070073389A1 (en) | 2001-11-28 | 2007-03-29 | Aptus Endosystems, Inc. | Endovascular aneurysm devices, systems, and methods |
CN100479786C (en) | 2001-11-28 | 2009-04-22 | 阿普特斯内系统公司 | 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 |
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 |
ATE462378T1 (en) * | 2001-12-28 | 2010-04-15 | Edwards Lifesciences Ag | DELAYED MEMORY DEVICE |
SE524709C2 (en) * | 2002-01-11 | 2004-09-21 | Edwards Lifesciences Ag | Device for delayed reshaping of a heart vessel and a heart valve |
US7174896B1 (en) | 2002-01-07 | 2007-02-13 | Paracor Medical, Inc. | Method and apparatus for supporting a heart |
US7022063B2 (en) | 2002-01-07 | 2006-04-04 | Paracor Medical, Inc. | Cardiac harness |
US6764510B2 (en) | 2002-01-09 | 2004-07-20 | Myocor, Inc. | Devices and methods for heart valve treatment |
US20030216769A1 (en) | 2002-05-17 | 2003-11-20 | Dillard David H. | Removable anchored lung volume reduction devices and methods |
US20030181922A1 (en) | 2002-03-20 | 2003-09-25 | Spiration, Inc. | Removable anchored lung volume reduction devices and methods |
US7181272B2 (en) | 2002-04-22 | 2007-02-20 | Medtronic, Inc. | Cardiac restraint with electrode attachment sites |
AU2003229003B2 (en) * | 2002-05-09 | 2008-09-18 | Covidien Lp | Organ retractor and method of using the same |
CA2483905C (en) * | 2002-05-09 | 2011-01-25 | Tyco Healthcare Group Lp | Endoscopic organ retractor and method of using the same |
EP1530441B1 (en) * | 2002-06-13 | 2017-08-02 | Ancora Heart, Inc. | Devices and methods for heart valve repair |
US7753922B2 (en) | 2003-09-04 | 2010-07-13 | Guided Delivery Systems, Inc. | Devices and methods for cardiac annulus stabilization and treatment |
US8641727B2 (en) | 2002-06-13 | 2014-02-04 | Guided Delivery Systems, Inc. | 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 |
US9949829B2 (en) | 2002-06-13 | 2018-04-24 | Ancora Heart, Inc. | Delivery devices and methods for heart valve repair |
US20060122633A1 (en) | 2002-06-13 | 2006-06-08 | John To | Methods and devices for termination |
US7883538B2 (en) | 2002-06-13 | 2011-02-08 | Guided Delivery Systems Inc. | Methods and devices for termination |
US9226825B2 (en) | 2002-06-13 | 2016-01-05 | Guided Delivery Systems, Inc. | Delivery devices and methods for heart valve repair |
US7081084B2 (en) * | 2002-07-16 | 2006-07-25 | University Of Cincinnati | Modular power system and method for a heart wall actuation system for the natural heart |
US7850729B2 (en) | 2002-07-18 | 2010-12-14 | The University Of Cincinnati | Deforming jacket for a heart actuation device |
US20040059180A1 (en) * | 2002-09-23 | 2004-03-25 | The University Of Cincinnati | Basal mounting cushion frame component to facilitate extrinsic heart wall actuation |
US6988982B2 (en) * | 2002-08-19 | 2006-01-24 | Cardioenergetics | Heart wall actuation system for the natural heart with shape limiting elements |
AU2003277116A1 (en) * | 2002-10-01 | 2004-04-23 | Ample Medical, Inc. | Devices, systems, and methods for reshaping a heart valve annulus |
DE60336497D1 (en) * | 2002-10-04 | 2011-05-05 | Tyco Healthcare | ENDOSCOPIC RETRACTOR |
US7087064B1 (en) | 2002-10-15 | 2006-08-08 | Advanced Cardiovascular Systems, Inc. | Apparatuses and methods for heart valve repair |
US20050119735A1 (en) | 2002-10-21 | 2005-06-02 | Spence Paul A. | Tissue fastening systems and methods utilizing magnetic guidance |
NZ539136A (en) | 2002-10-21 | 2008-04-30 | Mitralign Inc | Method and apparatus for performing catheter-based annuloplasty using local plications |
US7247134B2 (en) * | 2002-11-12 | 2007-07-24 | Myocor, Inc. | Devices and methods for heart valve treatment |
US7112219B2 (en) | 2002-11-12 | 2006-09-26 | Myocor, Inc. | Devices and methods for heart valve treatment |
US7981152B1 (en) | 2004-12-10 | 2011-07-19 | Advanced Cardiovascular Systems, Inc. | Vascular delivery system for accessing and delivering devices into coronary sinus and other vascular sites |
US7335213B1 (en) | 2002-11-15 | 2008-02-26 | Abbott Cardiovascular Systems Inc. | Apparatus and methods for heart valve repair |
US7404824B1 (en) | 2002-11-15 | 2008-07-29 | Advanced Cardiovascular Systems, Inc. | Valve aptation assist device |
US7331972B1 (en) | 2002-11-15 | 2008-02-19 | Abbott Cardiovascular Systems Inc. | Heart valve chord cutter |
US6945978B1 (en) | 2002-11-15 | 2005-09-20 | Advanced Cardiovascular Systems, Inc. | Heart valve catheter |
US7736299B2 (en) | 2002-11-15 | 2010-06-15 | Paracor Medical, Inc. | Introducer for a cardiac harness delivery |
US20040098116A1 (en) | 2002-11-15 | 2004-05-20 | Callas Peter L. | Valve annulus constriction apparatus and method |
US8187324B2 (en) | 2002-11-15 | 2012-05-29 | Advanced Cardiovascular Systems, Inc. | Telescoping apparatus for delivering and adjusting a medical device in a vessel |
US7485143B2 (en) * | 2002-11-15 | 2009-02-03 | Abbott Cardiovascular Systems Inc. | Apparatuses and methods for heart valve repair |
US7942884B2 (en) | 2002-12-11 | 2011-05-17 | Usgi Medical, Inc. | Methods for reduction of a gastric lumen |
US7942898B2 (en) | 2002-12-11 | 2011-05-17 | Usgi Medical, Inc. | Delivery systems and methods for gastric reduction |
US20060241334A1 (en) * | 2003-01-27 | 2006-10-26 | Corassist Cardiovascular Ltd. | In vivo device for improving diastolic ventricular function |
US20040254600A1 (en) * | 2003-02-26 | 2004-12-16 | David Zarbatany | Methods and devices for endovascular mitral valve correction from the left coronary sinus |
US7883500B2 (en) * | 2003-03-26 | 2011-02-08 | G&L Consulting, Llc | Method and system to treat and prevent myocardial infarct expansion |
US7100616B2 (en) | 2003-04-08 | 2006-09-05 | Spiration, Inc. | Bronchoscopic lung volume reduction method |
US10646229B2 (en) | 2003-05-19 | 2020-05-12 | Evalve, Inc. | Fixation devices, systems and methods for engaging tissue |
US7341584B1 (en) | 2003-05-30 | 2008-03-11 | Thomas David Starkey | Device and method to limit filling of the heart |
WO2004110257A2 (en) | 2003-06-09 | 2004-12-23 | The University Of Cincinnati | Power system for a heart actuation device |
US20060178551A1 (en) * | 2003-06-09 | 2006-08-10 | Melvin David B | Securement system for a heart actuation device |
WO2004110553A1 (en) | 2003-06-09 | 2004-12-23 | The University Of Cincinnati | Actuation mechanisms for a heart actuation device |
US7316706B2 (en) * | 2003-06-20 | 2008-01-08 | Medtronic Vascular, Inc. | Tensioning device, system, and method for treating mitral valve regurgitation |
US7513867B2 (en) * | 2003-07-16 | 2009-04-07 | Kardium, Inc. | Methods and devices for altering blood flow through the left ventricle |
EP1646332B1 (en) | 2003-07-18 | 2015-06-17 | Edwards Lifesciences AG | Remotely activated mitral annuloplasty system |
US7533671B2 (en) | 2003-08-08 | 2009-05-19 | Spiration, Inc. | Bronchoscopic repair of air leaks in a lung |
US8308765B2 (en) | 2004-05-07 | 2012-11-13 | Usgi Medical, Inc. | Apparatus and methods for positioning and securing anchors |
US8216252B2 (en) | 2004-05-07 | 2012-07-10 | Usgi Medical, Inc. | Tissue manipulation and securement system |
US7998112B2 (en) | 2003-09-30 | 2011-08-16 | Abbott Cardiovascular Systems Inc. | Deflectable catheter assembly and method of making same |
