CA2275766C - Heart wall tension reduction apparatus and method - Google Patents
Heart wall tension reduction apparatus and method Download PDFInfo
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- CA2275766C CA2275766C CA002275766A CA2275766A CA2275766C CA 2275766 C CA2275766 C CA 2275766C CA 002275766 A CA002275766 A CA 002275766A CA 2275766 A CA2275766 A CA 2275766A CA 2275766 C CA2275766 C CA 2275766C
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- 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
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- 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
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- 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
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- A61B2017/0496—Surgical instruments, devices or methods, e.g. tourniquets for suturing wounds; Holders or packages for needles or suture materials for tensioning sutures
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Abstract
This invention is an apparatus for treatment of a failing heart by reducing the wall tension therein, In one embodiment, the apparatus includes a tension member (18) for drawing at least two walls of a heart charnber toward each other. Methods for placing the apparatus on the heart are also provided.
Description
HEART WALL TENSION REDUCTION APPARATUS AND METHOD
Field of the Invention The present invention pertains to the field of apparatus for treatment of a failing heart. In particular, the apparatus of the present invention is directed toward reducing the wall stress in the failing heart.
Background of the Invention The syndrome of heart failure is a common course for the progression of many forms of heart disease. Heart failure may be considered to be the condition in which an abnormality of cardiac function is responsible for the inability of the heart to pump blood at a rate commensurate with the requirements of the metabolizing tissues, or can do so only at an abnormally elevated filling pressure. There are many specific disease processes that can lead to heart failure with a resulting difference in pathophysiology of the failing heart, such as the dilatation of the left ventricular chamber. Etiologies that can lead to this form of failure include 21439187.2 idiopathic cardiomyopathy, viral cardiomyopathy, and ischemic cardiomyopathy.
The process of ventricular dilatation is generally the result of chronic volume overload or specific damage to the myocardium. In a normal heart that is exposed to long term increased cardiac output requirements, for example, that of an athlete, there is an adaptive process of slight ventricular dilation and muscle myocyte hypertrophy. In this way, the heart fully compensates for the increased cardiac output requirements. With damage to the myocardium or chronic volume overload, however, 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. In a normal heart, the adaptation of muscle hypertrophy (thickening) and ventricular dilatation maintain a fairly constant wall tension for systolic contraction. However, in a failing heart, 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
Field of the Invention The present invention pertains to the field of apparatus for treatment of a failing heart. In particular, the apparatus of the present invention is directed toward reducing the wall stress in the failing heart.
Background of the Invention The syndrome of heart failure is a common course for the progression of many forms of heart disease. Heart failure may be considered to be the condition in which an abnormality of cardiac function is responsible for the inability of the heart to pump blood at a rate commensurate with the requirements of the metabolizing tissues, or can do so only at an abnormally elevated filling pressure. There are many specific disease processes that can lead to heart failure with a resulting difference in pathophysiology of the failing heart, such as the dilatation of the left ventricular chamber. Etiologies that can lead to this form of failure include 21439187.2 idiopathic cardiomyopathy, viral cardiomyopathy, and ischemic cardiomyopathy.
The process of ventricular dilatation is generally the result of chronic volume overload or specific damage to the myocardium. In a normal heart that is exposed to long term increased cardiac output requirements, for example, that of an athlete, there is an adaptive process of slight ventricular dilation and muscle myocyte hypertrophy. In this way, the heart fully compensates for the increased cardiac output requirements. With damage to the myocardium or chronic volume overload, however, 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. In a normal heart, the adaptation of muscle hypertrophy (thickening) and ventricular dilatation maintain a fairly constant wall tension for systolic contraction. However, in a failing heart, 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
-2-further muscle damage. The increase in wall stress is also true for diastolic filling. Additionally, because of the lack of cardiac output, there is generally a rise in ventricular filling pressure from several physiologic mechanisms. Moreover, in diastole there is both a diameter increase and a pressure increase over normal, both contributing to higher wall stress levels. The increase in diastolic wall stress is felt to be the primary contributor to ongoing dilatation of the chamber.
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.
With respect to pharmacological treatments, diuretics have been used to reduce the workload of the heart by reducing blood volume and preload. Clinically, preload is defined in several ways including left ventricular end diastolic pressure (LVEDP?, or left ventricular end diastolic volume (LVEDV).
Physiologically, 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
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.
With respect to pharmacological treatments, diuretics have been used to reduce the workload of the heart by reducing blood volume and preload. Clinically, preload is defined in several ways including left ventricular end diastolic pressure (LVEDP?, or left ventricular end diastolic volume (LVEDV).
Physiologically, 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
-3-WO 98/29041 PCTlUS97/24116 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 like digoxin are cardiac glycosides and function to increase cardiac output by increasing the force and speed of cardiac muscle contraction. These drug therapies offer some beneficial effects but do not stop the progression of the disease.
Assist devices include mechanical pumps and electrical stimulators. 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. Electrical stimulation such as bi-ventricular pacing have been investigated for the treatment of patients with dilated cardiomyopathy.
There are at least three surgical procedures for treatment of heart failure: 1) heart transplant; 2) dynamic cardiomyoplasty; and 3) the Batista partial left ventriculectomy. Heart transplantation has serious limitations including restricted availability of organs and adverse effects of immunosuppressive therapies required following heart transplantation.
Cardiomyoplasty includes wrapping the heart with skeletal
Assist devices include mechanical pumps and electrical stimulators. 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. Electrical stimulation such as bi-ventricular pacing have been investigated for the treatment of patients with dilated cardiomyopathy.
There are at least three surgical procedures for treatment of heart failure: 1) heart transplant; 2) dynamic cardiomyoplasty; and 3) the Batista partial left ventriculectomy. Heart transplantation has serious limitations including restricted availability of organs and adverse effects of immunosuppressive therapies required following heart transplantation.
Cardiomyoplasty includes wrapping the heart with skeletal
-4-muscle and electrically stimulating the muscle to contract synchronously with the heart in order to help the pumping function of the heart. The Batista partial left ventriculectomy includes surgically remodeling the left ventricle by removing a segment of the muscular wall. This procedure reduces the diameter of the dilated heart, which in turn reduces the loading of the heart.
However, this extremely invasive' procedure reduces muscle mass of the heart.
Summary of the Invention The present invention pertains to a non-pharmacological, passive apparatus and method for the treatment of a failing heart. The device is configured to reduce the tension in the heart wall. It is believed to reverse, stop or slow the die;ease process of a failing heart as it reduces the energy consumption of the failing heart, decreases isovolumetric: contraction, increases sarcomere shortening during contraction and increases isotonic shortening which in turn increases stroke volume. The device reduces wall tension during diastole and systole.
In one embodiment, the apparatus includes a tension member for drawing at least two walls of the heart - 25 chamber toward each other to reduce the radius or area of the heart chamber in at least o:ne cross sectianal plane.
_5_ The tension member has anchoring members disposed at opposite ends for engagement with the heart or chamber wall.
In another embodiment, the apparatus includes a compression member for drawing at least two walls of a heart chamber toward each other. In one embodiment, the compression member includes a balloon. In another embodiment of the apparatus, a frame is provided for supporting the compression member.
Yet another embodiment of the invention includes a clamp having two ends biased toward one another for drawing at least two walls of a heart chamber toward each other. The clamp includes at least two ends having atraumatic anchoring member disposed thereon for engagement with the heart or chamber wall.
In yet another embodiment, a heart wall tension reduction apparatus is provided which includes a first tension member having two oppositely disposed ends and first and second elongate anchor members. A second tension member can be provided. One of the elongate anchors may be substituted for by two smaller anchors.
In an alternate embodiment of the heart wall tension reduction apparatus, an elongate compression member can be provided. First and second elongate lever members preferably extend from opposite ends of the compression member. A tension member extends between the first and second lever members.
The compression member of the above embodiment can be disposed exterior to, or internally of the heart. The tension member extends through the chamber or chambers to bias the lever members toward the heart.
In yet another embodiment of a heart wall tension reduction apparatus in accordance with the present invention, a rigid elongate frame member is provided.
The frame member can extend through one or more chambers of the heart. One or more cantilever members can be disposed at opposite ends of t=he frame member. Each cantilever member includes at 7_east one atraumatic pad disposed thereon. The atraumatic pads disposed at opposite ends of the frame member can be biased toward each other to compress the heart chamber.
One method of placing a heart wall tension apparatus or splint on a human heart includes the step of extending a hollow needle through at least one chamber of the heart such that each end of the needle is external to the chamber. A flexible leader is connected to a first end of a tension member. A second end of the tension member is connected to an atraumatic pad. The leader is advanced through the needle from one end of the needle to the other. The leader is furi~her advanced until the second end of the tension member is proximate the heart and the first end of the tension member is external to the heart. A second atraumatic pad is connected to the first end of the tension member such that the first and second atraumatic pads engage the heart.
An alternate method of placing the heart wall tension reduction apparatus on the heart includes the step of extending a guide member through at least one chamber of the heart such that each end of the guide member is external to the chamber. A tension member for use in this method has at least one lumen extending through at least a portion of the member. The guide member is placed in the lumen. The tension member is advanced over the guide member such that a first end of the tension member is disposed to one side of and external to the heart and a second end of the tension member is disposed to an opposite side of and external to the heart. A first atraumatic pad is connected to one end of the tension member and a second atraumatic pad is connected to the opposite end of the tension member.
Yet another method of placing a heart wall tension apparatus on a heart includes the step of extending a needle having a flexible tension member releasably connected thereto through at least one chamber of the heart such that opposite ends of the tension member are external to the chamber and exposed on opposite sides of the chamber. The needle is removed from the tension _g_ member. Then first and second atraumatic pads are connected to the tension member at opposite ends of the tension member.
Brief Description of the Drawinas Figure 1 is a transverse cross-section of the left and right ventricles of a human heart showing the placement of a splint in accordance with the present invention;
l0 Figure 2 is a transverse cross-section of the left and right ventricles of a human heart showing the placement of a balloon device in accordance with the present invention;
Figure 3 is a transverse cross-section of the left and right ventricles of a hi.zman heart showing the placement of an external compression frame structure in accordance with the present invention;
Figure 4 is a transverse cross-section of the left and right ventricles of a human heart showing a clamp in accordance with the present invention;
Figure 5 is a transverse cross-section of the left and right ventricles of a human heart showing a three tension member version of the splint of Figure 1;
Figure 6 is a transverse cross-section of the left and right ventricles of a human heart showing a four tension member version of the splint shown in Figure 1;
Figure 7 is a vertical cross-sectional view of the left ventricle of a human heart showing an alternate version of the splint in accordance with the present invention;
Figure 8 is an end of the splint shown in Figure 7;
Figure 9 is a vertical cross-sectional view of a chamber of a human heart showing another alternative embodiment of the splint in accordance with the present invention;
Figure 10 is a vertical cross-section of a chamber of a human heart showing another alternative configuration of splints in accordance with the present invention;
Figure 11 is a vertical cross-sectional view of a chamber of a human heart showing another embodiment of a splint in accordance with the present invention;
Figure 12 is a vertical cross-sectional view of a chamber of a human heart showing another embodiment of the splint in accordance with the present invention;
Figure 13 is a vertical cross-sectional view of a chamber of a human heart showing a compression member version of the splint -in accordance with the present invention;
Figure 14 is a vertical cross-sectional view of a chamber of a human heart showing another version of the splint shown in Figure 13;
Figure 15 is a vertical cross-sectional view of a chamber of a human heart showing a frame member version of the splint in accordance with the present invention;
Figure 16 is an end view of: the splint of Figure 15;
Figure 17 is a vertical cross-section of the left ventricle and atrium, the left ventricle having scar tissue;
Figure 18 is a vertical cross-section of the heart of Figure 7 showing the splint of Figure 1 drawing the scar tissue toward the opposite wall of the left ventricle;
Figure 19 is a vertical cross-section of the left ventricle and atrium of a human heart showing a version of the splint of Figure 1 having an elongate anchor bar;
Figure 20 is a side view of an undeployed hinged anchor member;
Figure 21 is a side view of a deployed hinged anchor member of Figure 10;
Figure 22 is a cross-sectional view of an captured ball anchor member;
Figure 23 is a perspective view of a cross bar anchor member;
Figure 24 is a vertical cross-sectional view of a chamber of a human heart showing a needle used for placement of splint in accordance with the present invention;
Figure 25 is a view of the heart and needle of Figure 24 showing a tension member being placed in the heart;
Figure 26 is a view of the heart shown in Figure 24 wherein oppositely disposed anchor pads are being joined by a tension member;
Figure 27 is a view of the heart of Figure 24, wherein two oppositely disposed anchor pads have been joined by two tension members;
Figure 28 is a view of a tension member having a lumen extending therethrough;
Figure 29 is a view of a tension member having lumens extending therethrough;
Figure 30 is a vertical cross-sectional view of a chamber of the heart and two pads, and a needle extending therethrough;
Figure 31 is a vertical cross-sectional view of a chamber of the heart showing a guidewire extending therethrough;
Figure 32 is a view of the heart of Figure 31, and two pads, and a guidewire extending therethrough;
Figure 33 is a vertical cross-sectional view of a chamber of the heart showing a needle connected to a tension member being inserted into the chamber;
Figure 34 is a vertical cross-sectional view of a chamber of a heart showing two anchors connected by a tension member;
Figure 35 is a vertical cross-sectional view of a chamber of the heart, showing a band surrounding the heart;
Figure 36 is a idealized cylindrical model of a left ventricle of a human heart;
Figure 37 is a splinted model of the left ventricle of Figure 14;
Figure 38 is a transverse cross-sectional view of Figure 15 showing various modeling parameters;
Figure 39 is a transver:~e cross-section of the splinted left ventricle of Figure 15 showing a hypothetical force distribution; and Figure 40 is a second transverse cross-sectional view of the model left ventricle of Figure 15 showing a hypothetical force distribution.
Detailed Description of the Invention Referring now to the drawings wherein like reference numerals refer to like elements throughout the several views, Figure 1 shows a transverse cross-section of a left ventricle 10 and a right ventricle 12 of a human heart 14. Extending through l:he left ventricle is a splint 16 including a tension member 18 and oppositely disposed anchors 20. Splint 16 as shown in Figure 1 has been positioned to draw opposite walls of left ventricle toward each other to reduce the "radius" of the left ventricular cross-section or the cross-sectional area
However, this extremely invasive' procedure reduces muscle mass of the heart.
Summary of the Invention The present invention pertains to a non-pharmacological, passive apparatus and method for the treatment of a failing heart. The device is configured to reduce the tension in the heart wall. It is believed to reverse, stop or slow the die;ease process of a failing heart as it reduces the energy consumption of the failing heart, decreases isovolumetric: contraction, increases sarcomere shortening during contraction and increases isotonic shortening which in turn increases stroke volume. The device reduces wall tension during diastole and systole.
In one embodiment, the apparatus includes a tension member for drawing at least two walls of the heart - 25 chamber toward each other to reduce the radius or area of the heart chamber in at least o:ne cross sectianal plane.
_5_ The tension member has anchoring members disposed at opposite ends for engagement with the heart or chamber wall.