US7004176B2 (en) * | 2003-10-17 | 2006-02-28 | Edwards Lifesciences Ag | Heart valve leaflet locator |
US7158839B2 (en) * | 2003-11-07 | 2007-01-02 | Paracor Medical, Inc. | Cardiac harness for treating heart disease |
US20060276684A1 (en) | 2003-11-07 | 2006-12-07 | Giovanni Speziali | Device and method for treating congestive heart failure |
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 |
US20050187620A1 (en) * | 2003-11-14 | 2005-08-25 | Suresh Pai | Systems for heart treatment |
US7347863B2 (en) | 2004-05-07 | 2008-03-25 | Usgi Medical, Inc. | Apparatus and methods for manipulating and securing tissue |
US7361180B2 (en) | 2004-05-07 | 2008-04-22 | Usgi Medical, Inc. | Apparatus for manipulating and securing tissue |
US20050251189A1 (en) | 2004-05-07 | 2005-11-10 | Usgi Medical Inc. | Multi-position tissue manipulation assembly |
US20050273138A1 (en) * | 2003-12-19 | 2005-12-08 | Guided Delivery Systems, Inc. | Devices and methods for anchoring tissue |
US8864822B2 (en) | 2003-12-23 | 2014-10-21 | Mitralign, Inc. | Devices and methods for introducing elements into tissue |
US7166127B2 (en) * | 2003-12-23 | 2007-01-23 | Mitralign, Inc. | Tissue fastening systems and methods utilizing magnetic guidance |
US20050148814A1 (en) * | 2004-01-05 | 2005-07-07 | Fischi Michael C. | Muscle function augmentation |
EP1703854A1 (en) * | 2004-01-12 | 2006-09-27 | Paracor Medical, Inc. | Cardiac harness having interconnected strands |
US7703459B2 (en) | 2004-03-09 | 2010-04-27 | Usgi Medical, Inc. | Apparatus and methods for mapping out endoluminal gastrointestinal surgery |
US7758491B2 (en) * | 2004-04-05 | 2010-07-20 | Genesee Biomedical, Inc. | Method and apparatus for the surgical treatment of congestive heart failure |
US7993397B2 (en) * | 2004-04-05 | 2011-08-09 | Edwards Lifesciences Ag | Remotely adjustable coronary sinus implant |
US7736374B2 (en) | 2004-05-07 | 2010-06-15 | Usgi Medical, Inc. | Tissue manipulation and securement system |
US8444657B2 (en) | 2004-05-07 | 2013-05-21 | Usgi Medical, Inc. | Apparatus and methods for rapid deployment of tissue anchors |
US8257394B2 (en) | 2004-05-07 | 2012-09-04 | Usgi Medical, Inc. | Apparatus and methods for positioning and securing anchors |
US7918869B2 (en) | 2004-05-07 | 2011-04-05 | Usgi Medical, Inc. | Methods and apparatus for performing endoluminal gastroplasty |
US8206417B2 (en) | 2004-06-09 | 2012-06-26 | Usgi Medical Inc. | Apparatus and methods for optimizing anchoring force |
US7736379B2 (en) | 2004-06-09 | 2010-06-15 | Usgi Medical, Inc. | Compressible tissue anchor assemblies |
US7678135B2 (en) | 2004-06-09 | 2010-03-16 | Usgi Medical, Inc. | Compressible tissue anchor assemblies |
US7695493B2 (en) | 2004-06-09 | 2010-04-13 | Usgi Medical, Inc. | System for optimizing anchoring force |
US7601117B2 (en) * | 2004-06-30 | 2009-10-13 | Ethicon, Inc. | Systems and methods for assisting cardiac valve coaptation |
DE102004040135B3 (en) * | 2004-08-19 | 2005-12-15 | Abg Allgemeine Baumaschinen-Gesellschaft Mbh | Self-propelled device for milling traffic areas |
AU2005286101A1 (en) * | 2004-09-22 | 2006-03-30 | Corassist Cardiovascular Ltd. | In vivo device for assisting and improving diastolic ventricular function |
US8052592B2 (en) | 2005-09-27 | 2011-11-08 | Evalve, Inc. | Methods and devices for tissue grasping and assessment |
CA2748617C (en) | 2004-09-27 | 2014-09-23 | Evalve, Inc. | Methods and devices for tissue grasping and assessment |
US20060079736A1 (en) | 2004-10-13 | 2006-04-13 | Sing-Fatt Chin | Method and device for percutaneous left ventricular reconstruction |
US20060089711A1 (en) * | 2004-10-27 | 2006-04-27 | Medtronic Vascular, Inc. | Multifilament anchor for reducing a compass of a lumen or structure in mammalian body |
US20060135966A1 (en) * | 2004-11-15 | 2006-06-22 | Laurent Schaller | Catheter-based tissue remodeling devices and methods |
WO2006055820A2 (en) * | 2004-11-19 | 2006-05-26 | G & L Consulting Llc | Biodegradable pericardial constraint system and method |
US7211110B2 (en) * | 2004-12-09 | 2007-05-01 | Edwards Lifesciences Corporation | Diagnostic kit to assist with heart valve annulus adjustment |
WO2006078694A2 (en) | 2005-01-21 | 2006-07-27 | Mayo Foundation For Medical Education And Research | Thorascopic heart valve repair method and apparatus |
EP3967269A3 (en) | 2005-02-07 | 2022-07-13 | Evalve, Inc. | Systems and devices for cardiac valve repair |
US20100298929A1 (en) * | 2005-02-07 | 2010-11-25 | Thornton Troy L | Methods, systems and devices for cardiac valve repair |
US8470028B2 (en) | 2005-02-07 | 2013-06-25 | Evalve, Inc. | Methods, systems and devices for cardiac valve repair |
US7320665B2 (en) * | 2005-03-02 | 2008-01-22 | Venkataramana Vijay | Cardiac Ventricular Geometry Restoration Device and Treatment for Heart Failure |
US20060199995A1 (en) * | 2005-03-02 | 2006-09-07 | Venkataramana Vijay | Percutaneous cardiac ventricular geometry restoration device and treatment for heart failure |
US10219902B2 (en) | 2005-03-25 | 2019-03-05 | Mvrx, Inc. | Devices, systems, and methods for reshaping a heart valve anulus, including the use of a bridge implant having an adjustable bridge stop |
US8333777B2 (en) * | 2005-04-22 | 2012-12-18 | Benvenue Medical, Inc. | Catheter-based tissue remodeling devices and methods |
US8298291B2 (en) | 2005-05-26 | 2012-10-30 | Usgi Medical, Inc. | Methods and apparatus for securing and deploying tissue anchors |
US9585651B2 (en) | 2005-05-26 | 2017-03-07 | Usgi Medical, Inc. | Methods and apparatus for securing and deploying tissue anchors |
US7621866B2 (en) * | 2005-05-31 | 2009-11-24 | Ethicon, Inc. | Method and device for deployment of a sub-pericardial sack |
US7766816B2 (en) | 2005-06-09 | 2010-08-03 | Chf Technologies, Inc. | Method and apparatus for closing off a portion of a heart ventricle |
US8951285B2 (en) | 2005-07-05 | 2015-02-10 | Mitralign, Inc. | Tissue anchor, anchoring system and methods of using the same |
JP4376836B2 (en) * | 2005-07-29 | 2009-12-02 | 富士フイルム株式会社 | Magnetic recording device |
US20070055206A1 (en) * | 2005-08-10 | 2007-03-08 | Guided Delivery Systems, Inc. | Methods and devices for deployment of tissue anchors |
WO2007022519A2 (en) | 2005-08-19 | 2007-02-22 | Chf Technologies, Inc. | Steerable heart implants for congestive heart failure |
US8506474B2 (en) | 2005-08-19 | 2013-08-13 | Bioventrix, Inc. | Method and device for treating dysfunctional cardiac tissue |
US20070078297A1 (en) * | 2005-08-31 | 2007-04-05 | Medtronic Vascular, Inc. | Device for Treating Mitral Valve Regurgitation |
US7715918B2 (en) | 2005-10-18 | 2010-05-11 | University Of Cincinnati | Muscle energy converter with smooth continuous tissue interface |
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 |
US8726909B2 (en) | 2006-01-27 | 2014-05-20 | Usgi Medical, Inc. | Methods and apparatus for revision of obesity procedures |
US7749249B2 (en) | 2006-02-21 | 2010-07-06 | Kardium Inc. | Method and device for closing holes in tissue |
US20070203391A1 (en) * | 2006-02-24 | 2007-08-30 | Medtronic Vascular, Inc. | System for Treating Mitral Valve Regurgitation |
US20070208217A1 (en) * | 2006-03-03 | 2007-09-06 | Acorn Cardiovascular, Inc. | Self-adjusting attachment structure for a cardiac support device |
US7691151B2 (en) | 2006-03-31 | 2010-04-06 | Spiration, Inc. | Articulable Anchor |
US20070265658A1 (en) * | 2006-05-12 | 2007-11-15 | Aga Medical Corporation | Anchoring and tethering system |
US20070270882A1 (en) * | 2006-05-19 | 2007-11-22 | Acorn Cardiovascular, Inc. | Pericardium management method for intra-pericardial surgical procedures |
US8449605B2 (en) | 2006-06-28 | 2013-05-28 | Kardium Inc. | Method for anchoring a mitral valve |
US20080004488A1 (en) * | 2006-06-29 | 2008-01-03 | Acorn Cardiovascular, Inc. | Low friction delivery tool for a cardiac support device |
US8870916B2 (en) | 2006-07-07 | 2014-10-28 | USGI Medical, Inc | Low profile tissue anchors, tissue anchor systems, and methods for their delivery and use |
US7651462B2 (en) | 2006-07-17 | 2010-01-26 | Acorn Cardiovascular, Inc. | Cardiac support device delivery tool with release mechanism |
US7837610B2 (en) * | 2006-08-02 | 2010-11-23 | Kardium Inc. | System for improving diastolic dysfunction |
US7875017B2 (en) * | 2007-04-11 | 2011-01-25 | Henry Ford Health System | Cardiac repair, resizing and reshaping using the venous system of the heart |
US9782258B2 (en) * | 2006-09-08 | 2017-10-10 | The Regents Of The University Of California | Intramyocardial patterning for global cardiac resizing and reshaping |
US20080071365A1 (en) * | 2006-09-19 | 2008-03-20 | Astudillo Medical Aktiebolag | Transpericardial mitral annuloplasty system for the treatment of ischemic mitral regurgitation |
US7641608B1 (en) | 2006-09-26 | 2010-01-05 | Acorn Cardiovascular, Inc. | Sectional cardiac support device and method of delivery |
US8123668B2 (en) | 2006-09-28 | 2012-02-28 | Bioventrix (A Chf Technologies' Company) | Signal transmitting and lesion excluding heart implants for pacing defibrillating and/or sensing of heart beat |
US9211115B2 (en) | 2006-09-28 | 2015-12-15 | Bioventrix, Inc. | Location, time, and/or pressure determining devices, systems, and methods for deployment of lesion-excluding heart implants for treatment of cardiac heart failure and other disease states |
US20080082170A1 (en) * | 2006-09-29 | 2008-04-03 | Peterman Marc M | Apparatus and methods for surgical repair |
US20080091057A1 (en) * | 2006-10-11 | 2008-04-17 | Cardiac Pacemakers, Inc. | Method and apparatus for passive left atrial support |
US8388680B2 (en) | 2006-10-18 | 2013-03-05 | Guided Delivery Systems, Inc. | Methods and devices for catheter advancement and delivery of substances therethrough |
US11660190B2 (en) | 2007-03-13 | 2023-05-30 | Edwards Lifesciences Corporation | Tissue anchors, systems and methods, and devices |
US8911461B2 (en) | 2007-03-13 | 2014-12-16 | Mitralign, Inc. | Suture cutter and method of cutting suture |
US8845723B2 (en) | 2007-03-13 | 2014-09-30 | Mitralign, Inc. | Systems and methods for introducing elements into tissue |
WO2008154033A2 (en) * | 2007-06-11 | 2008-12-18 | Symphony Medical, Inc. | Cardiac patterning for improving diastolic function |
US20080082168A1 (en) * | 2007-07-31 | 2008-04-03 | Marc Peterman | Surgical scaffold to enhance fibrous tissue response |
US8192351B2 (en) | 2007-08-13 | 2012-06-05 | Paracor Medical, Inc. | Medical device delivery system having integrated introducer |
US8092363B2 (en) * | 2007-09-05 | 2012-01-10 | Mardil, Inc. | Heart band with fillable chambers to modify heart valve function |
DE102007043830A1 (en) | 2007-09-13 | 2009-04-02 | Lozonschi, Lucian, Madison | Heart valve stent |
US8491455B2 (en) | 2007-10-03 | 2013-07-23 | Bioventrix, Inc. | Treating dysfunctional cardiac tissue |
JP5357167B2 (en) | 2007-10-18 | 2013-12-04 | ネオコード インコーポレイテッド | Instrument for repairing pulsating leaflets in the heart with minimal invasiveness |
CA2702615C (en) * | 2007-10-19 | 2017-06-06 | Guided Delivery Systems, Inc. | Systems and methods for cardiac remodeling |
US9131928B2 (en) | 2007-12-20 | 2015-09-15 | Mor Research Applications Ltd. | Elongated body for deployment in a heart |
WO2009100242A2 (en) | 2008-02-06 | 2009-08-13 | Guided Delivery Systems, Inc. | Multi-window guide tunnel |
CA2723810C (en) * | 2008-05-07 | 2015-06-30 | Guided Delivery Systems, Inc. | Deflectable guide |
US20090287304A1 (en) | 2008-05-13 | 2009-11-19 | Kardium Inc. | Medical Device for Constricting Tissue or a Bodily Orifice, for example a mitral valve |
US8337390B2 (en) * | 2008-07-30 | 2012-12-25 | Cube S.R.L. | Intracardiac device for restoring the functional elasticity of the cardiac structures, holding tool for the intracardiac device, and method for implantation of the intracardiac device in the heart |
US20100121349A1 (en) * | 2008-10-10 | 2010-05-13 | Meier Stephen C | Termination devices and related methods |
EP2349020B1 (en) * | 2008-10-10 | 2020-06-03 | Ancora Heart, Inc. | Tether tensioning device |
EP2349086B1 (en) | 2008-10-16 | 2017-03-22 | Medtronic Vascular, Inc. | Devices and systems for endovascular staple and/or prosthesis delivery and implantation |
WO2010085456A1 (en) | 2009-01-20 | 2010-07-29 | Guided Delivery Systems Inc. | Anchor deployment devices and related methods |
US20100210899A1 (en) * | 2009-01-21 | 2010-08-19 | Tendyne Medical, Inc. | Method for percutaneous lateral access to the left ventricle for treatment of mitral insufficiency by papillary muscle alignment |
US20100274227A1 (en) * | 2009-02-13 | 2010-10-28 | Alexander Khairkhahan | Delivery catheter handle cover |
US20110015476A1 (en) * | 2009-03-04 | 2011-01-20 | Jeff Franco | Devices and Methods for Treating Cardiomyopathy |
US8449466B2 (en) | 2009-05-28 | 2013-05-28 | Edwards Lifesciences Corporation | System and method for locating medical devices in vivo using ultrasound Doppler mode |
EP3042615A1 (en) | 2009-09-15 | 2016-07-13 | Evalve, Inc. | Methods, systems and devices for cardiac valve repair |
EP2482749B1 (en) | 2009-10-01 | 2017-08-30 | Kardium Inc. | Kit for constricting tissue or a bodily orifice, for example, a mitral valve |
CA2777495A1 (en) | 2009-10-26 | 2011-05-12 | Cardiokinetix, Inc. | Ventricular volume reduction |
WO2011072084A2 (en) | 2009-12-08 | 2011-06-16 | Avalon Medical Ltd. | Device and system for transcatheter mitral valve replacement |
US9307980B2 (en) | 2010-01-22 | 2016-04-12 | 4Tech Inc. | Tricuspid valve repair using tension |
US10058323B2 (en) | 2010-01-22 | 2018-08-28 | 4 Tech Inc. | Tricuspid valve repair using tension |
US8475525B2 (en) | 2010-01-22 | 2013-07-02 | 4Tech Inc. | Tricuspid valve repair using tension |
WO2011109813A2 (en) * | 2010-03-05 | 2011-09-09 | Edwards Lifesciences Corporation | Retaining mechanisms for prosthetic valves |
US9050066B2 (en) | 2010-06-07 | 2015-06-09 | Kardium Inc. | Closing openings in anatomical tissue |
US9861350B2 (en) | 2010-09-03 | 2018-01-09 | Ancora Heart, Inc. | Devices and methods for anchoring tissue |
US8940002B2 (en) | 2010-09-30 | 2015-01-27 | Kardium Inc. | Tissue anchor system |
CN103347464B (en) | 2010-12-29 | 2016-02-03 | 尼奥绰德有限公司 | The replaceable system of beating heart valve leaflet is repaired by Wicresoft |
US8888843B2 (en) | 2011-01-28 | 2014-11-18 | Middle Peak Medical, Inc. | Device, system, and method for transcatheter treatment of valve regurgitation |