In another embodiment, the apparatus includes a compression member for drawing at least two walls of a heart chamber toward each other. In one embodiment, the compression member includes a balloon. In another embodiment of the apparatus, a frame is provided for supporting the compression member.
Yet another embodiment of the invention includes a clamp having two ends biased toward one another for drawing at least two walls of a heart chamber toward each other. The clamp includes at least two ends having atraumatic anchoring member disposed thereon for engagement with the heart or chamber wall.
In yet another embodiment, a heart wall tension reduction apparatus is provided which includes a first tension member having two oppositely disposed ends and first and second elongate anchor members. A second tension member can be provided. One of the elongate anchors may be substituted for by two smaller anchors.
In an alternate embodiment of the heart wall tension reduction apparatus, an elongate compression member can be provided. First and second elongate lever members preferably extend from opposite ends of the compression member. A tension member extends between the first and second lever members.
The compression member of the above embodiment can be disposed exterior to, or internally of the heart. The tension member extends through the chamber or chambers to bias the lever members toward the heart.
In yet another embodiment of a heart wall tension reduction apparatus in accordance with the present invention, a rigid elongate frame member is provided.
The frame member can extend through one or more chambers of the heart. One or more cantilever members can be disposed at opposite ends of t=he frame member. Each cantilever member includes at 7_east one atraumatic pad disposed thereon. The atraumatic pads disposed at opposite ends of the frame member can be biased toward each other to compress the heart chamber.
One method of placing a heart wall tension apparatus or splint on a human heart includes the step of extending a hollow needle through at least one chamber of the heart such that each end of the needle is external to the chamber. A flexible leader is connected to a first end of a tension member. A second end of the tension member is connected to an atraumatic pad. The leader is advanced through the needle from one end of the needle to the other. The leader is furi~her advanced until the second end of the tension member is proximate the heart and the first end of the tension member is external to the heart. A second atraumatic pad is connected to the first end of the tension member such that the first and second atraumatic pads engage the heart.
An alternate method of placing the heart wall tension reduction apparatus on the heart includes the step of extending a guide member through at least one chamber of the heart such that each end of the guide member is external to the chamber. A tension member for use in this method has at least one lumen extending through at least a portion of the member. The guide member is placed in the lumen. The tension member is advanced over the guide member such that a first end of the tension member is disposed to one side of and external to the heart and a second end of the tension member is disposed to an opposite side of and external to the heart. A first atraumatic pad is connected to one end of the tension member and a second atraumatic pad is connected to the opposite end of the tension member.
Yet another method of placing a heart wall tension apparatus on a heart includes the step of extending a needle having a flexible tension member releasably connected thereto through at least one chamber of the heart such that opposite ends of the tension member are external to the chamber and exposed on opposite sides of the chamber. The needle is removed from the tension _g_ member. Then first and second atraumatic pads are connected to the tension member at opposite ends of the tension member.
Brief Description of the Drawinas Figure 1 is a transverse cross-section of the left and right ventricles of a human heart showing the placement of a splint in accordance with the present invention;
l0 Figure 2 is a transverse cross-section of the left and right ventricles of a human heart showing the placement of a balloon device in accordance with the present invention;
Figure 3 is a transverse cross-section of the left and right ventricles of a hi.zman heart showing the placement of an external compression frame structure in accordance with the present invention;
Figure 4 is a transverse cross-section of the left and right ventricles of a human heart showing a clamp in accordance with the present invention;
Figure 5 is a transverse cross-section of the left and right ventricles of a human heart showing a three tension member version of the splint of Figure 1;
Figure 6 is a transverse cross-section of the left and right ventricles of a human heart showing a four tension member version of the splint shown in Figure 1;
Figure 7 is a vertical cross-sectional view of the left ventricle of a human heart showing an alternate version of the splint in accordance with the present invention;
Figure 8 is an end of the splint shown in Figure 7;
Figure 9 is a vertical cross-sectional view of a chamber of a human heart showing another alternative embodiment of the splint in accordance with the present invention;
Figure 10 is a vertical cross-section of a chamber of a human heart showing another alternative configuration of splints in accordance with the present invention;
Figure 11 is a vertical cross-sectional view of a chamber of a human heart showing another embodiment of a splint in accordance with the present invention;
Figure 12 is a vertical cross-sectional view of a chamber of a human heart showing another embodiment of the splint in accordance with the present invention;
Figure 13 is a vertical cross-sectional view of a chamber of a human heart showing a compression member version of the splint -in accordance with the present invention;
Figure 14 is a vertical cross-sectional view of a chamber of a human heart showing another version of the splint shown in Figure 13;
Figure 15 is a vertical cross-sectional view of a chamber of a human heart showing a frame member version of the splint in accordance with the present invention;
Figure 16 is an end view of: the splint of Figure 15;
Figure 17 is a vertical cross-section of the left ventricle and atrium, the left ventricle having scar tissue;
Figure 18 is a vertical cross-section of the heart of Figure 7 showing the splint of Figure 1 drawing the scar tissue toward the opposite wall of the left ventricle;
Figure 19 is a vertical cross-section of the left ventricle and atrium of a human heart showing a version of the splint of Figure 1 having an elongate anchor bar;
Figure 20 is a side view of an undeployed hinged anchor member;
Figure 21 is a side view of a deployed hinged anchor member of Figure 10;
Figure 22 is a cross-sectional view of an captured ball anchor member;
Figure 23 is a perspective view of a cross bar anchor member;
Figure 24 is a vertical cross-sectional view of a chamber of a human heart showing a needle used for placement of splint in accordance with the present invention;
Figure 25 is a view of the heart and needle of Figure 24 showing a tension member being placed in the heart;
Figure 26 is a view of the heart shown in Figure 24 wherein oppositely disposed anchor pads are being joined by a tension member;
Figure 27 is a view of the heart of Figure 24, wherein two oppositely disposed anchor pads have been joined by two tension members;
Figure 28 is a view of a tension member having a lumen extending therethrough;
Figure 29 is a view of a tension member having lumens extending therethrough;
Figure 30 is a vertical cross-sectional view of a chamber of the heart and two pads, and a needle extending therethrough;
Figure 31 is a vertical cross-sectional view of a chamber of the heart showing a guidewire extending therethrough;
Figure 32 is a view of the heart of Figure 31, and two pads, and a guidewire extending therethrough;
Figure 33 is a vertical cross-sectional view of a chamber of the heart showing a needle connected to a tension member being inserted into the chamber;
Figure 34 is a vertical cross-sectional view of a chamber of a heart showing two anchors connected by a tension member;
Figure 35 is a vertical cross-sectional view of a chamber of the heart, showing a band surrounding the heart;
Figure 36 is a idealized cylindrical model of a left ventricle of a human heart;
Figure 37 is a splinted model of the left ventricle of Figure 14;
Figure 38 is a transverse cross-sectional view of Figure 15 showing various modeling parameters;
Figure 39 is a transver:~e cross-section of the splinted left ventricle of Figure 15 showing a hypothetical force distribution; and Figure 40 is a second transverse cross-sectional view of the model left ventricle of Figure 15 showing a hypothetical force distribution.
Detailed Description of the Invention Referring now to the drawings wherein like reference numerals refer to like elements throughout the several views, Figure 1 shows a transverse cross-section of a left ventricle 10 and a right ventricle 12 of a human heart 14. Extending through l:he left ventricle is a splint 16 including a tension member 18 and oppositely disposed anchors 20. Splint 16 as shown in Figure 1 has been positioned to draw opposite walls of left ventricle toward each other to reduce the "radius" of the left ventricular cross-section or the cross-sectional area
5 thereof to reduce left ventricular wall stresses. It should be understood that although the splint 16 and the alternative devices disclosed herein are described in relation to the left ventricle of a human heart, these devices could also be used to reduce the radius or cross-10 sectional area of the other chambers of a human heart in transverse or vertical directions, or at an angle between the transverse and vertical.
Figure 2 discloses an alternate embodiment of the present invention, wherein a balloon 200 is deployed adjacent the left ventricle. The size and degree of inflation of the balloon can be varied to reduce the radius or cross-sectional area of left ventricle 10 of heart 14 .
Figure 3 shows yet another alternative embodiment of the present invention deployed with respect to left ventricle 10 of human heart 14. Here a compression frame structure 300 is engaged with heart 14 at atraumatic anchor pads 310. A compression member 312 having an atraumatic surface 314 presses against a wall of left ventricle 10 to reduce the radius or cross-sectional area thereof .
Figure 4 is a transverse cross-sectional view of human heart 14 showing yet another embodiment of the present invention. In this case a clamp 400 having atraumatic anchor pads 410 biased toward each other is shown disposed on a wall of left ventricle 10. Here the radius or cross-sectional area of left ventricle 10 is reduced by clamping off the portion of the wall between pads 410. Pads 410 can be biased toward each other and/or can be held together by a locking device.
Each of the various embodiments of the present invention disclosed in Figures 1-4 can be made from materials which can remain implanted in the human body indefinitely. Such biocompati.ble materials are well known to those skilled in the art of clinical medical devices.
Figure 5 shows an alternate: embodiment of the splint of Figure 1 referred to in Figure 5 by the numeral 116.
The embodiment 116 shown in :E'igure 5 includes three tension members 118 as opposed to a single tension member 18 as shown in Figure 1. Figure 6 shows yet another embodiment of the splint 216 haring four tension members 218. It is anticipated that in some patients, the disease process of the failing heart may be so advanced that three, four or more tension members may be desirable to reduce the heart wall stresses more substantially than possible with a single tension member as shown in Figure 1.
Figure 7 is a partial vertical cross-section of human heart 14 showing left ventricle 10. In Figure 7, another splint embodiment 316 is shown having a tension member 318 extending through left ventricle 10. On opposite ends of tension member 318 are disposed elongate anchors or pads 320. Figure 8 is an end view of tension member 318 showing elongate anchor 320.
Figure 9 shows another embodiment of a splint 416 disposed in a partial vertical cross-section of human heart 14. Splint 416 includes two elongate anchors or pads 420 similar to those shown in Figures 7 and 8. In Figure 9, however, two tension members 418 extend through left ventricle 10 to interconnect anchors 420 on opposite sides of heart 14.
Figure 10 is a vertical cross section of heart 14 showing left ventricle 10. In this case, two splints 16 are disposed through left ventricle 10 and vertically spaced from each other to resemble the configuration of Figure 9.
Figure 11 is a vertical cross sectional view of the left ventricle of heart 14. Two alternate embodiment splints 516 are shown extending through left ventricle 10. Each splint 516 includes two tension members 518 interconnecting two anchors or pads 520.
Figure 12 is yet another vertical cross sectional view of left ventricle 10 of heart 14. An alternate embodiment 616 of the splint ie; shown extending through left ventricle 10. Splint 6:16 includes an elongate anchor pad 620 and two shorter anchors or pads 621.
Splint 616 includes two tension members 618. Each tension member 618 extends between anchors 620 and respective anchors 621.
Figure 13 is a vertical cross sectional view of left ventricle l0 of heart 14. A sp7_int 50 is shown disposed on heart 14. Splint 50 include: a compression member 52 shown extending through left ventricle 10. Opposite ends of compression member 52 are disposed exterior to left ventricle 10. Lever members 54 extend from each end of compression member 52 upwardly along the exterior surface of ventricle 10. A tension member 56 extends between lever members 54 to bias lever mfsmbers 54 toward heart 14 to compress chamber 10. Compression member 52 should be substantially rigid, but lever members 54 and to some degree compression member 52 should be flexible enough to allow tension member 56 to bias lever members 54 toward heart 14. Alternately, lever members 54 could be hinged to compression member 52 such th~~t lever members 54 could pivot about the hinge when biased toward heart 14 by tension member 56.
WO 98!29041 PCT/L1S97/24116 Figure 14 shows an alternate embodiment 156 of the splint shown in Figure 13. In this case lever members 154 are longer than members 54 as compression member 152 of splint 150 has been disposed to the exterior of left ventricle 10.
Figure 15 is a vertical cross sectional view of left ventricle 10 of heart 14. An alternate embodiment 250 of the splint is shown on heart 14. A preferably relatively rigid frame member 255 extends through ventricle 10.
l0 Disposed on opposite ends of frame 250 are cantilever member 254. Disposed on cantilever members 254 are atraumatic pads 258. Cantilever members 254 can be positioned along frame member 256 such that atraumatic pads 258 press against heart 14 to compress chamber 10.
Figure 16 is an end view of frame member 256 showing cantilever members 254 and pads 258.
It should be understood that each of the embodiments described above should be formed from suitable biocompatible materials known to those skilled in the art. The tension members can be formed from flexible or relatively more rigid material. The compression members and frame member should be formed from generally rigid material which may flex under load, but generally hold its shape.
Figure 17 is a partial vertical cross-section of human heart 14 showing left ventricle 10 and left atrium 22. As shown in Figure 7, heart: 14 includes a region of scar tissue 24 associated with an aneurysm or ischemia.
As shown in Figure 7, the scar tissue 24 increases the radius or cross-sectional area of left ventricle 10 in the region affected by the scar tissue. Such an increase in the radius or cross-sectional area of the left ventricle will result in greater wall stresses on the walls of the left ventricle.
Figure 18 is a vertical crc>ss-sectional view of the heart 14 as shown in Figure 7, wherein a splint 16 has been placed to draw the scar tis:~ue 24 toward an opposite wall of left ventricle 10. As a consequence of placing splint 16, the radius or cross-se=_ctional area of the left ventricle affected by the scar tissue 24 is reduced. The reduction of this radius or cross-sectional area results in reduction in the wall stress in the left ventricular wall and thus improves heart pumping efficiency.
Figure 19 is a vertical cro:~s-sectional view of left ventricle 10 and left atrium 22 of heart 14 in which a splint 16 has been placed. As shown in Figure 9, splint 16 includes an alternative anchor 26. The anchor 26 is preferably an elongate member having a length as shown in Figure 9 substantially greater than its width (not shown). Anchor bar 26 might be used to reduce the radius or cross-sectional area of than left ventricle in an instance where there is generalized enlargement of left ventricle 10 such as in idiopathic dilated cardiomyopathy. In such an instance, bar anchor 26 can distribute forces more widely than anchor 20.
Figures 20 and 21 are side views of a hinged anchor 28 which could be substituted for anchors 20 in undeployed and deployed positions respectively. Anchor 28 as shown in Figure 20 includes two legs similar to bar anchor 26. Hinged anchor 28 could include additional legs and the length of those legs could be varied to distribute the force over the surface of the heart wall.
In addition there could be webbing between each of the legs to give anchor 28 an umbrella-like appearance.
Preferably the webbing would be disposed on the surface of the legs which would be in contact with the heart wall.
Figure 22 is a cross-sectional view of a capture ball anchor 30. Capture ball anchor 30 can be used in place of anchor 20. Capture ball anchor 30 includes a disk portion 32 to distribute the force of the anchor on the heart wall, and a recess 34 for receiving a ball 36 affixed to an end of tension member 18. Disk 32 and recess 34 include a side groove which allows tension member 38 to be passed from an outside edge of disk 32 into recess 34. Ball 36 can then be advanced into recess 34 by drawing tension member 18 through an opening 38 in recess 34 opposite disk 32.