US8845717B2 (en) | 2011-01-28 | 2014-09-30 | Middle Park Medical, Inc. | Coaptation enhancement implant, system, and method |
US10709449B2 (en) | 2011-02-18 | 2020-07-14 | Ancora Heart, Inc. | Systems and methods for variable stiffness tethers |
US10111663B2 (en) | 2011-02-18 | 2018-10-30 | Ancora Heart, Inc. | Implant retrieval device |
US9072511B2 (en) | 2011-03-25 | 2015-07-07 | Kardium Inc. | Medical kit for constricting tissue or a bodily orifice, for example, a mitral valve |
US8795241B2 (en) | 2011-05-13 | 2014-08-05 | Spiration, Inc. | Deployment catheter |
CA2837206C (en) | 2011-06-01 | 2019-09-24 | John Zentgraf | Minimally invasive repair of heart valve leaflets |
EP4289398A3 (en) | 2011-08-11 | 2024-03-13 | Tendyne Holdings, Inc. | Improvements for prosthetic valves and related inventions |
US8945177B2 (en) | 2011-09-13 | 2015-02-03 | Abbott Cardiovascular Systems Inc. | Gripper pusher mechanism for tissue apposition systems |
EP3175797B1 (en) | 2011-09-30 | 2020-02-12 | Bioventrix, Inc. | Trans-catheter ventricular reconstruction structures and systems for treatment of congestive heart failure and other conditions |
US9827092B2 (en) | 2011-12-16 | 2017-11-28 | Tendyne Holdings, Inc. | Tethers for prosthetic mitral valve |
JP6084775B2 (en) * | 2012-03-09 | 2017-02-22 | 学校法人金沢医科大学 | Heart correction net |
US9265514B2 (en) | 2012-04-17 | 2016-02-23 | Miteas Ltd. | Manipulator for grasping tissue |
WO2014022124A1 (en) | 2012-07-28 | 2014-02-06 | Tendyne Holdings, Inc. | Improved 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 |
EP2943132B1 (en) | 2013-01-09 | 2018-03-28 | 4Tech Inc. | Soft tissue anchors |
WO2014141239A1 (en) | 2013-03-14 | 2014-09-18 | 4Tech Inc. | Stent with tether interface |
US11224510B2 (en) | 2013-04-02 | 2022-01-18 | Tendyne Holdings, Inc. | Prosthetic heart valve and systems and methods for delivering the same |
US10463489B2 (en) | 2013-04-02 | 2019-11-05 | Tendyne Holdings, Inc. | Prosthetic heart valve and systems and methods for delivering the same |
US9486306B2 (en) | 2013-04-02 | 2016-11-08 | Tendyne Holdings, Inc. | Inflatable annular sealing device for prosthetic mitral valve |
US10478293B2 (en) | 2013-04-04 | 2019-11-19 | Tendyne Holdings, Inc. | Retrieval and repositioning system for prosthetic heart valve |
AU2014268717A1 (en) | 2013-05-24 | 2015-12-03 | Bioventrix, Inc. | Cardiac tissue penetrating devices, methods, and systems for treatment of congestive heart failure and other conditions |
US9610159B2 (en) | 2013-05-30 | 2017-04-04 | Tendyne Holdings, Inc. | Structural members for prosthetic mitral valves |
JP6461122B2 (en) | 2013-06-25 | 2019-01-30 | テンダイン ホールディングス,インコーポレイテッド | Thrombus management and structural compliance features of prosthetic heart valves |
EP3027144B1 (en) | 2013-08-01 | 2017-11-08 | Tendyne Holdings, Inc. | Epicardial anchor devices |
CA2922132A1 (en) | 2013-08-30 | 2015-03-05 | Bioventrix, Inc. | Heart anchor positioning devices, methods, and systems for treatment of congestive heart failure and other conditions |
CA2922126A1 (en) | 2013-08-30 | 2015-03-05 | Bioventrix, Inc. | Cardiac tissue anchoring devices, methods, and systems for treatment of congestive heart failure and other conditions |
US10070857B2 (en) | 2013-08-31 | 2018-09-11 | Mitralign, Inc. | Devices and methods for locating and implanting tissue anchors at mitral valve commissure |
USD717954S1 (en) | 2013-10-14 | 2014-11-18 | Mardil, Inc. | Heart treatment device |
WO2015058039A1 (en) | 2013-10-17 | 2015-04-23 | Robert Vidlund | Apparatus and methods for alignment and deployment of intracardiac devices |
US10166098B2 (en) | 2013-10-25 | 2019-01-01 | Middle Peak Medical, Inc. | Systems and methods for transcatheter treatment of valve regurgitation |
EP3656353A1 (en) | 2013-10-28 | 2020-05-27 | Tendyne Holdings, Inc. | Prosthetic heart valve and systems for delivering the same |
US9526611B2 (en) | 2013-10-29 | 2016-12-27 | Tendyne Holdings, Inc. | Apparatus and methods for delivery of transcatheter prosthetic valves |
US10052095B2 (en) | 2013-10-30 | 2018-08-21 | 4Tech Inc. | Multiple anchoring-point tension system |
US10022114B2 (en) | 2013-10-30 | 2018-07-17 | 4Tech Inc. | Percutaneous tether locking |
WO2015120122A2 (en) | 2014-02-05 | 2015-08-13 | Robert Vidlund | Apparatus and methods for transfemoral delivery of prosthetic mitral valve |
US9986993B2 (en) | 2014-02-11 | 2018-06-05 | Tendyne Holdings, Inc. | Adjustable tether and epicardial pad system for prosthetic heart valve |
AU2015229708B2 (en) | 2014-03-10 | 2019-08-15 | Tendyne Holdings, Inc. | Devices and methods for positioning and monitoring tether load for prosthetic mitral valve |
US10390943B2 (en) | 2014-03-17 | 2019-08-27 | Evalve, Inc. | Double orifice device for transcatheter mitral valve replacement |
CA2951413C (en) | 2014-06-12 | 2019-07-02 | The Cleveland Clinic Foundation | Device, system, and method for treating a regurgitant heart valve |
CA2958061A1 (en) | 2014-06-18 | 2015-12-23 | Middle Peak Medical, Inc. | Mitral valve implants for the treatment of valvular regurgitation |
CN106573129B (en) * | 2014-06-19 | 2019-09-24 | 4科技有限公司 | Heart tissue is tightened |
EP3160396B1 (en) | 2014-06-24 | 2022-03-23 | Polares Medical Inc. | Systems for anchoring an implant |
WO2016048802A1 (en) | 2014-09-28 | 2016-03-31 | Cardiokinetix, Inc. | Apparatuses for treating cardiac dysfunction |
US9907547B2 (en) | 2014-12-02 | 2018-03-06 | 4Tech Inc. | Off-center tissue anchors |
US10188392B2 (en) | 2014-12-19 | 2019-01-29 | Abbott Cardiovascular Systems, Inc. | Grasping for tissue repair |
EP3242630A2 (en) | 2015-01-07 | 2017-11-15 | Tendyne Holdings, Inc. | Prosthetic mitral valves and apparatus and methods for delivery of same |
CA2975294A1 (en) | 2015-02-05 | 2016-08-11 | Tendyne Holdings, Inc. | Expandable epicardial pads and devices and methods for delivery of same |
CA2978599C (en) | 2015-03-05 | 2022-09-06 | Ancora Heart, Inc. | Devices and methods of visualizing and determining depth of penetration in cardiac tissue |
US10201423B2 (en) | 2015-03-11 | 2019-02-12 | Mvrx, Inc. | Devices, systems, and methods for reshaping a heart valve annulus |
US10524912B2 (en) | 2015-04-02 | 2020-01-07 | Abbott Cardiovascular Systems, Inc. | Tissue fixation devices and methods |
CA2983002C (en) | 2015-04-16 | 2023-07-04 | Tendyne Holdings, Inc. | Apparatus and methods for delivery, repositioning, and retrieval of transcatheter prosthetic valves |
US10980973B2 (en) | 2015-05-12 | 2021-04-20 | Ancora Heart, Inc. | Device and method for releasing catheters from cardiac structures |
US10376673B2 (en) | 2015-06-19 | 2019-08-13 | Evalve, Inc. | Catheter guiding system and methods |
US10238494B2 (en) | 2015-06-29 | 2019-03-26 | Evalve, Inc. | Self-aligning radiopaque ring |
US10667815B2 (en) | 2015-07-21 | 2020-06-02 | Evalve, Inc. | Tissue grasping devices and related methods |
US10413408B2 (en) | 2015-08-06 | 2019-09-17 | Evalve, Inc. | Delivery catheter systems, methods, and devices |
US10206779B2 (en) | 2015-09-10 | 2019-02-19 | Bioventrix, Inc. | Systems and methods for deploying a cardiac anchor |
US10327894B2 (en) | 2015-09-18 | 2019-06-25 | Tendyne Holdings, Inc. | Methods for delivery of prosthetic mitral valves |
WO2017059406A1 (en) | 2015-10-01 | 2017-04-06 | Neochord, Inc. | Ringless web for repair of heart valves |
US10238495B2 (en) | 2015-10-09 | 2019-03-26 | Evalve, Inc. | Delivery catheter handle and methods of use |
US9592121B1 (en) | 2015-11-06 | 2017-03-14 | Middle Peak Medical, Inc. | Device, system, and method for transcatheter treatment of valvular regurgitation |
ES2777609T3 (en) | 2015-12-03 | 2020-08-05 | Tendyne Holdings Inc | Framework Features for Prosthetic Mitral Valves |
AU2016366840B2 (en) | 2015-12-10 | 2021-09-23 | Mvrx, Inc. | Devices, systems, and methods for reshaping a heart valve annulus |
CN108366859B (en) | 2015-12-28 | 2021-02-05 | 坦迪尼控股股份有限公司 | Atrial capsular bag closure for prosthetic heart valves |
US11478353B2 (en) | 2016-01-29 | 2022-10-25 | Bioventrix, Inc. | Percutaneous arterial access to position trans-myocardial implant devices and methods |
US10470877B2 (en) | 2016-05-03 | 2019-11-12 | Tendyne Holdings, Inc. | Apparatus and methods for anterior valve leaflet management |
EP3468480B1 (en) | 2016-06-13 | 2023-01-11 | Tendyne Holdings, Inc. | Sequential delivery of two-part prosthetic mitral valve |
WO2018005779A1 (en) | 2016-06-30 | 2018-01-04 | Tegels Zachary J | Prosthetic heart valves and apparatus and methods for delivery of same |
US10736632B2 (en) | 2016-07-06 | 2020-08-11 | Evalve, Inc. | Methods and devices for valve clip excision |
US11065116B2 (en) | 2016-07-12 | 2021-07-20 | Tendyne Holdings, Inc. | Apparatus and methods for trans-septal retrieval of prosthetic heart valves |
US11071564B2 (en) | 2016-10-05 | 2021-07-27 | Evalve, Inc. | Cardiac valve cutting device |
US10363138B2 (en) | 2016-11-09 | 2019-07-30 | Evalve, Inc. | Devices for adjusting the curvature of cardiac valve structures |
US10398553B2 (en) | 2016-11-11 | 2019-09-03 | Evalve, Inc. | Opposing disk device for grasping cardiac valve tissue |
US10426616B2 (en) | 2016-11-17 | 2019-10-01 | Evalve, Inc. | Cardiac implant delivery system |
US10667914B2 (en) | 2016-11-18 | 2020-06-02 | Ancora Heart, Inc. | Myocardial implant load sharing device and methods to promote LV function |
US10779837B2 (en) | 2016-12-08 | 2020-09-22 | Evalve, Inc. | Adjustable arm device for grasping tissues |
US10314586B2 (en) | 2016-12-13 | 2019-06-11 | Evalve, Inc. | Rotatable device and method for fixing tricuspid valve tissue |
US10653524B2 (en) | 2017-03-13 | 2020-05-19 | Polares Medical Inc. | Device, system, and method for transcatheter treatment of valvular regurgitation |
CN110913801B (en) | 2017-03-13 | 2022-04-15 | 宝来瑞斯医疗有限公司 | Coaptation assistance element for treating an adverse coaptation of a heart valve of a heart and system for delivering the same |
US10478303B2 (en) | 2017-03-13 | 2019-11-19 | Polares Medical Inc. | Device, system, and method for transcatheter treatment of valvular regurgitation |
DE102018107407A1 (en) | 2017-03-28 | 2018-10-04 | Edwards Lifesciences Corporation | POSITIONING, INSERTING AND RETRIEVING IMPLANTABLE DEVICES |
US10213306B2 (en) | 2017-03-31 | 2019-02-26 | Neochord, Inc. | Minimally invasive heart valve repair in a beating heart |
WO2018209313A1 (en) | 2017-05-12 | 2018-11-15 | Evalve, Inc. | Long arm valve repair clip |
WO2019014473A1 (en) | 2017-07-13 | 2019-01-17 | Tendyne Holdings, Inc. | Prosthetic heart valves and apparatus and methods for delivery of same |
JP7291124B2 (en) | 2017-08-28 | 2023-06-14 | テンダイン ホールディングス,インコーポレイテッド | Heart valve prosthesis with tethered connections |
EP3768176B1 (en) | 2018-03-23 | 2024-03-20 | NeoChord, Inc. | Device for suture attachment for minimally invasive heart valve repair |
US11253360B2 (en) | 2018-05-09 | 2022-02-22 | Neochord, Inc. | Low profile tissue anchor for minimally invasive heart valve repair |
US11173030B2 (en) | 2018-05-09 | 2021-11-16 | Neochord, Inc. | Suture length adjustment for minimally invasive heart valve repair |
CN113194854A (en) | 2018-09-07 | 2021-07-30 | 尼奥绰德有限公司 | Suture attachment device for minimally invasive heart valve repair |
EP3955855A4 (en) | 2019-04-16 | 2023-01-25 | NeoChord, Inc. | Transverse helical cardiac anchor for minimally invasive heart valve repair |
WO2021011659A1 (en) | 2019-07-15 | 2021-01-21 | Ancora Heart, Inc. | Devices and methods for tether cutting |
EP3831343B1 (en) | 2019-12-05 | 2024-01-31 | Tendyne Holdings, Inc. | Braided anchor for mitral valve |
US11648114B2 (en) | 2019-12-20 | 2023-05-16 | Tendyne Holdings, Inc. | Distally loaded sheath and loading funnel |
US11951002B2 (en) | 2020-03-30 | 2024-04-09 | Tendyne Holdings, Inc. | Apparatus and methods for valve and tether fixation |
WO2022039853A1 (en) | 2020-08-19 | 2022-02-24 | Tendyne Holdings, Inc. | Fully-transseptal apical pad with pulley for tensioning |
US11464634B2 (en) | 2020-12-16 | 2022-10-11 | Polares Medical Inc. | Device, system, and method for transcatheter treatment of valvular regurgitation with secondary anchors |
US11759321B2 (en) | 2021-06-25 | 2023-09-19 | Polares Medical Inc. | Device, system, and method for transcatheter treatment of valvular regurgitation |
Family Cites Families (150)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US34021A (en) * | 1861-12-24 | Ufacture of fibrous water | ||
US3019790A (en) | 1960-07-15 | 1962-02-06 | Robert J Militana | Combination hemostat and intravenous needle |
US3980086A (en) | 1974-02-28 | 1976-09-14 | Bio-Medicus, Inc. | Fluid conveying surgical instrument |
US4192293A (en) * | 1978-09-05 | 1980-03-11 | Manfred Asrican | Cardiac assist device |
ES474582A1 (en) * | 1978-10-26 | 1979-11-01 | Aranguren Duo Iker | Process for installing mitral valves in their anatomical space by attaching cords to an artificial stent |
JPS5563638A (en) | 1978-11-09 | 1980-05-13 | Olympus Optical Co | Renal pelvis forceps |
US4372293A (en) | 1980-12-24 | 1983-02-08 | Vijil Rosales Cesar A | Apparatus and method for surgical correction of ptotic breasts |
US4409974A (en) * | 1981-06-29 | 1983-10-18 | Freedland Jeffrey A | Bone-fixating surgical implant device |
IT1155105B (en) * | 1982-03-03 | 1987-01-21 | Roberto Parravicini | PLANT DEVICE TO SUPPORT THE MYOCARDIUM ACTIVITY |
US5104392A (en) * | 1985-03-22 | 1992-04-14 | Massachusetts Institute Of Technology | Laser spectro-optic imaging for diagnosis and treatment of diseased tissue |
US4690134A (en) | 1985-07-01 | 1987-09-01 | Snyders Robert V | Ventricular assist device |
US4705040A (en) | 1985-11-18 | 1987-11-10 | Medi-Tech, Incorporated | Percutaneous fixation of hollow organs |
USRE34021E (en) | 1985-11-18 | 1992-08-04 | Abbott Laboratories | Percutaneous fixation of hollow organs |
DE3614292C1 (en) | 1986-04-26 | 1987-11-19 | Alexander Prof Dr Bernhard | Holder for unframed biological mitral valve implant |
SU1604377A1 (en) * | 1987-02-23 | 1990-11-07 | Благовещенский государственный медицинский институт | Artificial pericardium |
US4925443A (en) | 1987-02-27 | 1990-05-15 | Heilman Marlin S | Biocompatible ventricular assist and arrhythmia control device |
US4960424A (en) * | 1988-06-30 | 1990-10-02 | Grooters Ronald K | Method of replacing a defective atrio-ventricular valve with a total atrio-ventricular valve bioprosthesis |