Figure 23 is a perspective view of a cross bar anchor 40. The cross bar anchor 40 can be used in place of anchors 20. The anchor 40 preferably includes a disk or pad portion 42 having a cross bar 44 extending over an opening 46 in pad 42. Tension member 18 can be extended through opening 46 and tied to cross bar 42 as shown.
In use, the various embodiments of the present invention are placed in or adj;~cent the human heart to reduce the radius or cross-section area of at least one chamber of the heart. This is done to reduce wall stress or tension in the heart or chamber wall to slow, stop or reverse failure of the heart. 7:n the case of the splint 16 shown in Figure 1, a canula can be used to pierce both walls of the heart and one end of the splint can be advanced through the canula from one side of the heart to the opposite side where an anchor can be affixed or deployed. Likewise, an anchor i.s affixed or deployed at the opposite end of splint 16.
Figure 24 is a vertical cross-sectional view of a chamber 10 of a heart 14. A needle 60 having a stylet inserted therethrough is inserted through chamber 10.
Figure 25 shows needle 60 disposed in heart 40 as shown in Figure 24. In Figure 25, stylet 62 has been removed.
A tension member 64 having a flexible leader 66 attached to one end of tension member 64, is threaded through needle 60 and an anchor 68.
WO 98129041 PCT/iJS97/24116 As shown in Figure 25, tension member 64 includes a generally elongate cylindrical shaft 70 having two generally cylindrical ends 72. Ends 72 preferably have a greater diameter than shaft 70. Also shown in Figure 25 is a perspective view of anchor 68 showing an opening 73 extending through anchor 68. Opening 73 includes a first cylindrically shaped opening 74 extending entirely through anchor 68. The diameter of opening 74 is preferably slightly greater than the diameter of end 72 of tension member 64. A groove 76 having a width preferably slightly greater than that of shaft 70 of tension member 64 extends from opening 74 to a generally cylindrical opening 78. Generally cylindrical opening 78 has a diameter approximately equal to end 72. Unlike opening 74, however, opening 78 includes a reduced base opening 80 which has a width approximately equal to that of groove 76. The width of the opening 80 is also less than the diameter of end 72 of tension member 64.
It can be appreciated that tension member 64 can be advanced through opening 74 until shaft 70 is disposed therein. Shaft 70 can be then slid transversely through groove 76. Tension member 64 can then be advanced further through opening 73 until end portion 72 enters opening 78 and seats against base 80.
Figure 26 shows the view of heart 14 shown in Figure 25. Needle 60 has been removed from heart 14. Tension member 64 has been advanced into chamber 10 and anchor 68 connected thereto is engaging the heart wall. Leader 66 has been advanced through yet another anchor 68 disposed on the opposite side of heart 7_4.
Figure 27 is a view of heart 14 of Figure 26. Two tension member 64 have been advanced through chamber 10.
Each tension member has been seated in respective opening 78 against respective bases 80 to form a splint in a configuration such as that shown in Figure 9.
It can be appreciated that each of the other tension member splints configurations can be placed on the heart in a similar manner. It can <~lso be appreciated that anchors 68 could initially be held against the heart and needle 60 advanced through anchors 68 and chamber 10 prior to extending leader 66 through the needle.
Figure 28 is a perspective view of a tension member 164 in accordance with the present invention. Tension member 164 is similar to tension member 64 described above in that it has an elongate, generally cylindrical shaft 170 and generally cylindrical ends 172. A lumen, however, extends longitudinally through tension member 164 along axis A.
Figure 29 is a perspective view of yet another embodiment of the tension member 264. Tension member 264, is similar to tension member 164, and includes an elongate cylindrical shaft 270 and cylindrical ends 272.
Lumens 282, however, extend through ends 272 aligned along axis B.
Figure 30 is a vertical, cross-sectional view of left ventricle 10 of heart 14. Anchors 68 have been placed on opposite sides of heart 14. A needle 160 extends through the lumen of tension member 164, left ventricle 10 and openings 73 in anchors 68. It can be appreciated that tension member 64 can be advanced through anchors 68 and left ventricle 10 and be seated within openings 78 as described above with respect to tension member 64.
Figure 31 is a vertical, cross-sectional view of left ventricle 10 of heart 14. A needle 60 has been advanced through the wall of left ventricle 10 and a guidewire 162 has been advanced through needle 60.
Figure 32 is the same view of heart 14 as shown in Figure 32. Needle 60, however, has been removed from heart 14 while guidewire 162 remains in position.
Anchors 68 have been placed on guidewire 162, on opposite sides of left ventricle 10. Tension member 264 has been threaded onto guidewire 162 through lumens 282. It can be appreciated that as discussed above with respect to tension member 164 above, tension member 264 can be advanced through left ventricle 10 such that ends 272 of tension member 264 seat in respective openings 78 against base 80.
Figure 33 is a vertical, cross-sectional view of left ventricle 10 of heart 14. In Figure 34, flexible tension member 364 has been connected to a needle 360.
Needle 360 is shown being advanced into left ventricle 10 through a ventricle wall.
Figure 34 is the same view of heart 14 as shown in Figure 33 except that tension member 364 has been advanced entirely through left ventricle 10 and anchors 68. Knots 384 have been tied at the ends of tension member 364 to prevent the ends of tension member 364 from passing through opening 73 of anchors 68.
It can be appreciated that the methods described above to advance the tension members through the ventricles can be repeated to advance the desired number of tension members through the ventricle for a particular configuration. The length of the tension members can be determined based upon the size and condition of the patient's heart. It should also be noted that although the left ventricle has been referred to here for illustrative purposes, that the apparatus and methods of this invention can also be used to splint multiple chambers of a patient's heart. as well as the right ventricle or either atrium.
Figure 35 is a vertical cross-section of left ventricle 10 of heart 14. Disposed about heart 14 is a band 716. Band 716 is shown as being sized relative to the heart such that the heart' s radius or cross-sectional area in a plane parallel to the length of the band is reduced relative to the radius at that location prior to placement of the band on the heart. The length of the heart perpendicular to the band is also increased. The band may be formed from a continuous ribbon of elastomeric material or from other biocompatible materials which are sufficiently strong to provide the desired effect of heart radius reduction and lengthening.
Figure 36 is a view of a cylinder or idealized heart chamber 48 which is used to illustrate the reduction of wall stress in a heart chamber as a result of deployment of the splint in accordance with the present invention.
The model used herein and the calculations related to this model are intended merely to illustrate the mechanism by which wall stress is reduced in the heart chamber. No effort is made herein to quantify the actual reduction which would be realized in any particular in vivo application.
Figure 37 is a view of the idealized heart chamber 48 of Figure 36 wherein the chamber has been splinted along its length L such that a "figure eight" cross-section has been formed along the length thereof. It should be noted that the perimeter of the circular transverse cross-section of the chamber in Figure 36 is equal to 'the perimeter of the figure eight transverse cross-section of Figure 37. Fo:r purposes of this model, opposite lobes of the figure in cross-section are assumed to be mirror images.
Figure 38 shows various parameters of the Figure 1 cross-section of the splinted idealized heart chamber of Figure 37. Where Q is the length of the splint between opposite walls of the chamber, Rz is the radius of each lobe, B is the angle between the two radii of one lobe which extends to opposite ends; of the portion of the splint within chamber 48 and h is the height of the triangle formed by the two radii and the portion of the splint within the chamber 48 (R1 is the radius of the cylinder of Figure 36). These various parameters are related as follows:
h = Rz COS ( B / 2 ) Q - 2 RZ SIN (B/2) Ra = RW / ( 27r - B ) From these relationships, the area of the figure eight cross-section can be calculated by:
AZ = 2~r (RZ) 2 (1-B/2~r) + h$
Where chamber 48 is unsplini=ed as shown in Figure 36 Al, the original cross-sectional area of the cylinder is equal to AZ where B - 180°, h :- 0 and $ - 2R2. Volume equals Az times length L and circumferential wall tension equals pressure within the chamber times Rz times the length L of the chamber.
Thus, for example, with an original cylindrical radius of four centimeters and a pressure within the chamber of 140 mm of mercury, the wall tension T in the walls of the cylinder is 104.4 newtons. When a 3.84 cm splint is placed as shown in Figures 37 and 38 such that $ = 3.84 cm, the wall tension T is 77.33 newtons.
Figures 39 and 40 show a hypothetical distribution of wall tension T and pressure P for the figure eight cross-section. As 8 goes from 180° to 0°, tension TS in the splint goes from 0 to a 2T load where the chamber walls carry a T load.
In yet another example, assuming that the chamber length L is a constant 10 cm, the original radius R1 is 4 cm, at a 140 mmHg the tension in the walls is 74.7 N.
If a 4.5 cm splint is placed such that P - 4.5 cm, the wall tension will then be 52.8 N.
It will be understood that this disclosure, in many respects, is only illustrative. Changes may be made in details, particularly in matters of shape, size, material, and arrangement of parts without exceeding the scope of the invention. Accordingly, the scope of the invention is as defined in the language of the appended claims.
Figure 2 discloses an alternate embodiment of the present invention, wherein a balloon 200 is deployed adjacent the left ventricle. The size and degree of inflation of the balloon can be varied to reduce the radius or cross-sectional area of left ventricle 10 of heart 14 .
Figure 3 shows yet another alternative embodiment of the present invention deployed with respect to left ventricle 10 of human heart 14. Here a compression frame structure 300 is engaged with heart 14 at atraumatic anchor pads 310. A compression member 312 having an atraumatic surface 314 presses against a wall of left ventricle 10 to reduce the radius or cross-sectional area thereof .
Figure 4 is a transverse cross-sectional view of human heart 14 showing yet another embodiment of the present invention. In this case a clamp 400 having atraumatic anchor pads 410 biased toward each other is shown disposed on a wall of left ventricle 10. Here the radius or cross-sectional area of left ventricle 10 is reduced by clamping off the portion of the wall between pads 410. Pads 410 can be biased toward each other and/or can be held together by a locking device.
Each of the various embodiments of the present invention disclosed in Figures 1-4 can be made from materials which can remain implanted in the human body indefinitely. Such biocompati.ble materials are well known to those skilled in the art of clinical medical devices.
Figure 5 shows an alternate: embodiment of the splint of Figure 1 referred to in Figure 5 by the numeral 116.
The embodiment 116 shown in :E'igure 5 includes three tension members 118 as opposed to a single tension member 18 as shown in Figure 1. Figure 6 shows yet another embodiment of the splint 216 haring four tension members 218. It is anticipated that in some patients, the disease process of the failing heart may be so advanced that three, four or more tension members may be desirable to reduce the heart wall stresses more substantially than possible with a single tension member as shown in Figure 1.
Figure 7 is a partial vertical cross-section of human heart 14 showing left ventricle 10. In Figure 7, another splint embodiment 316 is shown having a tension member 318 extending through left ventricle 10. On opposite ends of tension member 318 are disposed elongate anchors or pads 320. Figure 8 is an end view of tension member 318 showing elongate anchor 320.
Figure 9 shows another embodiment of a splint 416 disposed in a partial vertical cross-section of human heart 14. Splint 416 includes two elongate anchors or pads 420 similar to those shown in Figures 7 and 8. In Figure 9, however, two tension members 418 extend through left ventricle 10 to interconnect anchors 420 on opposite sides of heart 14.
Figure 10 is a vertical cross section of heart 14 showing left ventricle 10. In this case, two splints 16 are disposed through left ventricle 10 and vertically spaced from each other to resemble the configuration of Figure 9.
Figure 11 is a vertical cross sectional view of the left ventricle of heart 14. Two alternate embodiment splints 516 are shown extending through left ventricle 10. Each splint 516 includes two tension members 518 interconnecting two anchors or pads 520.
Figure 12 is yet another vertical cross sectional view of left ventricle 10 of heart 14. An alternate embodiment 616 of the splint ie; shown extending through left ventricle 10. Splint 6:16 includes an elongate anchor pad 620 and two shorter anchors or pads 621.
Splint 616 includes two tension members 618. Each tension member 618 extends between anchors 620 and respective anchors 621.
Figure 13 is a vertical cross sectional view of left ventricle l0 of heart 14. A sp7_int 50 is shown disposed on heart 14. Splint 50 include: a compression member 52 shown extending through left ventricle 10. Opposite ends of compression member 52 are disposed exterior to left ventricle 10. Lever members 54 extend from each end of compression member 52 upwardly along the exterior surface of ventricle 10. A tension member 56 extends between lever members 54 to bias lever mfsmbers 54 toward heart 14 to compress chamber 10. Compression member 52 should be substantially rigid, but lever members 54 and to some degree compression member 52 should be flexible enough to allow tension member 56 to bias lever members 54 toward heart 14. Alternately, lever members 54 could be hinged to compression member 52 such th~~t lever members 54 could pivot about the hinge when biased toward heart 14 by tension member 56.
WO 98!29041 PCT/L1S97/24116 Figure 14 shows an alternate embodiment 156 of the splint shown in Figure 13. In this case lever members 154 are longer than members 54 as compression member 152 of splint 150 has been disposed to the exterior of left ventricle 10.
Figure 15 is a vertical cross sectional view of left ventricle 10 of heart 14. An alternate embodiment 250 of the splint is shown on heart 14. A preferably relatively rigid frame member 255 extends through ventricle 10.
l0 Disposed on opposite ends of frame 250 are cantilever member 254. Disposed on cantilever members 254 are atraumatic pads 258. Cantilever members 254 can be positioned along frame member 256 such that atraumatic pads 258 press against heart 14 to compress chamber 10.
Figure 16 is an end view of frame member 256 showing cantilever members 254 and pads 258.
It should be understood that each of the embodiments described above should be formed from suitable biocompatible materials known to those skilled in the art. The tension members can be formed from flexible or relatively more rigid material. The compression members and frame member should be formed from generally rigid material which may flex under load, but generally hold its shape.
Figure 17 is a partial vertical cross-section of human heart 14 showing left ventricle 10 and left atrium 22. As shown in Figure 7, heart: 14 includes a region of scar tissue 24 associated with an aneurysm or ischemia.
As shown in Figure 7, the scar tissue 24 increases the radius or cross-sectional area of left ventricle 10 in the region affected by the scar tissue. Such an increase in the radius or cross-sectional area of the left ventricle will result in greater wall stresses on the walls of the left ventricle.
Figure 18 is a vertical crc>ss-sectional view of the heart 14 as shown in Figure 7, wherein a splint 16 has been placed to draw the scar tis:~ue 24 toward an opposite wall of left ventricle 10. As a consequence of placing splint 16, the radius or cross-se=_ctional area of the left ventricle affected by the scar tissue 24 is reduced. The reduction of this radius or cross-sectional area results in reduction in the wall stress in the left ventricular wall and thus improves heart pumping efficiency.
Figure 19 is a vertical cro:~s-sectional view of left ventricle 10 and left atrium 22 of heart 14 in which a splint 16 has been placed. As shown in Figure 9, splint 16 includes an alternative anchor 26. The anchor 26 is preferably an elongate member having a length as shown in Figure 9 substantially greater than its width (not shown). Anchor bar 26 might be used to reduce the radius or cross-sectional area of than left ventricle in an instance where there is generalized enlargement of left ventricle 10 such as in idiopathic dilated cardiomyopathy. In such an instance, bar anchor 26 can distribute forces more widely than anchor 20.