US4944753A (en) * | 1988-09-26 | 1990-07-31 | Burgess Frank M | Method for producing retro-sternal space |
US5290300A (en) | 1989-07-31 | 1994-03-01 | Baxter International Inc. | Flexible suture guide and holder |
US4997431A (en) * | 1989-08-30 | 1991-03-05 | Angeion Corporation | Catheter |
GB9012716D0 (en) * | 1990-06-07 | 1990-08-01 | Frater Robert W M | Mitral heart valve replacements |
US5131905A (en) * | 1990-07-16 | 1992-07-21 | Grooters Ronald K | External cardiac assist device |
JPH05184611A (en) | 1991-03-19 | 1993-07-27 | Kenji Kusuhara | Valvular annulation retaining member and its attaching method |
US5300087A (en) | 1991-03-22 | 1994-04-05 | Knoepfler Dennis J | Multiple purpose forceps |
US5169381A (en) * | 1991-03-29 | 1992-12-08 | Snyders Robert V | Ventricular assist device |
US5584803A (en) * | 1991-07-16 | 1996-12-17 | Heartport, Inc. | System for cardiac procedures |
US5571215A (en) * | 1993-02-22 | 1996-11-05 | Heartport, Inc. | Devices and methods for intracardiac procedures |
US5452733A (en) * | 1993-02-22 | 1995-09-26 | Stanford Surgical Technologies, Inc. | Methods for performing thoracoscopic coronary artery bypass |
US5458574A (en) * | 1994-03-16 | 1995-10-17 | Heartport, Inc. | System for performing a cardiac procedure |
US5344385A (en) | 1991-09-30 | 1994-09-06 | Thoratec Laboratories Corporation | Step-down skeletal muscle energy conversion system |
US5192314A (en) * | 1991-12-12 | 1993-03-09 | Daskalakis Michael K | Synthetic intraventricular implants and method of inserting |
US5250049A (en) * | 1992-01-10 | 1993-10-05 | Michael Roger H | Bone and tissue connectors |
US5758663A (en) | 1992-04-10 | 1998-06-02 | Wilk; Peter J. | Coronary artery by-pass method |
US5733331A (en) * | 1992-07-28 | 1998-03-31 | Newcor Industrial S.A. | Total mitral heterologous bioprosthesis to be used in mitral or tricuspid heat replacement |
DE4234127C2 (en) * | 1992-10-09 | 1996-02-22 | Herbert Dr Vetter | Heart valve prosthesis |
US5718725A (en) * | 1992-12-03 | 1998-02-17 | Heartport, Inc. | Devices and methods for intracardiac procedures |
US5814097A (en) * | 1992-12-03 | 1998-09-29 | Heartport, Inc. | Devices and methods for intracardiac procedures |
US5284488A (en) * | 1992-12-23 | 1994-02-08 | Sideris Eleftherios B | Adjustable devices for the occlusion of cardiac defects |
US6125852A (en) | 1993-02-22 | 2000-10-03 | Heartport, Inc. | Minimally-invasive devices and methods for treatment of congestive heart failure |
US20020029783A1 (en) | 1993-02-22 | 2002-03-14 | Stevens John H. | Minimally-invasive devices and methods for treatment of congestive heart failure |
US5972030A (en) | 1993-02-22 | 1999-10-26 | Heartport, Inc. | Less-invasive devices and methods for treatment of cardiac valves |
US5797960A (en) | 1993-02-22 | 1998-08-25 | Stevens; John H. | Method and apparatus for thoracoscopic intracardiac procedures |
US5682906A (en) * | 1993-02-22 | 1997-11-04 | Heartport, Inc. | Methods of performing intracardiac procedures on an arrested heart |
US6010531A (en) | 1993-02-22 | 2000-01-04 | Heartport, Inc. | Less-invasive devices and methods for cardiac valve surgery |
DE4306277C2 (en) | 1993-03-01 | 2000-11-02 | Leibinger Gmbh | Operation marking tool |
US6155968A (en) | 1998-07-23 | 2000-12-05 | Wilk; Peter J. | Method and device for improving cardiac function |
US5800334A (en) | 1993-06-17 | 1998-09-01 | Wilk; Peter J. | Intrapericardial assist device and associated method |
US6258021B1 (en) | 1993-06-17 | 2001-07-10 | Peter J. Wilk | Intrapericardial assist method |
US5971911A (en) | 1993-06-17 | 1999-10-26 | Wilk; Peter J. | Intrapericardial assist device and associated method |
US6572529B2 (en) * | 1993-06-17 | 2003-06-03 | Wilk Patent Development Corporation | Intrapericardial assist method |
US5385528A (en) * | 1993-06-17 | 1995-01-31 | Wilk; Peter J. | Intrapericardial assist device and associated method |
US5533958A (en) * | 1993-06-17 | 1996-07-09 | Wilk; Peter J. | Intrapericardial assist device and associated method |
US5389006A (en) | 1993-08-13 | 1995-02-14 | Burndy Corporation | Lightweight entertainment connector |
US5450860A (en) | 1993-08-31 | 1995-09-19 | W. L. Gore & Associates, Inc. | Device for tissue repair and method for employing same |
AU699189B2 (en) * | 1993-12-17 | 1998-11-26 | Heartport, Inc. | System for cardiac procedures |
US5417709A (en) | 1994-04-12 | 1995-05-23 | Symbiosis Corporation | Endoscopic instrument with end effectors forming suction and/or irrigation lumens |
US5509428A (en) * | 1994-05-31 | 1996-04-23 | Dunlop; Richard W. | Method and apparatus for the creation of tricuspid regurgitation |
US6217610B1 (en) * | 1994-07-29 | 2001-04-17 | Edwards Lifesciences Corporation | Expandable annuloplasty ring |
US5593424A (en) | 1994-08-10 | 1997-01-14 | Segmed, Inc. | Apparatus and method for reducing and stabilizing the circumference of a vascular structure |
US5433727A (en) * | 1994-08-16 | 1995-07-18 | Sideris; Eleftherios B. | Centering buttoned device for the occlusion of large defects for occluding |
JPH08196538A (en) | 1994-09-26 | 1996-08-06 | Ethicon Inc | Tissue sticking apparatus for surgery with elastomer component and method of attaching mesh for surgery to said tissue |
US5849005A (en) * | 1995-06-07 | 1998-12-15 | Heartport, Inc. | Method and apparatus for minimizing the risk of air embolism when performing a procedure in a patient's thoracic cavity |
US6132438A (en) * | 1995-06-07 | 2000-10-17 | Ep Technologies, Inc. | Devices for installing stasis reducing means in body tissue |
US5840059A (en) | 1995-06-07 | 1998-11-24 | Cardiogenesis Corporation | Therapeutic and diagnostic agent delivery |
US5713954A (en) | 1995-06-13 | 1998-02-03 | Abiomed R&D, Inc. | Extra cardiac ventricular assist device |
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 |
DE19538796C2 (en) * | 1995-10-18 | 1999-09-23 | Fraunhofer Ges Forschung | Device for supporting the heart function with elastic filling chambers |
US5662704A (en) * | 1995-12-01 | 1997-09-02 | Medtronic, Inc. | Physiologic mitral valve bioprosthesis |
US6592619B2 (en) * | 1996-01-02 | 2003-07-15 | University Of Cincinnati | Heart wall actuation device for the natural heart |
US6520904B1 (en) * | 1996-01-02 | 2003-02-18 | The University Of Cincinnati | Device and method for restructuring heart chamber geometry |
US5957977A (en) | 1996-01-02 | 1999-09-28 | University Of Cincinnati | Activation device for the natural heart including internal and external support structures |
US6182664B1 (en) | 1996-02-19 | 2001-02-06 | Edwards Lifesciences Corporation | Minimally invasive cardiac valve surgery procedure |
US5853422A (en) | 1996-03-22 | 1998-12-29 | Scimed Life Systems, Inc. | Apparatus and method for closing a septal defect |
US5855601A (en) | 1996-06-21 | 1999-01-05 | The Trustees Of Columbia University In The City Of New York | Artificial heart valve and method and device for implanting the same |
US5972019A (en) | 1996-07-25 | 1999-10-26 | Target Therapeutics, Inc. | Mechanical clot treatment device |
US5755783A (en) | 1996-07-29 | 1998-05-26 | Stobie; Robert | Suture rings for rotatable artificial heart valves |
US5800531A (en) | 1996-09-30 | 1998-09-01 | Baxter International Inc. | Bioprosthetic heart valve implantation device |
US5702343A (en) * | 1996-10-02 | 1997-12-30 | Acorn Medical, Inc. | Cardiac reinforcement device |
US6123662A (en) | 1998-07-13 | 2000-09-26 | Acorn Cardiovascular, Inc. | Cardiac disease treatment and device |
BR9712239A (en) | 1996-10-18 | 2000-01-25 | Cardio Tech Inc | Method and apparatus to assist a heart to pump blood by applying substantially uniform pressure to at least a portion of the ventricles. |
US5827268A (en) | 1996-10-30 | 1998-10-27 | Hearten Medical, Inc. | Device for the treatment of patent ductus arteriosus and method of using the device |
EP0839497A1 (en) * | 1996-11-01 | 1998-05-06 | EndoSonics Corporation | A method for measuring volumetric fluid flow and its velocity profile in a lumen or other body cavity |
US5865749A (en) * | 1996-11-07 | 1999-02-02 | Data Sciences International, Inc. | Blood flow meter apparatus and method of use |
DE29619294U1 (en) | 1996-11-07 | 1997-07-17 | Caic Pero | Heart cuff |
US6120520A (en) | 1997-05-27 | 2000-09-19 | Angiotrax, Inc. | Apparatus and methods for stimulating revascularization and/or tissue growth |
US6206004B1 (en) * | 1996-12-06 | 2001-03-27 | Comedicus Incorporated | Treatment method via the pericardial space |
US6071303A (en) | 1996-12-08 | 2000-06-06 | Hearten Medical, Inc. | Device for the treatment of infarcted tissue and method of treating infarcted tissue |
US5807384A (en) | 1996-12-20 | 1998-09-15 | Eclipse Surgical Technologies, Inc. | Transmyocardial revascularization (TMR) enhanced treatment for coronary artery disease |
US5999678A (en) | 1996-12-27 | 1999-12-07 | Eclipse Surgical Technologies, Inc. | Laser delivery means adapted for drug delivery |
US6077214A (en) | 1998-07-29 | 2000-06-20 | Myocor, Inc. | Stress reduction apparatus and method |
US20030045771A1 (en) * | 1997-01-02 | 2003-03-06 | Schweich Cyril J. | Heart wall tension reduction devices and methods |
US6406420B1 (en) | 1997-01-02 | 2002-06-18 | Myocor, Inc. | Methods and devices for improving cardiac function in hearts |
US6050936A (en) | 1997-01-02 | 2000-04-18 | Myocor, Inc. | Heart wall tension reduction apparatus |
US5961440A (en) | 1997-01-02 | 1999-10-05 | Myocor, Inc. | Heart wall tension reduction apparatus and method |
US6183411B1 (en) | 1998-09-21 | 2001-02-06 | Myocor, Inc. | External stress reduction device and method |
US6045497A (en) * | 1997-01-02 | 2000-04-04 | Myocor, Inc. | Heart wall tension reduction apparatus and method |
US5928224A (en) | 1997-01-24 | 1999-07-27 | Hearten Medical, Inc. | Device for the treatment of damaged heart valve leaflets and methods of using the device |
US6443949B2 (en) * | 1997-03-13 | 2002-09-03 | Biocardia, Inc. | Method of drug delivery to interstitial regions of the myocardium |
US5928281A (en) | 1997-03-27 | 1999-07-27 | Baxter International Inc. | Tissue heart valves |
US5961549A (en) | 1997-04-03 | 1999-10-05 | Baxter International Inc. | Multi-leaflet bioprosthetic heart valve |
US6245102B1 (en) * | 1997-05-07 | 2001-06-12 | Iowa-India Investments Company Ltd. | Stent, stent graft and stent valve |
EP0991373B1 (en) * | 1997-06-21 | 2004-09-15 | Acorn Cardiovascular, Inc. | Bag for at least partially enveloping a heart |
WO1999000059A1 (en) * | 1997-06-27 | 1999-01-07 | The Trustees Of Columbia University In The City Of New York | Method and apparatus for circulatory valve repair |
AU9225598A (en) | 1997-09-04 | 1999-03-22 | Endocore, Inc. | Artificial chordae replacement |
FR2768324B1 (en) | 1997-09-12 | 1999-12-10 | Jacques Seguin | SURGICAL INSTRUMENT FOR PERCUTANEOUSLY FIXING TWO AREAS OF SOFT TISSUE, NORMALLY MUTUALLY REMOTE, TO ONE ANOTHER |
US6338712B2 (en) * | 1997-09-17 | 2002-01-15 | Origin Medsystems, Inc. | Device to permit offpump beating heart coronary bypass surgery |
US6019722A (en) | 1997-09-17 | 2000-02-01 | Guidant Corporation | Device to permit offpump beating heart coronary bypass surgery |
US6086532A (en) * | 1997-09-26 | 2000-07-11 | Ep Technologies, Inc. | Systems for recording use of structures deployed in association with heart tissue |
WO1999022784A1 (en) | 1997-11-03 | 1999-05-14 | Cardio Technologies, Inc. | Method and apparatus for assisting a heart to pump blood |
US6332893B1 (en) | 1997-12-17 | 2001-12-25 | Myocor, Inc. | Valve to myocardium tension members device and method |
US6001126A (en) | 1997-12-24 | 1999-12-14 | Baxter International Inc. | Stentless bioprosthetic heart valve with coronary protuberances and related methods for surgical repair of defective heart valves |
DE69838526T2 (en) | 1998-02-05 | 2008-07-03 | Biosense Webster, Inc., Diamond Bar | Device for releasing a drug in the heart |
US5944738A (en) | 1998-02-06 | 1999-08-31 | Aga Medical Corporation | Percutaneous catheter directed constricting occlusion device |
US6314322B1 (en) | 1998-03-02 | 2001-11-06 | Abiomed, Inc. | System and method for treating dilated cardiomyopathy using end diastolic volume (EDV) sensing |
US6190408B1 (en) * | 1998-03-05 | 2001-02-20 | The University Of Cincinnati | Device and method for restructuring the heart chamber geometry |
US5902229A (en) | 1998-03-30 | 1999-05-11 | Cardio Technologies, Inc. | Drive system for controlling cardiac compression |
US6095968A (en) | 1998-04-10 | 2000-08-01 | Cardio Technologies, Inc. | Reinforcement device |
US6110100A (en) | 1998-04-22 | 2000-08-29 | Scimed Life Systems, Inc. | System for stress relieving the heart muscle and for controlling heart function |
US6221104B1 (en) * | 1998-05-01 | 2001-04-24 | Cor Restore, Inc. | Anterior and interior segment cardiac restoration apparatus and method |
US6544167B2 (en) | 1998-05-01 | 2003-04-08 | Correstore, Inc. | Ventricular restoration patch |
US6024096A (en) | 1998-05-01 | 2000-02-15 | Correstore Inc | Anterior segment ventricular restoration apparatus and method |
US6511426B1 (en) * | 1998-06-02 | 2003-01-28 | Acuson Corporation | Medical diagnostic ultrasound system and method for versatile processing |
US6250308B1 (en) | 1998-06-16 | 2001-06-26 | Cardiac Concepts, Inc. | Mitral valve annuloplasty ring and method of implanting |
EP1102567B1 (en) | 1998-07-13 | 2004-11-10 | Acorn Cardiovascular, Inc. | Cardiac disease treatment device |
US6085754A (en) | 1998-07-13 | 2000-07-11 | Acorn Cardiovascular, Inc. | Cardiac disease treatment method |
US6165183A (en) * | 1998-07-15 | 2000-12-26 | St. Jude Medical, Inc. | Mitral and tricuspid valve repair |
US6547821B1 (en) * | 1998-07-16 | 2003-04-15 | Cardiothoracic Systems, Inc. | Surgical procedures and devices for increasing cardiac output of the heart |
US6260552B1 (en) * | 1998-07-29 | 2001-07-17 | Myocor, Inc. | Transventricular implant tools and devices |
US6251061B1 (en) | 1998-09-09 | 2001-06-26 | Scimed Life Systems, Inc. | Cardiac assist device using field controlled fluid |
US6080532A (en) * | 1998-09-17 | 2000-06-27 | Eastman Kodak Company | Clear duplitized display materials |
DE19947885B4 (en) | 1998-10-05 | 2009-04-09 | Cardiothoracic Systems, Inc., Cupertino | Device for positioning the heart during cardiac surgery while maintaining cardiac output |