Figures 20 and 21 are side views of a hinged anchor 28 which could be substituted for anchors 20 in undeployed and deployed positions respectively. Anchor 28 as shown in Figure 20 includes two legs similar to bar anchor 26. Hinged anchor 28 could include additional legs and the length of those legs could be varied to distribute the force over the surface of the heart wall.
In addition there could be webbing between each of the legs to give anchor 28 an umbrella-like appearance.
Preferably the webbing would be disposed on the surface of the legs which would be in contact with the heart wall.
Figure 22 is a cross-sectional view of a capture ball anchor 30. Capture ball anchor 30 can be used in place of anchor 20. Capture ball anchor 30 includes a disk portion 32 to distribute the force of the anchor on the heart wall, and a recess 34 for receiving a ball 36 affixed to an end of tension member 18. Disk 32 and recess 34 include a side groove which allows tension member 38 to be passed from an outside edge of disk 32 into recess 34. Ball 36 can then be advanced into recess 34 by drawing tension member 18 through an opening 38 in recess 34 opposite disk 32.
Figure 23 is a perspective view of a cross bar anchor 40. The cross bar anchor 40 can be used in place of anchors 20. The anchor 40 preferably includes a disk or pad portion 42 having a cross bar 44 extending over an opening 46 in pad 42. Tension member 18 can be extended through opening 46 and tied to cross bar 42 as shown.
In use, the various embodiments of the present invention are placed in or adj;~cent the human heart to reduce the radius or cross-section area of at least one chamber of the heart. This is done to reduce wall stress or tension in the heart or chamber wall to slow, stop or reverse failure of the heart. 7:n the case of the splint 16 shown in Figure 1, a canula can be used to pierce both walls of the heart and one end of the splint can be advanced through the canula from one side of the heart to the opposite side where an anchor can be affixed or deployed. Likewise, an anchor i.s affixed or deployed at the opposite end of splint 16.
Figure 24 is a vertical cross-sectional view of a chamber 10 of a heart 14. A needle 60 having a stylet inserted therethrough is inserted through chamber 10.
Figure 25 shows needle 60 disposed in heart 40 as shown in Figure 24. In Figure 25, stylet 62 has been removed.
A tension member 64 having a flexible leader 66 attached to one end of tension member 64, is threaded through needle 60 and an anchor 68.
WO 98129041 PCT/iJS97/24116 As shown in Figure 25, tension member 64 includes a generally elongate cylindrical shaft 70 having two generally cylindrical ends 72. Ends 72 preferably have a greater diameter than shaft 70. Also shown in Figure 25 is a perspective view of anchor 68 showing an opening 73 extending through anchor 68. Opening 73 includes a first cylindrically shaped opening 74 extending entirely through anchor 68. The diameter of opening 74 is preferably slightly greater than the diameter of end 72 of tension member 64. A groove 76 having a width preferably slightly greater than that of shaft 70 of tension member 64 extends from opening 74 to a generally cylindrical opening 78. Generally cylindrical opening 78 has a diameter approximately equal to end 72. Unlike opening 74, however, opening 78 includes a reduced base opening 80 which has a width approximately equal to that of groove 76. The width of the opening 80 is also less than the diameter of end 72 of tension member 64.
It can be appreciated that tension member 64 can be advanced through opening 74 until shaft 70 is disposed therein. Shaft 70 can be then slid transversely through groove 76. Tension member 64 can then be advanced further through opening 73 until end portion 72 enters opening 78 and seats against base 80.
Figure 26 shows the view of heart 14 shown in Figure 25. Needle 60 has been removed from heart 14. Tension member 64 has been advanced into chamber 10 and anchor 68 connected thereto is engaging the heart wall. Leader 66 has been advanced through yet another anchor 68 disposed on the opposite side of heart 7_4.
Figure 27 is a view of heart 14 of Figure 26. Two tension member 64 have been advanced through chamber 10.
Each tension member has been seated in respective opening 78 against respective bases 80 to form a splint in a configuration such as that shown in Figure 9.
It can be appreciated that each of the other tension member splints configurations can be placed on the heart in a similar manner. It can <~lso be appreciated that anchors 68 could initially be held against the heart and needle 60 advanced through anchors 68 and chamber 10 prior to extending leader 66 through the needle.
Figure 28 is a perspective view of a tension member 164 in accordance with the present invention. Tension member 164 is similar to tension member 64 described above in that it has an elongate, generally cylindrical shaft 170 and generally cylindrical ends 172. A lumen, however, extends longitudinally through tension member 164 along axis A.
Figure 29 is a perspective view of yet another embodiment of the tension member 264. Tension member 264, is similar to tension member 164, and includes an elongate cylindrical shaft 270 and cylindrical ends 272.
Lumens 282, however, extend through ends 272 aligned along axis B.
Figure 30 is a vertical, cross-sectional view of left ventricle 10 of heart 14. Anchors 68 have been placed on opposite sides of heart 14. A needle 160 extends through the lumen of tension member 164, left ventricle 10 and openings 73 in anchors 68. It can be appreciated that tension member 64 can be advanced through anchors 68 and left ventricle 10 and be seated within openings 78 as described above with respect to tension member 64.
Figure 31 is a vertical, cross-sectional view of left ventricle 10 of heart 14. A needle 60 has been advanced through the wall of left ventricle 10 and a guidewire 162 has been advanced through needle 60.
Figure 32 is the same view of heart 14 as shown in Figure 32. Needle 60, however, has been removed from heart 14 while guidewire 162 remains in position.
Anchors 68 have been placed on guidewire 162, on opposite sides of left ventricle 10. Tension member 264 has been threaded onto guidewire 162 through lumens 282. It can be appreciated that as discussed above with respect to tension member 164 above, tension member 264 can be advanced through left ventricle 10 such that ends 272 of tension member 264 seat in respective openings 78 against base 80.
Figure 33 is a vertical, cross-sectional view of left ventricle 10 of heart 14. In Figure 34, flexible tension member 364 has been connected to a needle 360.
Needle 360 is shown being advanced into left ventricle 10 through a ventricle wall.
Figure 34 is the same view of heart 14 as shown in Figure 33 except that tension member 364 has been advanced entirely through left ventricle 10 and anchors 68. Knots 384 have been tied at the ends of tension member 364 to prevent the ends of tension member 364 from passing through opening 73 of anchors 68.
It can be appreciated that the methods described above to advance the tension members through the ventricles can be repeated to advance the desired number of tension members through the ventricle for a particular configuration. The length of the tension members can be determined based upon the size and condition of the patient's heart. It should also be noted that although the left ventricle has been referred to here for illustrative purposes, that the apparatus and methods of this invention can also be used to splint multiple chambers of a patient's heart. as well as the right ventricle or either atrium.
Figure 35 is a vertical cross-section of left ventricle 10 of heart 14. Disposed about heart 14 is a band 716. Band 716 is shown as being sized relative to the heart such that the heart' s radius or cross-sectional area in a plane parallel to the length of the band is reduced relative to the radius at that location prior to placement of the band on the heart. The length of the heart perpendicular to the band is also increased. The band may be formed from a continuous ribbon of elastomeric material or from other biocompatible materials which are sufficiently strong to provide the desired effect of heart radius reduction and lengthening.
Figure 36 is a view of a cylinder or idealized heart chamber 48 which is used to illustrate the reduction of wall stress in a heart chamber as a result of deployment of the splint in accordance with the present invention.
The model used herein and the calculations related to this model are intended merely to illustrate the mechanism by which wall stress is reduced in the heart chamber. No effort is made herein to quantify the actual reduction which would be realized in any particular in vivo application.
Figure 37 is a view of the idealized heart chamber 48 of Figure 36 wherein the chamber has been splinted along its length L such that a "figure eight" cross-section has been formed along the length thereof. It should be noted that the perimeter of the circular transverse cross-section of the chamber in Figure 36 is equal to 'the perimeter of the figure eight transverse cross-section of Figure 37. Fo:r purposes of this model, opposite lobes of the figure in cross-section are assumed to be mirror images.
Figure 38 shows various parameters of the Figure 1 cross-section of the splinted idealized heart chamber of Figure 37. Where Q is the length of the splint between opposite walls of the chamber, Rz is the radius of each lobe, B is the angle between the two radii of one lobe which extends to opposite ends; of the portion of the splint within chamber 48 and h is the height of the triangle formed by the two radii and the portion of the splint within the chamber 48 (R1 is the radius of the cylinder of Figure 36). These various parameters are related as follows:
h = Rz COS ( B / 2 ) Q - 2 RZ SIN (B/2) Ra = RW / ( 27r - B ) From these relationships, the area of the figure eight cross-section can be calculated by:
AZ = 2~r (RZ) 2 (1-B/2~r) + h$
Where chamber 48 is unsplini=ed as shown in Figure 36 Al, the original cross-sectional area of the cylinder is equal to AZ where B - 180°, h :- 0 and $ - 2R2. Volume equals Az times length L and circumferential wall tension equals pressure within the chamber times Rz times the length L of the chamber.
Thus, for example, with an original cylindrical radius of four centimeters and a pressure within the chamber of 140 mm of mercury, the wall tension T in the walls of the cylinder is 104.4 newtons. When a 3.84 cm splint is placed as shown in Figures 37 and 38 such that $ = 3.84 cm, the wall tension T is 77.33 newtons.
Figures 39 and 40 show a hypothetical distribution of wall tension T and pressure P for the figure eight cross-section. As 8 goes from 180° to 0°, tension TS in the splint goes from 0 to a 2T load where the chamber walls carry a T load.
In yet another example, assuming that the chamber length L is a constant 10 cm, the original radius R1 is 4 cm, at a 140 mmHg the tension in the walls is 74.7 N.
If a 4.5 cm splint is placed such that P - 4.5 cm, the wall tension will then be 52.8 N.
It will be understood that this disclosure, in many respects, is only illustrative. Changes may be made in details, particularly in matters of shape, size, material, and arrangement of parts without exceeding the scope of the invention. Accordingly, the scope of the invention is as defined in the language of the appended claims.
Claims (141)
1. An apparatus for treatment of a heart, the apparatus comprising:
a passive member adapted to be adjacent a wall of a heart chamber for drawing portions of the chamber wall towards each other so that the portions remain in a non-contacting relationship; and an anchor device coupled to the member for fixing the member in a position adjacent the chamber wall.
a passive member adapted to be adjacent a wall of a heart chamber for drawing portions of the chamber wall towards each other so that the portions remain in a non-contacting relationship; and an anchor device coupled to the member for fixing the member in a position adjacent the chamber wall.
2. The apparatus of claim 1, wherein the member is adapted to be placed within the chamber.
3. The apparatus of claim 2, wherein the member includes a tension member.
4. The apparatus of claim 3, wherein the member includes a plurality of tension members.
5. The apparatus of claim 3, wherein the anchor device includes a first anchor attached to a first end of the tension member and a second anchor attached to a second end of the tension member.
6. The apparatus of claim 5, wherein the first and second anchors are adapted to remain external the chamber and engage walls of the chamber.
7. The apparatus of claim 1, wherein the member is adapted to remain external the chamber.
8. The apparatus of claim 7, wherein the member includes a compression member.
9. An apparatus for treatment of a heart, the apparatus comprising:
a passive member adapted to be adjacent a wall of an intact heart chamber for drawing portions of the chamber wall towards each other, the member being configured so that all interior parts of the chamber remain in direct fluid communication; and an anchor device coupled to the member for fixing the member in a position adjacent the chamber wall.
a passive member adapted to be adjacent a wall of an intact heart chamber for drawing portions of the chamber wall towards each other, the member being configured so that all interior parts of the chamber remain in direct fluid communication; and an anchor device coupled to the member for fixing the member in a position adjacent the chamber wall.
10. The apparatus of claim 9, wherein the member is adapted to be placed within the chamber.
11. The apparatus of claim 10, wherein the member includes a tension member.
12. The apparatus of claim 11, wherein the member includes a plurality of tension members.
13. The apparatus of claim 11, wherein the anchor device includes a first anchor attached to a first end of the tension member and a second anchor attached to a second end of the tension member.
14. The apparatus of claim 13, wherein the first and second anchors are adapted to remain external the chamber and engage walls of the chamber.
15. The apparatus of claim 9, wherein the member is adapted to remain external the chamber.
16. The apparatus of claim 15, wherein the member includes a compression member.
17. An apparatus for treatment of a heart, the apparatus comprising:
a passive member adapted to be adjacent a wall of an intact heart chamber for altering a shape of the chamber, the member being configured so that all interior parts of the chamber remain in direct fluid communication; and an anchor device coupled to the member for fixing the member in a position adjacent the chamber wall.
a passive member adapted to be adjacent a wall of an intact heart chamber for altering a shape of the chamber, the member being configured so that all interior parts of the chamber remain in direct fluid communication; and an anchor device coupled to the member for fixing the member in a position adjacent the chamber wall.
18. The apparatus of claim 17, wherein the member is adapted to be placed within the chamber.
19. The apparatus of claim 18, wherein the member includes a tension member.
20. The apparatus of claim 19, wherein the member includes a plurality of tension members.
21. The apparatus of claim 19, wherein the anchor device includes a first anchor attached to a first end of the tension member and a second anchor attached to a second end of the tension member.
22. The apparatus of claim 21, wherein the first and second anchors are adapted to remain external the chamber and engage walls of the chamber.
23. The apparatus of claim 17, wherein the member is adapted to remain external the chamber.
24. The apparatus of claim 23, wherein the member includes a compression member.
25. The apparatus of claim 23, wherein the member includes a clamp.
26. An apparatus for treatment of a heart, the apparatus comprising:
a passive member adapted to be adjacent a wall of an intact heart chamber for reducing a radius of the chamber, the member being configured so that all interior parts of the chamber remain in direct fluid communication; and an anchor device coupled to the member for fixing the member in a position adjacent the chamber wall.
a passive member adapted to be adjacent a wall of an intact heart chamber for reducing a radius of the chamber, the member being configured so that all interior parts of the chamber remain in direct fluid communication; and an anchor device coupled to the member for fixing the member in a position adjacent the chamber wall.
27. The apparatus of claim 26, wherein the member is adapted to be placed within the chamber.
28. The apparatus of claim 27, wherein the member includes a tension member.
29. The apparatus of claim 28, wherein the member includes a plurality of tension members.
30. The apparatus of claim 28, wherein the anchor includes a first anchor attached to a first end of the tension member and a second anchor attached to a second end of the tension member.
31. The apparatus of claim 30, wherein the first and second anchors are adapted to remain external the chamber and engage walls of the chamber.
32. The apparatus of claim 26, wherein the member is adapted to remain external the chamber.
33. The apparatus of claim 32, wherein the member includes a compression member.
34. The apparatus of claim 32, wherein the member includes a clamp.
35. An apparatus for treatment of a heart, the apparatus comprising:
a passive member adapted to be adjacent a wall of an intact heart chamber for reducing a cross-sectional area of the chamber, the member being configured so that all interior parts of the chamber remain in direct fluid communication; and an anchor device coupled to the member for fixing the member in a position adjacent the chamber wall.
a passive member adapted to be adjacent a wall of an intact heart chamber for reducing a cross-sectional area of the chamber, the member being configured so that all interior parts of the chamber remain in direct fluid communication; and an anchor device coupled to the member for fixing the member in a position adjacent the chamber wall.
36. The apparatus of claim 35, wherein the member is adapted to be placed within the chamber.
37. The apparatus of claim 36, wherein the member includes a tension member.
38. The apparatus of claim 37, wherein the member includes a plurality of tension members.
39. The apparatus of claim 37, wherein the anchor device includes a first anchor attached to a first end of the tension member and a second anchor attached to a second end of the tension member.
40. The apparatus of claim 39, wherein the first and second anchors are adapted to remain external the chamber and engage walls of the chamber.
41. The apparatus of claim 35, wherein the member is adapted to remain external the chamber.
42. The apparatus of claim 41, wherein the member includes a compression member.
43. The apparatus of claim 41, wherein the member includes a clamp.
44. An apparatus for treatment of a heart, the apparatus comprising:
a passive member adapted to be adjacent portions of a wall of a heart chamber for altering a shape of the chamber, the member being configured so that the portions remain in a non-contacting relationship; and an anchor device coupled to the member for fixing the member in a position adjacent the chamber wall.
a passive member adapted to be adjacent portions of a wall of a heart chamber for altering a shape of the chamber, the member being configured so that the portions remain in a non-contacting relationship; and an anchor device coupled to the member for fixing the member in a position adjacent the chamber wall.
45. The apparatus of claim 44, wherein the member is adapted to be placed within the chamber.
46. The apparatus of claim 45, wherein the member includes a tension member.
47. The apparatus of claim 46, wherein the member includes a plurality of tension members.
48. The apparatus of claim 46, wherein the anchor device includes a first anchor attached to a first end of the tension member and a second anchor attached to a second end of the tension member.
49. The apparatus of claim 48, wherein the first and second anchors are adapted to remain external the chamber and engage walls of the chamber.
50. The apparatus of claim 44, wherein the member is adapted to remain external the chamber.
51. The apparatus of claim 48, wherein the member includes a compression member.
52. An apparatus for treatment of a heart, the apparatus comprising:
a passive member adapted to be adjacent portions of a wall of a heart chamber for reducing a radius of the chamber, the member being configured so that the portions remain in a non-contacting relationship; and an anchor device coupled to the member for fixing the member in a position adjacent the chamber wall.
a passive member adapted to be adjacent portions of a wall of a heart chamber for reducing a radius of the chamber, the member being configured so that the portions remain in a non-contacting relationship; and an anchor device coupled to the member for fixing the member in a position adjacent the chamber wall.
53. The apparatus of claim 52, wherein the member is adapted to be placed within the chamber.
54. The apparatus of claim 53, wherein the member includes a tension member.
55. The apparatus of claim 54, wherein the member includes a plurality of tension members.
56. The apparatus of claim 54, wherein the anchor device includes a first anchor attached to a first end of the tension member and a second anchor attached to a second end of the tension member.
57. The apparatus of claim 56, wherein the first and second anchors are adapted to remain external the chamber and engage walls of the chamber.
58. The apparatus of claim 52, wherein the member is adapted to remain external the chamber.
59. The apparatus of claim 58, wherein the member includes a compression member.
60. An apparatus for treatment of a heart, the apparatus comprising:
a passive member adapted to be adjacent portions of a wall of a heart chamber for reducing a cross-sectional area of the chamber, the member being configured so that the portions remain in a non-contacting relationship; and an anchor device coupled to the member for fixing the member in a position adjacent the chamber wall.
a passive member adapted to be adjacent portions of a wall of a heart chamber for reducing a cross-sectional area of the chamber, the member being configured so that the portions remain in a non-contacting relationship; and an anchor device coupled to the member for fixing the member in a position adjacent the chamber wall.
61. The apparatus of claim 60, wherein the member is adapted to be placed within the chamber.
62. The apparatus of claim 61, wherein the member includes a tension member.
63. The apparatus of claim 62, wherein the member includes a plurality of tension members.
64. The apparatus of claim 62, wherein the anchor device includes a first anchor attached to a first end of the tension member and a second anchor attached to a second end of the tension member.
65. The apparatus of claim 64, wherein the first and second anchors are adapted to remain external the chamber and engage walls of the chamber.
66. The apparatus of claim 60, wherein the member is adapted to remain external the chamber.
67. The apparatus of claim 66, wherein the member includes a compression member.
68. An apparatus for treatment of a heart, the apparatus comprising:
an elongate member having opposite ends the member adapted to be adjacent portions of a heart wall so that the portions remain in a non-contacting relationship; and an anchor disposed at each to engage the wall of the heart, the anchor including structure to receive and secure the member to the anchor.
an elongate member having opposite ends the member adapted to be adjacent portions of a heart wall so that the portions remain in a non-contacting relationship; and an anchor disposed at each to engage the wall of the heart, the anchor including structure to receive and secure the member to the anchor.
69. The apparatus of claim 68, wherein the structure includes a recess portion of the anchor.
70. The apparatus of claim 69, wherein the recess portion receives an end of the member.
71. The apparatus of claim 70, wherein the end of the member includes a ball.
72. The apparatus of claim 68, wherein the structure includes a cross bar.
73. The apparatus of claim 72, wherein the member ties to the cross bar.
74. A device for treatment of a heart, the device comprising:
a static member configured to be positioned adjacent a wall of a heart chamber; and an anchoring mechanism coupled to the member to engage the wall of the heart chamber, wherein the device is configured to draw portions of the chamber wall toward each other during at least a portion of a cardiac cycle such that all interior parts of the chamber remain in direct fluid communication with each other.
a static member configured to be positioned adjacent a wall of a heart chamber; and an anchoring mechanism coupled to the member to engage the wall of the heart chamber, wherein the device is configured to draw portions of the chamber wall toward each other during at least a portion of a cardiac cycle such that all interior parts of the chamber remain in direct fluid communication with each other.
75. The device of claim 74, wherein the member includes first and second opposite ends, and the anchoring mechanism includes an anchoring mechanism provided on each of the first and second opposite ends.
76. The device of claim 74, wherein the member is a tension member configured to be positioned transverse the heart chamber.
77. The device of claim 76, wherein an amount that portions of the chamber wall are drawn toward each other is determined by a length of the tension member transverse the heart chamber.
78. The device of claim 76, wherein the tension member includes more than one tension member configured to be positioned transverse the heart chamber.
79. The device of claim 74, wherein the anchoring mechanism is configured to engage an external surface of the heart wall.
80. The device of claim 74, wherein the member is adapted to remain external the chamber.
81. A device fox treatment of a heart, the device comprising:
a static member configured to be positioned adjacent a wall of a heart chamber; and an anchoring mechanism coupled to the member to engage the wall of the heart chamber wherein the device is configured to alter a shape of the chamber during at least a portion of a cardiac cycle such that all interior parts of the chamber remain in direct fluid communication with each other.
a static member configured to be positioned adjacent a wall of a heart chamber; and an anchoring mechanism coupled to the member to engage the wall of the heart chamber wherein the device is configured to alter a shape of the chamber during at least a portion of a cardiac cycle such that all interior parts of the chamber remain in direct fluid communication with each other.
82. The device of claim 81, wherein the member includes first and second opposite ends, and the anchoring mechanism includes an anchoring mechanism provided on each of the first and second opposite ends.
83. The device of claim 81, wherein the member is a tension member configured to be positioned .transverse the heart chamber.
84. The device of claim 83, wherein an amount that the shape of the chamber is altered is determined by a length of the tension member transverse the heart chamber.
85. The device of claim 83, wherein the tension member includes more than one tension member configured to be positioned transverse the heart chamber.
86. The device of claim 81, wherein the anchoring mechanism is configured to engage an external surface of the heart wall.
87. The device of claim 81, wherein the member is adapted to remain external the chamber.
88. A device for treatment of a heart, the device comprising:
a static member configured to be positioned adjacent a wall of a heart chamber; and an anchoring mechanism coupled to the member to engage the wail of the heart chamber, wherein the device is configured to reduce a radius of the chamber during at least a portion of a cardiac cycle such that all interior parts of the chamber remain in direct fluid communication with each other.
a static member configured to be positioned adjacent a wall of a heart chamber; and an anchoring mechanism coupled to the member to engage the wail of the heart chamber, wherein the device is configured to reduce a radius of the chamber during at least a portion of a cardiac cycle such that all interior parts of the chamber remain in direct fluid communication with each other.
89. The device of claim 88, wherein the member includes first and second opposite ends, and the anchoring mechanism includes an anchoring mechanism provided on each of the first and second opposite ends.
90. The device of claim 88, wherein the member is a tension member configured to be positioned transverse the heart chamber.
91. The device of claim 90, wherein an amount that the radius of the chamber is reduced is determined by a length of the tension member transverse the heart chamber.
92. The device of claim 90, wherein the tension member includes more than one tension member configured to be positioned transverse the heart chamber.
93. The device of claim 88, wherein the anchoring mechanism is configured to engage an external surface of the heart wall.
94. The device of claim 88, wherein the member is adapted to remain external the chamber.
95. A device for treatment of a heart, the device comprising:
a static member configured to be positioned adjacent a wall of a heart chamber; and an anchoring mechanism coupled to the member to engage the wall of the heart chamber, wherein the device is configured to draw portions of the chamber wall toward each other dining at least a portion of a cardiac cycle such that the portions of the chamber wall remain in a non-contacting relationship.
a static member configured to be positioned adjacent a wall of a heart chamber; and an anchoring mechanism coupled to the member to engage the wall of the heart chamber, wherein the device is configured to draw portions of the chamber wall toward each other dining at least a portion of a cardiac cycle such that the portions of the chamber wall remain in a non-contacting relationship.
96. The device of claim 95, wherein the member includes first and second opposite ends, and the anchoring mechanism includes an anchoring mechanism provided on each of the first and second opposite ends.
97. The device of claim 95, wherein the member is a tension member configured to be positioned transverse the heart chamber.
98. The device of claim 97, wherein an amount that portions of the chamber wall are drawn toward each other is determined by a length of the tension member transverse the heart chamber.
99. The device of claim 97, wherein the tension member includes more than one tension member configured to be positioned transverse the heart chamber.
100. The device of claim 95, wherein the anchoring mechanism is configured to engage an external surface of the heart wall.
101. The device of claim 95, wherein the member is adapted to remain external the chamber.
102. A device for treatment of a heart, the device comprising:
a static member configured to be positioned adjacent portions of a wall of a heart chamber; and an anchoring mechanism coupled to the member to engage the wall of the heart chamber, wherein the device is configured to alter a shape of the chamber during at least portion of a cardiac cycle such that the portions of the wall remain in a non-contacting relationship.
a static member configured to be positioned adjacent portions of a wall of a heart chamber; and an anchoring mechanism coupled to the member to engage the wall of the heart chamber, wherein the device is configured to alter a shape of the chamber during at least portion of a cardiac cycle such that the portions of the wall remain in a non-contacting relationship.
103. The device of claim 102, wherein the member includes first and second opposite ends, and the anchoring mechanism includes an anchoring mechanism provided on each of the first and second opposite ends.
104. The device of claim 102, wherein the member is a tension member configured to be positioned transverse the heart chamber.
105. The device of claim 104, wherein an amount that the shape of the chamber is altered is determined by a length of the tension member transverse the heart chamber.
106. The device of claim 104, wherein the tension member includes more than one tension member configured to be positioned transverse the heart chamber.
107. The device of claim 102, wherein the anchoring mechanism is configured to engage an external surface of the heart wall.
108. The device of claim 102, wherein the member is adapted to remain external the chamber.
109. A device for treatment of a heart, the device comprising:
a static member configured to be positioned adjacent portions of a wall of a heart chamber; and an anchoring mechanism coupled to the member to engage the wall of the heart chamber, wherein the device is configured to reduce a radius of the chamber during at least a portion of a cardiac cycle such that the portions of the wall remain in a non-contacting relationship.
a static member configured to be positioned adjacent portions of a wall of a heart chamber; and an anchoring mechanism coupled to the member to engage the wall of the heart chamber, wherein the device is configured to reduce a radius of the chamber during at least a portion of a cardiac cycle such that the portions of the wall remain in a non-contacting relationship.
110. The device of claim 109, wherein the member includes first and second opposite ends, and the anchoring mechanism includes an anchoring mechanism provided on each of the first and second opposite ends.
111. The device of claim 109, wherein the member is a tension member configured to be positioned transverse the heart chamber.
112. The device of claim 111, wherein an amount that the radius of the chamber is reduced is determined by a length of the tension member transverse the heart chamber.
113. The device of claim 112, wherein the tension member includes more than one tension member configured to be positioned transverse the heart chamber.
114. The device of claim 109, wherein the anchoring mechanism is configured to engage an external surface of the heart wall.
115. The device of claim 109, wherein the member is adapted to remain external the chamber.
116. A device for treating a heart, the device comprising:
an elongate member having first and second oppositely disposed ends;
a first anchoring member attached to the first end of the elongate member; and a second anchoring member attached to the second end of the elongate member, wherein. each of the first and second anchoring members are configured to engage an exterior surface of a wall of the heart to maintain a position of the elongate member transverse the heart chamber.
an elongate member having first and second oppositely disposed ends;
a first anchoring member attached to the first end of the elongate member; and a second anchoring member attached to the second end of the elongate member, wherein. each of the first and second anchoring members are configured to engage an exterior surface of a wall of the heart to maintain a position of the elongate member transverse the heart chamber.
117. The device of claim 116, wherein each of the first and second anchoring members has a disc-like shape .
118. The device of claim 116, wherein the heart chamber is the left ventricle.
119. The device of claim 116, wherein the first anchoring member is spaced from the second anchoring member.
120. The device of claim 116, wherein the device is configured to draw portions of the heart wall toward each other in a non-contacting relationship when the first and second anchoring members are engaged with the exterior portion of the wall and the elongate member is positioned transverse the heart chamber.
121. The device of claim 116, wherein the first anchoring member is configured to be attached to the elongate member after the elongate member is positioned transverse the heart chamber.
122. The device of claim 116, further comprising a mechanism configured to attach the elongate member to the first and second anchoring members.
123. The device of claim 116, wherein each of the first and second anchoring members define an opening configured to receive the elongate member.
124. A device for treating a heart, the device comprising:
a static member configured to be placed adjacent a wall of an intact heart chamber, the member having a surface adapted to press against the chamber wall to draw portions of the chamber wall towards each other and create a pair of lobes within the chamber that are in direct fluid communication.
a static member configured to be placed adjacent a wall of an intact heart chamber, the member having a surface adapted to press against the chamber wall to draw portions of the chamber wall towards each other and create a pair of lobes within the chamber that are in direct fluid communication.
125. The device of claim 124, wherein the surface is adapted to press against the chamber wall so that a radius of each of the pair off lobes is less than a radius of the chamber prior to creating the pair of lobes.
126. The device of claim 124, wherein the surface is adapted to press against the chamber wall so that the portions of the chamber wall drawn together remain in a noncontacting relationship.