US6169922B1 (en) | 1998-11-18 | 2001-01-02 | Acorn Cardiovascular, Inc. | Defibrillating cardiac jacket with interwoven electrode grids |
US6230714B1 (en) | 1998-11-18 | 2001-05-15 | Acorn Cardiovascular, Inc. | Cardiac constraint with prior venus occlusion methods |
US6155972A (en) | 1999-02-02 | 2000-12-05 | Acorn Cardiovascular, Inc. | Cardiac constraint jacket construction |
US6231602B1 (en) | 1999-04-16 | 2001-05-15 | Edwards Lifesciences Corporation | Aortic annuloplasty ring |
US6577902B1 (en) | 1999-04-16 | 2003-06-10 | Tony R. Brown | Device for shaping infarcted heart tissue and method of using the device |
US6260820B1 (en) | 1999-05-21 | 2001-07-17 | Nordstrom Valves, Inc. | Valve with rotatable valve member and method for forming same |
US6241654B1 (en) | 1999-07-07 | 2001-06-05 | Acorn Cardiovasculr, Inc. | Cardiac reinforcement devices and methods |
US6179791B1 (en) | 1999-09-21 | 2001-01-30 | Acorn Cardiovascular, Inc. | Device for heart measurement |
US6193648B1 (en) | 1999-09-21 | 2001-02-27 | Acorn Cardiovascular, Inc. | Cardiac constraint with draw string tensioning |
US6174279B1 (en) | 1999-09-21 | 2001-01-16 | Acorn Cardiovascular, Inc. | Cardiac constraint with tension indicator |
US6797002B2 (en) | 2000-02-02 | 2004-09-28 | Paul A. Spence | Heart valve repair apparatus and methods |
JP2001317938A (en) * | 2000-05-01 | 2001-11-16 | Asahi Optical Co Ltd | Surveying machine with light wave range finder |
US6723038B1 (en) | 2000-10-06 | 2004-04-20 | Myocor, Inc. | Methods and devices for improving mitral valve function |
US7297150B2 (en) | 2002-08-29 | 2007-11-20 | Mitralsolutions, Inc. | Implantable devices for controlling the internal circumference of an anatomic orifice or lumen |
US7404824B1 (en) | 2002-11-15 | 2008-07-29 | Advanced Cardiovascular Systems, Inc. | Valve aptation assist device |
EP1943982A1 (en) | 2004-02-23 | 2008-07-16 | International Heart Institute of Montana Foundation | Papilloplasty band and sizing device |
US8206439B2 (en) | 2004-02-23 | 2012-06-26 | International Heart Institute Of Montana Foundation | Internal prosthesis for reconstruction of cardiac geometry |
WO2007100408A2 (en) | 2005-12-15 | 2007-09-07 | Georgia Tech Research Corporation | Papillary muscle position control devices, systems & methods |
DE602007012691D1 (en) | 2006-05-15 | 2011-04-07 | Edwards Lifesciences Ag | SYSTEM FOR CHANGING THE GEOMETRY OF THE HEART |
-
1998
- 1998-07-29 US US09/124,321 patent/US6077214A/en not_active Expired - Lifetime
-
1999
- 1999-07-27 AU AU52309/99A patent/AU5230999A/en not_active Abandoned
- 1999-07-27 EP EP99937484A patent/EP1143859A2/en not_active Withdrawn
- 1999-07-27 WO PCT/US1999/016875 patent/WO2000006027A2/en active Application Filing
-
2000
- 2000-03-09 US US09/522,068 patent/US6264602B1/en not_active Expired - Lifetime
-
2001
- 2001-04-27 US US09/843,078 patent/US6402680B2/en not_active Expired - Lifetime
-
2002
- 2002-05-06 US US10/138,520 patent/US6908424B2/en not_active Expired - Lifetime
-
2005
- 2005-02-17 US US11/060,380 patent/US8439817B2/en not_active Expired - Lifetime
Cited By (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9005109B2 (en) | 2000-05-10 | 2015-04-14 | Mardil, Inc. | Cardiac disease treatment and device |
US9149602B2 (en) | 2005-04-22 | 2015-10-06 | Advanced Cardiovascular Systems, Inc. | Dual needle delivery system |
US9370425B2 (en) | 2012-10-12 | 2016-06-21 | Mardil, Inc. | Cardiac treatment system and method |
US9421101B2 (en) | 2012-10-12 | 2016-08-23 | Mardil, Inc. | Cardiac treatment system |
US9421102B2 (en) | 2012-10-12 | 2016-08-23 | Mardil, Inc. | Cardiac treatment system and method |
Also Published As
Publication number | Publication date |
---|---|
EP1143859A2 (en) | 2001-10-17 |
US6264602B1 (en) | 2001-07-24 |
US20010016675A1 (en) | 2001-08-23 |
US20050143620A1 (en) | 2005-06-30 |
US20020173694A1 (en) | 2002-11-21 |
US6402680B2 (en) | 2002-06-11 |
US8439817B2 (en) | 2013-05-14 |
US6908424B2 (en) | 2005-06-21 |
WO2000006027A2 (en) | 2000-02-10 |
WO2000006027A3 (en) | 2001-11-08 |
AU5230999A (en) | 2000-02-21 |
US6077214A (en) | 2000-06-20 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US6077214A (en) | Stress reduction apparatus and method | |
US7883539B2 (en) | Heart wall tension reduction apparatus and method | |
US6332863B1 (en) | Heart wall tension reduction kit | |
EP1854414B1 (en) | Heart wall tension reduction apparatus and method | |
US6808488B2 (en) | External stress reduction device and method | |
US20040133062A1 (en) | Minimally invasive cardiac force transfer structures | |
CA2405382C (en) | Endoventricular device for the treatment and correction of cardiomyopathies | |
US20030045771A1 (en) | Heart wall tension reduction devices and methods |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AK | Designated states |
Kind code of ref document: A2 Designated state(s): AE AL AM AT AU AZ BA BB BG BR BY CA CH CN CU CZ DE DK EE ES FI GB GD GE GH GM HR HU ID IL IN IS JP KE KG KP KR KZ LC LK LR LS LT LU LV MD MG MK MN MW MX NO NZ PL PT RO RU SD SE SG SI SK SL TJ TM TR TT UA UG US UZ VN YU ZA ZW |
|
AL | Designated countries for regional patents |
Kind code of ref document: A2 Designated state(s): GH GM KE LS MW SD SL SZ UG ZW AM AZ BY KG KZ MD RU TJ TM AT BE CH CY DE DK ES FI FR GB GR IE IT LU MC NL PT SE BF BJ CF CG CI CM GA GN GW ML MR NE SN TD TG |
|
121 | Ep: the epo has been informed by wipo that ep was designated in this application | ||
DFPE | Request for preliminary examination filed prior to expiration of 19th month from priority date (pct application filed before 20040101) | ||
AK | Designated states |
Kind code of ref document: C2 Designated state(s): AE AL AM AT AU AZ BA BB BG BR BY CA CH CN CU CZ DE DK EE ES FI GB GD GE GH GM HR HU ID IL IN IS JP KE KG KP KR KZ LC LK LR LS LT LU LV MD MG MK MN MW MX NO NZ PL PT RO RU SD SE SG SI SK SL TJ TM TR TT UA UG US UZ VN YU ZA ZW |
|
AL | Designated countries for regional patents |
Kind code of ref document: C2 Designated state(s): GH GM KE LS MW SD SL SZ UG ZW AM AZ BY KG KZ MD RU TJ TM AT BE CH CY DE DK ES FI FR GB GR IE IT LU MC NL PT SE BF BJ CF CG CI CM GA GN GW ML MR NE SN TD TG |
|
COP | Corrected version of pamphlet |
Free format text: PAGES 1/12-12/12, DRAWINGS, REPLACED BY NEW PAGES 1/11-11/11; DUE TO LATE TRANSMITTAL BY THE RECEIVING OFFICE |
|
WWE | Wipo information: entry into national phase |
Ref document number: 1999937484 Country of ref document: EP |
|
REG | Reference to national code |
Ref country code: DE Ref legal event code: 8642 |
|
WWP | Wipo information: published in national office |
Ref document number: 1999937484 Country of ref document: EP |
|
AK | Designated states |
Kind code of ref document: A3 Designated state(s): AE AL AM AT AU AZ BA BB BG BR BY CA CH CN CU CZ DE DK EE ES FI GB GD GE GH GM HR HU ID IL IN IS JP KE KG KP KR KZ LC LK LR LS LT LU LV MD MG MK MN MW MX NO NZ PL PT RO RU SD SE SG SI SK SL TJ TM TR TT UA UG US UZ VN YU ZA ZW |
|
AL | Designated countries for regional patents |
Kind code of ref document: A3 Designated state(s): GH GM KE LS MW SD SL SZ UG ZW AM AZ BY KG KZ MD RU TJ TM AT BE CH CY DE DK ES FI FR GB GR IE IT LU MC NL PT SE BF BJ CF CG CI CM GA GN GW ML MR NE SN TD TG |