127. The device of claim 124, wherein the member is adapted to remain external the chamber.
128. The device of claim 124, wherein the member includes at least one anchor device adapted to engage the chamber wall to fix the member in a position adjacent the chamber wall.
129. A system for treatment of a heart, comprising:
two elongate members each having two oppositely disposed ends;
and four anchoring members, wherein an anchoring member is provided on each of the ends of the elongate members, the anchoring members being configured to engage an exterior wall of a heart chamber to maintain a position of the corresponding elongate member with respect to the heart chamber, wherein each elongate member and corresponding anchoring members are configured to draw portions of the heart wall toward each other in a non-contacting relationship when the anchoring members are engaged with the exterior wall of the heart chamber and the corresponding elongate member is positioned with respect to the heart chamber.
two elongate members each having two oppositely disposed ends;
and four anchoring members, wherein an anchoring member is provided on each of the ends of the elongate members, the anchoring members being configured to engage an exterior wall of a heart chamber to maintain a position of the corresponding elongate member with respect to the heart chamber, wherein each elongate member and corresponding anchoring members are configured to draw portions of the heart wall toward each other in a non-contacting relationship when the anchoring members are engaged with the exterior wall of the heart chamber and the corresponding elongate member is positioned with respect to the heart chamber.
130. The system of claim 129, wherein the two elongate members are positioned orthogonally relative to each other.
131. A device for treating a heart, the device comprising:
an elongate member having first and second oppositely disposed ends;
a first anchoring member attached to the first end of the elongate member; and a second anchoring member attached to the second end of the elongate member, wherein the first anchoring member is configured to engage a first exterior surface of a wall of the heart and the second anchoring member is configured to engage a second exterior surface of the wall of the heart to maintain a position of the elongate member transverse a heart chamber, and wherein during at least a portion of a cardiac cycle, the device is configured to distribute a first force on the first exterior surface that is substantially uniform about the first end of the elongate member, distribute a second force on the second exterior surface that is substantially uniform about the second end of the elongate member, and draw first and second portions of the heart wall toward each other in a non-contacting relationship.
an elongate member having first and second oppositely disposed ends;
a first anchoring member attached to the first end of the elongate member; and a second anchoring member attached to the second end of the elongate member, wherein the first anchoring member is configured to engage a first exterior surface of a wall of the heart and the second anchoring member is configured to engage a second exterior surface of the wall of the heart to maintain a position of the elongate member transverse a heart chamber, and wherein during at least a portion of a cardiac cycle, the device is configured to distribute a first force on the first exterior surface that is substantially uniform about the first end of the elongate member, distribute a second force on the second exterior surface that is substantially uniform about the second end of the elongate member, and draw first and second portions of the heart wall toward each other in a non-contacting relationship.
132. The device of claim 131, wherein each of the first and second anchoring members is configured to extend substantially a same distance in both the vertical and transverse directions with respect to the first and second exterior surfaces respectively.
133. A device for treatment of a heart, the device comprising:
a static member configured to surround at least a portion of the heart, the member having a surface adapted to press against a wall of a chamber of the heart to alter a shape of the chamber without a bifurcation of the chamber.
a static member configured to surround at least a portion of the heart, the member having a surface adapted to press against a wall of a chamber of the heart to alter a shape of the chamber without a bifurcation of the chamber.
134. The device of claim 133, wherein the member includes first and second opposite ends, and the surface includes a first surface and a second surface provided on the first and second opposite ends respectively.
135. The device of claim 134, wherein the member is adapted to remain external the chamber.
136. The device of claim 134, wherein the member includes first and second anchor pads having the first and second surfaces respectively.
137. A device for treatment of a heart, the device comprising:
a static member configured to be positioned transverse a chamber of the heart, the member having a surface adapted to press against a wall of the chamber to alter a shape of the chamber without a bifurcation of the chamber.
a static member configured to be positioned transverse a chamber of the heart, the member having a surface adapted to press against a wall of the chamber to alter a shape of the chamber without a bifurcation of the chamber.
138. The device of claim 137, wherein the member includes first and second opposite ends, and the surface includes a first surface and a second surface provided on the first and second opposite ends respectively.
139. The device of claim 138, wherein the member includes first and second anchor pads having the first and second surfaces respectively.
140. The device of claim 139, wherein the anchor pads are configured to engage an external surface of the heart wall.
141. The device of claim 137, wherein the member includes more than one tension member configured to be positioned transverse the heart chamber.
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US08/778,277 US6050936A (en) | 1997-01-02 | 1997-01-02 | Heart wall tension reduction apparatus |
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US08/933,456 US5961440A (en) | 1997-01-02 | 1997-09-18 | Heart wall tension reduction apparatus and method |
US08/933,456 | 1997-09-18 | ||
PCT/US1997/024116 WO1998029041A1 (en) | 1997-01-02 | 1997-12-31 | Heart wall tension reduction apparatus and method |
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CA2275766C true CA2275766C (en) | 2007-04-17 |
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Families Citing this family (523)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
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 |
US5702343A (en) * | 1996-10-02 | 1997-12-30 | Acorn Medical, Inc. | Cardiac reinforcement device |
US6406420B1 (en) * | 1997-01-02 | 2002-06-18 | Myocor, Inc. | Methods and devices for improving cardiac function in hearts |
US7883539B2 (en) | 1997-01-02 | 2011-02-08 | Edwards Lifesciences Llc | Heart wall tension reduction apparatus and method |
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 |
US6183411B1 (en) | 1998-09-21 | 2001-02-06 | Myocor, Inc. | External stress reduction device and method |
US6077214A (en) * | 1998-07-29 | 2000-06-20 | Myocor, Inc. | Stress reduction apparatus and method |
US6050936A (en) | 1997-01-02 | 2000-04-18 | Myocor, Inc. | Heart wall tension reduction apparatus |
JP2002504841A (en) | 1997-06-21 | 2002-02-12 | ハインドル・ハンス | A bag surrounding at least part of the 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 |
US6110100A (en) * | 1998-04-22 | 2000-08-29 | Scimed Life Systems, Inc. | System for stress relieving the heart muscle and for controlling heart function |
US7060021B1 (en) * | 1998-07-23 | 2006-06-13 | Wilk Patent Development Corporation | Method and device for improving cardiac function |
EP2111800B1 (en) | 1998-07-29 | 2016-06-15 | Edwards Lifesciences AG | Transventricular implant tools and devices |
US6260552B1 (en) | 1998-07-29 | 2001-07-17 | Myocor, Inc. | Transventricular implant tools and devices |
US8715156B2 (en) * | 1998-10-09 | 2014-05-06 | Swaminathan Jayaraman | Modification of properties and geometry of heart tissue to influence function |
US6685627B2 (en) | 1998-10-09 | 2004-02-03 | Swaminathan Jayaraman | Modification of properties and geometry of heart tissue to influence heart function |
US6587734B2 (en) | 1998-11-04 | 2003-07-01 | Acorn Cardiovascular, Inc. | Cardio therapeutic heart sack |
US6230714B1 (en) | 1998-11-18 | 2001-05-15 | Acorn Cardiovascular, Inc. | Cardiac constraint with prior venus occlusion methods |
US6169922B1 (en) | 1998-11-18 | 2001-01-02 | Acorn Cardiovascular, Inc. | Defibrillating cardiac jacket with interwoven electrode grids |
US6749598B1 (en) | 1999-01-11 | 2004-06-15 | Flowmedica, Inc. | Apparatus and methods for treating congestive heart disease |
US7780628B1 (en) | 1999-01-11 | 2010-08-24 | Angiodynamics, Inc. | Apparatus and methods for treating congestive heart disease |
US6155972A (en) * | 1999-02-02 | 2000-12-05 | Acorn Cardiovascular, Inc. | Cardiac constraint jacket construction |
US20040044350A1 (en) | 1999-04-09 | 2004-03-04 | Evalve, Inc. | Steerable access sheath and methods of use |
US10327743B2 (en) * | 1999-04-09 | 2019-06-25 | Evalve, Inc. | Device and methods for endoscopic annuloplasty |
US8216256B2 (en) | 1999-04-09 | 2012-07-10 | Evalve, Inc. | Detachment mechanism for implantable fixation devices |
US7811296B2 (en) | 1999-04-09 | 2010-10-12 | Evalve, Inc. | Fixation devices for variation in engagement of tissue |
US7563267B2 (en) | 1999-04-09 | 2009-07-21 | Evalve, Inc. | Fixation device and methods for engaging tissue |
US6752813B2 (en) | 1999-04-09 | 2004-06-22 | Evalve, Inc. | Methods and devices for capturing and fixing leaflets in valve repair |
AU770243B2 (en) | 1999-04-09 | 2004-02-19 | Evalve, Inc. | Methods and apparatus for cardiac valve repair |
EP1176998B1 (en) | 1999-05-04 | 2008-01-09 | Simon Marcus Horner | Cardiac assist apparatus |
US7637905B2 (en) | 2003-01-15 | 2009-12-29 | Usgi Medical, Inc. | Endoluminal tool deployment system |
US7416554B2 (en) | 2002-12-11 | 2008-08-26 | Usgi Medical Inc | Apparatus and methods for forming and securing gastrointestinal tissue folds |
US8574243B2 (en) | 1999-06-25 | 2013-11-05 | Usgi Medical, Inc. | Apparatus and methods for forming and securing gastrointestinal tissue folds |
US7618426B2 (en) * | 2002-12-11 | 2009-11-17 | Usgi Medical, Inc. | Apparatus and methods for forming gastrointestinal tissue approximations |
US20040122456A1 (en) * | 2002-12-11 | 2004-06-24 | Saadat Vahid C. | Methods and apparatus for gastric reduction |
SE514718C2 (en) * | 1999-06-29 | 2001-04-09 | Jan Otto Solem | Apparatus for treating defective closure of the mitral valve apparatus |
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 |
US7279007B2 (en) * | 1999-08-09 | 2007-10-09 | Cardioklnetix, Inc. | Method for improving cardiac function |
US9694121B2 (en) | 1999-08-09 | 2017-07-04 | Cardiokinetix, Inc. | Systems and methods for improving cardiac function |
US8377114B2 (en) * | 1999-08-09 | 2013-02-19 | Cardiokinetix, Inc. | Sealing and filling ventricular partitioning devices to improve cardiac function |
US7582051B2 (en) * | 2005-06-10 | 2009-09-01 | Cardiokinetix, Inc. | Peripheral seal for a ventricular partitioning device |
US20030109770A1 (en) * | 1999-08-09 | 2003-06-12 | Sharkey Hugh R. | Device with a porous membrane for improving cardiac function |
US8257428B2 (en) * | 1999-08-09 | 2012-09-04 | Cardiokinetix, Inc. | System 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 |
US20060229491A1 (en) * | 2002-08-01 | 2006-10-12 | Cardiokinetix, Inc. | Method for treating myocardial rupture |
US8246671B2 (en) | 1999-08-09 | 2012-08-21 | Cardiokinetix, Inc. | Retrievable cardiac devices |
US8529430B2 (en) | 2002-08-01 | 2013-09-10 | Cardiokinetix, Inc. | Therapeutic methods and devices following myocardial infarction |
US7220281B2 (en) * | 1999-08-18 | 2007-05-22 | Intrinsic Therapeutics, Inc. | Implant for reinforcing and annulus fibrosis |
MXPA03003600A (en) * | 1999-08-18 | 2004-12-02 | Intrinsic Orthopedics Inc | Devices and method for nucleus pulposus augmentation and retention. |
US8323341B2 (en) * | 2007-09-07 | 2012-12-04 | Intrinsic Therapeutics, Inc. | Impaction grafting for vertebral fusion |
EP1624832A4 (en) * | 1999-08-18 | 2008-12-24 | Intrinsic Therapeutics Inc | Devices and method for augmenting a vertebral disc nucleus |
US7998213B2 (en) | 1999-08-18 | 2011-08-16 | Intrinsic Therapeutics, Inc. | Intervertebral disc herniation repair |
US7972337B2 (en) | 2005-12-28 | 2011-07-05 | Intrinsic Therapeutics, Inc. | Devices and methods for bone anchoring |
US7717961B2 (en) * | 1999-08-18 | 2010-05-18 | Intrinsic Therapeutics, Inc. | Apparatus delivery in an intervertebral disc |
WO2009033100A1 (en) * | 2007-09-07 | 2009-03-12 | Intrinsic Therapeutics, Inc. | Bone anchoring systems |
US7553329B2 (en) * | 1999-08-18 | 2009-06-30 | Intrinsic Therapeutics, Inc. | Stabilized intervertebral disc barrier |
US6193648B1 (en) | 1999-09-21 | 2001-02-27 | Acorn Cardiovascular, Inc. | Cardiac constraint with draw string tensioning |
US6179791B1 (en) | 1999-09-21 | 2001-01-30 | Acorn Cardiovascular, Inc. | Device for heart measurement |
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 |
US6293906B1 (en) | 2000-01-14 | 2001-09-25 | Acorn Cardiovascular, Inc. | Delivery of cardiac constraint jacket |
US6989028B2 (en) | 2000-01-31 | 2006-01-24 | Edwards Lifesciences Ag | Medical system and method for remodeling an extravascular tissue structure |
US6402781B1 (en) | 2000-01-31 | 2002-06-11 | Mitralife | Percutaneous mitral annuloplasty and cardiac reinforcement |
US7296577B2 (en) * | 2000-01-31 | 2007-11-20 | Edwards Lifescience Ag | Transluminal mitral annuloplasty with active anchoring |
EP1261294B1 (en) | 2000-03-10 | 2006-11-29 | Paracor Medical, Inc. | Expandable cardiac harness for treating 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. |
US6425856B1 (en) | 2000-05-10 | 2002-07-30 | Acorn Cardiovascular, Inc. | Cardiac disease treatment and device |
US20030023132A1 (en) * | 2000-05-31 | 2003-01-30 | Melvin David B. | Cyclic device for restructuring heart chamber geometry |
US6730016B1 (en) | 2000-06-12 | 2004-05-04 | Acorn Cardiovascular, Inc. | Cardiac disease treatment and device |
US20050095268A1 (en) * | 2000-06-12 | 2005-05-05 | Acorn Cardiovascular, Inc. | Cardiac wall tension relief with cell loss management |
US6902522B1 (en) | 2000-06-12 | 2005-06-07 | 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 |
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 |
US6343605B1 (en) * | 2000-08-08 | 2002-02-05 | Scimed Life Systems, Inc. | Percutaneous transluminal myocardial implantation device and method |
US8398537B2 (en) * | 2005-06-10 | 2013-03-19 | Cardiokinetix, Inc. | Peripheral seal for a ventricular partitioning device |
US9078660B2 (en) * | 2000-08-09 | 2015-07-14 | Cardiokinetix, Inc. | Devices and methods for delivering an endocardial device |
US20060030881A1 (en) * | 2004-08-05 | 2006-02-09 | Cardiokinetix, Inc. | Ventricular partitioning 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 |
US9332993B2 (en) | 2004-08-05 | 2016-05-10 | Cardiokinetix, Inc. | Devices and methods for delivering an endocardial 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 |
US10064696B2 (en) | 2000-08-09 | 2018-09-04 | Edwards Lifesciences Corporation | 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 |
US7691144B2 (en) | 2003-10-01 | 2010-04-06 | Mvrx, Inc. | Devices, systems, and methods for reshaping a heart valve annulus |
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 |
WO2004030568A2 (en) * | 2002-10-01 | 2004-04-15 | Ample Medical, Inc. | Device and method for repairing 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 |
US6893459B1 (en) * | 2000-09-20 | 2005-05-17 | Ample Medical, Inc. | Heart valve annulus device and method of using same |
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 |
WO2004030570A2 (en) * | 2002-10-01 | 2004-04-15 | Ample Medical, Inc. | Devices for retaining native heart valve leaflet |
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 |
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 |
US8784482B2 (en) * | 2000-09-20 | 2014-07-22 | Mvrx, Inc. | Method of reshaping a heart valve annulus using an intravascular device |
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 |
US6616684B1 (en) * | 2000-10-06 | 2003-09-09 | Myocor, Inc. | Endovascular splinting devices and methods |
US6723038B1 (en) | 2000-10-06 | 2004-04-20 | Myocor, Inc. | Methods and devices for improving mitral valve function |
US6673009B1 (en) * | 2000-11-08 | 2004-01-06 | Acorn Cardiovascular, Inc. | Adjustment clamp |
US6564094B2 (en) | 2000-12-22 | 2003-05-13 | Acorn Cardiovascular, Inc. | Cardiac disease treatment and device |
US20020161382A1 (en) * | 2001-03-29 | 2002-10-31 | Neisz Johann J. | Implant inserted without bone anchors |
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 |
US6575921B2 (en) | 2001-02-09 | 2003-06-10 | Acorn Cardiovascular, Inc. | Device for heart measurement |
US6702763B2 (en) * | 2001-02-28 | 2004-03-09 | Chase Medical, L.P. | Sizing apparatus and method for use during ventricular restoration |
US20020133227A1 (en) * | 2001-02-28 | 2002-09-19 | Gregory Murphy | Ventricular restoration patch apparatus and method of use |
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 |
US20060069429A1 (en) * | 2001-04-24 | 2006-03-30 | Spence Paul A | Tissue fastening systems and methods utilizing magnetic guidance |
US8202315B2 (en) | 2001-04-24 | 2012-06-19 | Mitralign, Inc. | Catheter-based annuloplasty using ventricularly positioned catheter |
US6619291B2 (en) * | 2001-04-24 | 2003-09-16 | Edwin J. Hlavka | Method and apparatus for catheter-based annuloplasty |
US7346394B2 (en) * | 2001-04-27 | 2008-03-18 | Cardiac Pacemakers, Inc. | Cardiac stimulation at high ventricular wall stress areas |
US7338514B2 (en) | 2001-06-01 | 2008-03-04 | St. Jude Medical, Cardiology Division, Inc. | Closure devices, related delivery methods and tools, and related methods of use |
US20040243170A1 (en) * | 2001-09-05 | 2004-12-02 | Mitta Suresh | Method and device for percutaneous surgical ventricular repair |
US7485088B2 (en) | 2001-09-05 | 2009-02-03 | Chase Medical L.P. | Method and device for percutaneous surgical ventricular repair |
WO2003022131A2 (en) * | 2001-09-07 | 2003-03-20 | Mardil, Inc. | Method and apparatus for external heart stabilization |
WO2003022176A2 (en) * | 2001-09-10 | 2003-03-20 | Paracor Medical, Inc. | Cardiac harness |
US6695769B2 (en) | 2001-09-25 | 2004-02-24 | The Foundry, Inc. | Passive ventricular support 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 |
US7060023B2 (en) * | 2001-09-25 | 2006-06-13 | The Foundry Inc. | Pericardium reinforcing devices and methods of using them |
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 |
US7144363B2 (en) * | 2001-10-16 | 2006-12-05 | Extensia Medical, Inc. | Systems for heart treatment |
EP1446069A1 (en) * | 2001-10-31 | 2004-08-18 | Paracor Surgical, Inc. | Heart failure treatment device |
US7635387B2 (en) | 2001-11-01 | 2009-12-22 | Cardiac Dimensions, Inc. | Adjustable height focal tissue deflector |
US6824562B2 (en) | 2002-05-08 | 2004-11-30 | Cardiac Dimensions, Inc. | Body lumen device anchor, device and assembly |
US6575971B2 (en) * | 2001-11-15 | 2003-06-10 | Quantum Cor, Inc. | Cardiac valve leaflet stapler device and methods thereof |
US20110087320A1 (en) * | 2001-11-28 | 2011-04-14 | Aptus Endosystems, Inc. | Devices, Systems, and Methods for Prosthesis Delivery and Implantation, Including a Prosthesis Assembly |
US20070073389A1 (en) | 2001-11-28 | 2007-03-29 | Aptus Endosystems, Inc. | Endovascular aneurysm devices, systems, and methods |
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 |
US20090099650A1 (en) * | 2001-11-28 | 2009-04-16 | Lee Bolduc | Devices, systems, and methods for endovascular staple and/or prosthesis delivery and implantation |
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 |
EP1448117B1 (en) | 2001-11-28 | 2013-05-22 | Aptus Endosystems, Inc. | Endovascular aneurysm repair system |
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 |
US6976995B2 (en) | 2002-01-30 | 2005-12-20 | Cardiac Dimensions, Inc. | Fixed length anchor and pull mitral valve device and method |
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 |
US20030225420A1 (en) | 2002-03-11 | 2003-12-04 | Wardle John L. | Surgical coils and methods of deploying |
US7181272B2 (en) | 2002-04-22 | 2007-02-20 | Medtronic, Inc. | Cardiac restraint with electrode attachment sites |
CA2483905C (en) | 2002-05-09 | 2011-01-25 | Tyco Healthcare Group Lp | Endoscopic organ retractor and method of using the same |
EP1503678B1 (en) * | 2002-05-09 | 2010-01-20 | Tyco Healthcare Group Lp | Organ retractor |
US20040010180A1 (en) * | 2002-05-16 | 2004-01-15 | Scorvo Sean K. | Cardiac assist system |
US7274876B2 (en) * | 2002-06-06 | 2007-09-25 | At&T Corp. | Integrated electrical/optical hybrid communication system with revertive hitless switch |
US6682475B2 (en) | 2002-06-11 | 2004-01-27 | Acorn Cardiovascular, Inc. | Tension indicator for cardiac support device and method therefore |
US20030233022A1 (en) * | 2002-06-12 | 2003-12-18 | Vidlund Robert M. | Devices and methods for heart valve treatment |
US8641727B2 (en) | 2002-06-13 | 2014-02-04 | Guided Delivery Systems, Inc. | Devices and methods for heart valve repair |
US20060122633A1 (en) | 2002-06-13 | 2006-06-08 | John To | Methods and devices for termination |
US7753858B2 (en) * | 2002-06-13 | 2010-07-13 | Guided Delivery Systems, Inc. | Delivery devices and methods for heart valve repair |
US7883538B2 (en) * | 2002-06-13 | 2011-02-08 | Guided Delivery Systems Inc. | Methods and devices for termination |
AU2003245507A1 (en) * | 2002-06-13 | 2003-12-31 | Guided Delivery Systems, 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 |
US9949829B2 (en) | 2002-06-13 | 2018-04-24 | Ancora Heart, Inc. | Delivery devices and methods for heart valve repair |
US8287555B2 (en) * | 2003-02-06 | 2012-10-16 | Guided Delivery Systems, Inc. | Devices and methods for heart valve repair |
US20040243227A1 (en) * | 2002-06-13 | 2004-12-02 | Guided Delivery Systems, Inc. | Delivery devices and methods for heart valve repair |
US7753924B2 (en) | 2003-09-04 | 2010-07-13 | Guided Delivery Systems, Inc. | Delivery devices and methods for heart valve repair |
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 |
US20040015041A1 (en) * | 2002-07-18 | 2004-01-22 | The University Of Cincinnati | Protective sheath apparatus and method for use with a heart wall actuation system for the natural heart |
AU2003261252A1 (en) * | 2002-07-26 | 2004-02-16 | Myomend, Inc. | Cardiac rhythm management system with intramural myocardial pacing leads and electrodes |
US20040242956A1 (en) * | 2002-07-29 | 2004-12-02 | Scorvo Sean K. | System for controlling fluid in a body |
US6988982B2 (en) * | 2002-08-19 | 2006-01-24 | Cardioenergetics | Heart wall actuation system for the natural heart with shape limiting elements |
US7485089B2 (en) * | 2002-09-05 | 2009-02-03 | Paracor Medical, Inc. | Cardiac harness |
US7063679B2 (en) * | 2002-09-20 | 2006-06-20 | Flowmedica, Inc. | Intra-aortic renal delivery catheter |
US7993325B2 (en) | 2002-09-20 | 2011-08-09 | Angio Dynamics, Inc. | Renal infusion systems and methods |
AU2003276903A1 (en) | 2002-09-20 | 2004-05-04 | Flowmedica, Inc. | Method and apparatus for selective material delivery via an intra-renal catheter |
EP1585572A4 (en) | 2002-09-20 | 2010-02-24 | Flowmedica Inc | Method and apparatus for intra aortic substance delivery to a branch vessel |
EP1562522B1 (en) * | 2002-10-01 | 2008-12-31 | Ample Medical, Inc. | Devices and systems for reshaping a heart valve annulus |
EP1565111B1 (en) * | 2002-10-04 | 2011-03-23 | Tyco Healthcare Group LP | Endoscopic retractor |
US7087064B1 (en) * | 2002-10-15 | 2006-08-08 | Advanced Cardiovascular Systems, Inc. | Apparatuses and methods for heart valve repair |
US8979923B2 (en) | 2002-10-21 | 2015-03-17 | Mitralign, Inc. | Tissue fastening systems and methods utilizing magnetic guidance |
BR0315392A (en) * | 2002-10-21 | 2005-08-23 | Mitralign Inc | Incrementing catheters and methods of performing annuloplasty |
US7112219B2 (en) | 2002-11-12 | 2006-09-26 | Myocor, Inc. | Devices and methods for heart valve treatment |
US7247134B2 (en) | 2002-11-12 | 2007-07-24 | Myocor, Inc. | Devices and methods for heart valve treatment |
US20070255093A1 (en) * | 2002-11-15 | 2007-11-01 | Lilip Lau | Cardiac harness delivery device and method |
US7331972B1 (en) | 2002-11-15 | 2008-02-19 | Abbott Cardiovascular Systems Inc. | Heart valve chord cutter |
US20050059855A1 (en) * | 2002-11-15 | 2005-03-17 | Lilip Lau | Cardiac harness delivery device and method |
US7736299B2 (en) * | 2002-11-15 | 2010-06-15 | Paracor Medical, Inc. | Introducer for a cardiac harness delivery |
US9149602B2 (en) | 2005-04-22 | 2015-10-06 | Advanced Cardiovascular Systems, Inc. | Dual needle delivery system |
US8187324B2 (en) | 2002-11-15 | 2012-05-29 | Advanced Cardiovascular Systems, Inc. | Telescoping apparatus for delivering and adjusting a medical device in a vessel |
US7335213B1 (en) | 2002-11-15 | 2008-02-26 | Abbott Cardiovascular Systems Inc. | Apparatus and methods for heart valve repair |
US20040098116A1 (en) | 2002-11-15 | 2004-05-20 | Callas Peter L. | Valve annulus constriction apparatus and method |
US7404824B1 (en) * | 2002-11-15 | 2008-07-29 | Advanced Cardiovascular Systems, Inc. | Valve aptation assist device |
US7485143B2 (en) * | 2002-11-15 | 2009-02-03 | Abbott Cardiovascular Systems Inc. | Apparatuses and methods for heart valve repair |
CA2504555C (en) * | 2002-11-15 | 2012-09-04 | Paracor Medical, Inc. | Cardiac harness delivery device |
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 |
US6945978B1 (en) | 2002-11-15 | 2005-09-20 | Advanced Cardiovascular Systems, Inc. | Heart valve catheter |
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 |
US6984242B2 (en) * | 2002-12-20 | 2006-01-10 | Gore Enterprise Holdings, Inc. | Implantable medical device assembly |
US7883500B2 (en) * | 2003-03-26 | 2011-02-08 | G&L Consulting, Llc | Method and system to treat and prevent myocardial infarct expansion |
US20050283042A1 (en) * | 2003-03-28 | 2005-12-22 | Steve Meyer | Cardiac harness having radiopaque coating and method of use |
US20040249242A1 (en) * | 2003-03-28 | 2004-12-09 | Lilip Lau | Multi-panel cardiac harness |
US20040220654A1 (en) | 2003-05-02 | 2004-11-04 | Cardiac Dimensions, Inc. | Device and method for modifying the shape of a body organ |
US10667823B2 (en) | 2003-05-19 | 2020-06-02 | 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 |
JP2006526464A (en) | 2003-06-05 | 2006-11-24 | フローメディカ,インコーポレイテッド | System and method for performing bilateral intervention or diagnosis in a branched body lumen |
US7887582B2 (en) * | 2003-06-05 | 2011-02-15 | Cardiac Dimensions, Inc. | Device and method for modifying the shape of a body organ |
WO2004110257A2 (en) | 2003-06-09 | 2004-12-23 | The University Of Cincinnati | Power 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 |
US20060178551A1 (en) * | 2003-06-09 | 2006-08-10 | Melvin David B | Securement system 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 |
JP2007528749A (en) * | 2003-07-10 | 2007-10-18 | パラコー メディカル インコーポレイテッド | Self-fixing cardiac harness |
US7513867B2 (en) * | 2003-07-16 | 2009-04-07 | Kardium, Inc. | Methods and devices for altering blood flow through the left ventricle |
US8216252B2 (en) | 2004-05-07 | 2012-07-10 | Usgi Medical, Inc. | Tissue manipulation and securement system |
US7235042B2 (en) | 2003-09-16 | 2007-06-26 | Acorn Cardiovascular, Inc. | Apparatus and method for applying cardiac support device |
US7998112B2 (en) | 2003-09-30 | 2011-08-16 | Abbott Cardiovascular Systems Inc. | Deflectable catheter assembly and method of making same |
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 |
US20050137673A1 (en) * | 2003-11-07 | 2005-06-23 | Lilip Lau | Cardiac harness having electrodes and epicardial leads |
US20050171589A1 (en) * | 2003-11-07 | 2005-08-04 | Lilip Lau | Cardiac harness and method of delivery by minimally invasive access |
US20070106336A1 (en) * | 2003-11-07 | 2007-05-10 | Alan Schaer | Cardiac harness assembly for treating congestive heart failure and for pacing/sensing |
US7158839B2 (en) * | 2003-11-07 | 2007-01-02 | Paracor Medical, Inc. | Cardiac harness for treating heart disease |
US20070055091A1 (en) * | 2004-12-02 | 2007-03-08 | Lilip Lau | Cardiac harness for treating congestive heart failure and for defibrillating and/or pacing/sensing |
US20070106359A1 (en) * | 2003-11-07 | 2007-05-10 | Alan Schaer | Cardiac harness assembly for treating congestive heart failure and for pacing/sensing |
US7361180B2 (en) * | 2004-05-07 | 2008-04-22 | Usgi Medical, Inc. | Apparatus for manipulating and securing tissue |
US7347863B2 (en) * | 2004-05-07 | 2008-03-25 | Usgi Medical, Inc. | Apparatus and methods 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 |
US9526616B2 (en) | 2003-12-19 | 2016-12-27 | Cardiac Dimensions Pty. Ltd. | Mitral valve annuloplasty device with twisted anchor |
US20060271174A1 (en) * | 2003-12-19 | 2006-11-30 | Gregory Nieminen | Mitral Valve Annuloplasty Device with Wide Anchor |
US8864822B2 (en) | 2003-12-23 | 2014-10-21 | Mitralign, Inc. | Devices and methods for introducing elements into tissue |
US7431726B2 (en) | 2003-12-23 | 2008-10-07 | Mitralign, Inc. | Tissue fastening systems and methods utilizing magnetic guidance |
CA2553185A1 (en) * | 2004-01-12 | 2005-08-04 | Paracor Medical, Inc. | Cardiac harness having interconnected strands |
WO2005091910A2 (en) | 2004-03-04 | 2005-10-06 | Flowmedica, Inc. | Sheath for use in peripheral interventions |
US7703459B2 (en) | 2004-03-09 | 2010-04-27 | Usgi Medical, Inc. | Apparatus and methods for mapping out endoluminal gastrointestinal surgery |
WO2005087140A1 (en) | 2004-03-11 | 2005-09-22 | Percutaneous Cardiovascular Solutions Pty Limited | Percutaneous heart valve prosthesis |
US7255675B2 (en) * | 2004-03-23 | 2007-08-14 | Michael Gertner | Devices and methods to treat a patient |
US7172551B2 (en) * | 2004-04-12 | 2007-02-06 | Scimed Life Systems, Inc. | Cyclical pressure coronary assist pump |
EP1744679A2 (en) * | 2004-05-03 | 2007-01-24 | AMS Research Corporation | Surgical implants and related methods |
US8057511B2 (en) | 2004-05-07 | 2011-11-15 | Usgi Medical, Inc. | Apparatus and methods for positioning and securing anchors |
US7736374B2 (en) * | 2004-05-07 | 2010-06-15 | Usgi Medical, Inc. | Tissue manipulation and securement system |
US7390329B2 (en) * | 2004-05-07 | 2008-06-24 | Usgi Medical, Inc. | Methods for grasping and cinching tissue anchors |
US8444657B2 (en) | 2004-05-07 | 2013-05-21 | Usgi Medical, Inc. | Apparatus and methods for rapid deployment of tissue anchors |
US20050251208A1 (en) * | 2004-05-07 | 2005-11-10 | Usgi Medical Inc. | Linear anchors for anchoring to tissue |
US7918869B2 (en) | 2004-05-07 | 2011-04-05 | Usgi Medical, Inc. | Methods and apparatus for performing endoluminal gastroplasty |
US20050251176A1 (en) * | 2004-05-07 | 2005-11-10 | Usgi Medical Inc. | System for treating gastroesophageal reflux disease |
US20060135971A1 (en) * | 2004-05-07 | 2006-06-22 | Usgi Medical Inc. | System for treating gastroesophageal reflux disease |
US8257394B2 (en) * | 2004-05-07 | 2012-09-04 | Usgi Medical, Inc. | Apparatus and methods for positioning and securing anchors |
EP1750592B1 (en) | 2004-05-14 | 2016-12-28 | Evalve, Inc. | Locking mechanisms for fixation devices |
US7736379B2 (en) * | 2004-06-09 | 2010-06-15 | Usgi Medical, Inc. | Compressible tissue anchor assemblies |
US7695493B2 (en) * | 2004-06-09 | 2010-04-13 | Usgi Medical, Inc. | System for optimizing anchoring force |
US8206417B2 (en) * | 2004-06-09 | 2012-06-26 | Usgi Medical Inc. | Apparatus and methods for optimizing anchoring force |
US7678135B2 (en) | 2004-06-09 | 2010-03-16 | Usgi Medical, Inc. | Compressible tissue anchor assemblies |
US20060009675A1 (en) * | 2004-07-08 | 2006-01-12 | Steven Meyer | Self-anchoring cardiac harness for treating the heart and for defibrillating and/or pacing/sensing |
US7285087B2 (en) * | 2004-07-15 | 2007-10-23 | Micardia Corporation | Shape memory devices and methods for reshaping heart anatomy |
US7402134B2 (en) * | 2004-07-15 | 2008-07-22 | Micardia Corporation | Magnetic devices and methods for reshaping heart anatomy |
DE102004040135B3 (en) * | 2004-08-19 | 2005-12-15 | Abg Allgemeine Baumaschinen-Gesellschaft Mbh | Self-propelled device for milling traffic areas |
US7635329B2 (en) | 2004-09-27 | 2009-12-22 | Evalve, Inc. | Methods and devices for tissue grasping and assessment |
US8052592B2 (en) | 2005-09-27 | 2011-11-08 | Evalve, Inc. | Methods and devices for tissue grasping and assessment |
US20090326578A1 (en) * | 2004-09-30 | 2009-12-31 | Usgi Medical, Inc. | Interlocking tissue anchor apparatus and methods |
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 |
US20060135970A1 (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 |
US20060129026A1 (en) * | 2004-12-15 | 2006-06-15 | Joshua Wallin | Apparatus and method for mounting a cardiac harness on the heart |
US8060219B2 (en) | 2004-12-20 | 2011-11-15 | Cardiac Pacemakers, Inc. | Epicardial patch including isolated extracellular matrix with pacing electrodes |
US7981065B2 (en) * | 2004-12-20 | 2011-07-19 | Cardiac Pacemakers, Inc. | Lead electrode incorporating extracellular matrix |
US7731705B2 (en) | 2005-01-10 | 2010-06-08 | Wardle John L | Eluting coils and methods of deploying and retrieving |
JP4926980B2 (en) | 2005-01-20 | 2012-05-09 | カーディアック ディメンションズ インコーポレイテッド | Tissue shaping device |
EP1845861B1 (en) | 2005-01-21 | 2011-06-22 | Mayo Foundation for Medical Education and Research | Thorascopic heart valve repair apparatus |
US8470028B2 (en) | 2005-02-07 | 2013-06-25 | Evalve, Inc. | Methods, systems and devices for cardiac valve repair |
EP3967269A3 (en) | 2005-02-07 | 2022-07-13 | Evalve, Inc. | Systems and devices for cardiac valve repair |
US20060189840A1 (en) * | 2005-02-18 | 2006-08-24 | Acorn Cardiovascular, Inc. | Transmyocardial delivery of cardiac wall tension relief |
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 |
US8608797B2 (en) | 2005-03-17 | 2013-12-17 | Valtech Cardio Ltd. | Mitral valve treatment techniques |
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 |
JP2008534084A (en) * | 2005-03-25 | 2008-08-28 | アンプル メディカル, インコーポレイテッド | Apparatus, system, and method for reshaping a heart valve annulus |
US8333777B2 (en) | 2005-04-22 | 2012-12-18 | Benvenue Medical, Inc. | Catheter-based tissue remodeling devices and methods |
US8109866B2 (en) * | 2005-04-26 | 2012-02-07 | Ams Research Corporation | Method and apparatus for prolapse repair |
US20060247491A1 (en) * | 2005-04-27 | 2006-11-02 | Vidlund Robert M | Devices and methods for heart valve treatment |
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 |
US20070032696A1 (en) * | 2005-07-22 | 2007-02-08 | Sieu Duong | Cardiac harness delivery device |
JP4376836B2 (en) * | 2005-07-29 | 2009-12-02 | 富士フイルム株式会社 | Magnetic recording device |
US7587247B2 (en) * | 2005-08-01 | 2009-09-08 | Paracor Medical, Inc. | Cardiac harness having an optimal impedance range |
US20070055206A1 (en) * | 2005-08-10 | 2007-03-08 | Guided Delivery Systems, Inc. | Methods and devices for deployment of tissue anchors |
US20070043416A1 (en) * | 2005-08-19 | 2007-02-22 | Cardiac Pacemakers, Inc. | Implantable electrode array |
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 |
EP1968492A2 (en) * | 2005-12-15 | 2008-09-17 | Georgia Technology Research Corporation | Systems and methods to control the dimension of a heart valve |
US8568473B2 (en) * | 2005-12-15 | 2013-10-29 | Georgia Tech Research Corporation | Systems and methods for enabling heart valve replacement |
US9125742B2 (en) * | 2005-12-15 | 2015-09-08 | Georgia Tech Research Foundation | Papillary muscle position control devices, systems, and methods |
US8726909B2 (en) | 2006-01-27 | 2014-05-20 | Usgi Medical, Inc. | Methods and apparatus for revision of obesity procedures |
US20070233219A1 (en) * | 2006-02-16 | 2007-10-04 | Bilal Shafi | Polymeric heart restraint |
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 |
US7727142B2 (en) | 2006-03-03 | 2010-06-01 | Acorn Cardiovascular, Inc. | Delivery tool for cardiac support device |
JP5148598B2 (en) | 2006-05-03 | 2013-02-20 | ラプトール リッジ, エルエルシー | Tissue closure system and method |
US20070265658A1 (en) * | 2006-05-12 | 2007-11-15 | Aga Medical Corporation | Anchoring and tethering system |
US20070270654A1 (en) * | 2006-05-19 | 2007-11-22 | Acorn Cardiovascular, Inc. | Pericardium management tool for intra-pericardial surgical procedures |
US20070287883A1 (en) * | 2006-06-07 | 2007-12-13 | Lilip Lau | Apparatus and method for pulling a cardiac harness onto a heart |
US7771401B2 (en) | 2006-06-08 | 2010-08-10 | Angiodynamics, Inc. | Selective renal cannulation and infusion systems and methods |
DE102006028964A1 (en) * | 2006-06-16 | 2007-12-20 | Eberhard-Karls-Universität Tübingen | Device for the treatment of mitral valve insufficiency |
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 |
US7877142B2 (en) * | 2006-07-05 | 2011-01-25 | Micardia Corporation | Methods and systems for cardiac remodeling via resynchronization |
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 |
US11285005B2 (en) | 2006-07-17 | 2022-03-29 | Cardiac Dimensions Pty. Ltd. | Mitral valve annuloplasty device with twisted anchor |
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 |
US7641608B1 (en) | 2006-09-26 | 2010-01-05 | Acorn Cardiovascular, Inc. | Sectional cardiac support device and method of delivery |
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 |
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 |
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 |
US20110257723A1 (en) | 2006-11-07 | 2011-10-20 | Dc Devices, Inc. | Devices and methods for coronary sinus pressure relief |
US9232997B2 (en) | 2006-11-07 | 2016-01-12 | Corvia Medical, Inc. | Devices and methods for retrievable intra-atrial implants |
US8460372B2 (en) | 2006-11-07 | 2013-06-11 | Dc Devices, Inc. | Prosthesis for reducing intra-cardiac pressure having an embolic filter |
US10413284B2 (en) | 2006-11-07 | 2019-09-17 | Corvia Medical, Inc. | Atrial pressure regulation with control, sensing, monitoring and therapy delivery |
CA2664557C (en) | 2006-11-07 | 2015-05-26 | David Stephen Celermajer | Devices and methods for the treatment of heart failure |
JP2010511469A (en) * | 2006-12-05 | 2010-04-15 | バルテック カーディオ,リミティド | Segmented ring placement |
US9883943B2 (en) | 2006-12-05 | 2018-02-06 | Valtech Cardio, Ltd. | Implantation of repair devices in the heart |
WO2010004546A1 (en) | 2008-06-16 | 2010-01-14 | Valtech Cardio, Ltd. | Annuloplasty devices and methods of delivery therefor |
US11259924B2 (en) | 2006-12-05 | 2022-03-01 | Valtech Cardio Ltd. | Implantation of repair devices in the heart |
US20080177380A1 (en) * | 2007-01-19 | 2008-07-24 | Starksen Niel F | Methods and devices for heart tissue repair |
EP3345572A1 (en) | 2007-02-14 | 2018-07-11 | Edwards Lifesciences Corporation | Suture and method for repairing heart |
US8845723B2 (en) | 2007-03-13 | 2014-09-30 | Mitralign, Inc. | Systems and methods for introducing elements into tissue |
US8911461B2 (en) | 2007-03-13 | 2014-12-16 | Mitralign, Inc. | Suture cutter and method of cutting suture |
US11660190B2 (en) | 2007-03-13 | 2023-05-30 | Edwards Lifesciences Corporation | Tissue anchors, systems and methods, and devices |
CA2693198C (en) | 2007-07-27 | 2014-10-14 | Ams Research Corporation | Pelvic floor treatments and related tools and implants |
US20090048480A1 (en) * | 2007-08-13 | 2009-02-19 | Paracor Medical, Inc. | Cardiac harness delivery device |
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 |
EP2194888B1 (en) * | 2007-10-03 | 2021-04-28 | Bioventrix, Inc. | System for treating dysfunctional cardiac tissue |
CA2703129C (en) | 2007-10-18 | 2016-02-16 | Neochord Inc. | Minimially invasive repair of a valve leaflet in a beating heart |
EP2217153B1 (en) * | 2007-10-19 | 2021-03-03 | Ancora Heart, Inc. | Systems for cardiac remodeling |
WO2009076209A1 (en) * | 2007-12-05 | 2009-06-18 | Surgical Energetics, Inc | A bolster for securing a septal splint to a cardiac wall, a method of use thereof, and a system including the same |
WO2009075800A1 (en) * | 2007-12-07 | 2009-06-18 | Ams Research Corporation | Pelvic floor treatments and related tools and implants |
US20090177028A1 (en) * | 2008-01-04 | 2009-07-09 | Anthony John White | Non-blood contact cardiac compression device, for augmentation of cardiac function by timed cyclic tensioning of elastic cords in an epicardial location |
WO2009100242A2 (en) | 2008-02-06 | 2009-08-13 | Guided Delivery Systems, Inc. | Multi-window guide tunnel |
US8382829B1 (en) | 2008-03-10 | 2013-02-26 | Mitralign, Inc. | Method to reduce mitral regurgitation by cinching the commissure of the mitral valve |
US8260395B2 (en) * | 2008-04-18 | 2012-09-04 | Medtronic, Inc. | Method and apparatus for mapping a structure |
US20090281372A1 (en) * | 2008-05-06 | 2009-11-12 | Paracor Medical, Inc. | Cardiac harness assembly for treating congestive heart failure and for defibrillation and/or pacing/sensing |
WO2009137712A1 (en) * | 2008-05-07 | 2009-11-12 | 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 |
US8647254B2 (en) | 2008-07-01 | 2014-02-11 | Maquet Cardiovascular Llc | Epicardial clip |
US8425402B2 (en) * | 2008-07-21 | 2013-04-23 | Bioventrix, Inc. | Cardiac anchor structures, methods, and systems for treatment of congestive heart failure and other conditions |
EP2349019B1 (en) | 2008-10-10 | 2020-03-25 | Ancora Heart, Inc. | Termination devices and related methods |
CN102245110A (en) * | 2008-10-10 | 2011-11-16 | 导向传输系统股份有限公司 | Tether tensioning devices and related methods |
CA2740867C (en) | 2008-10-16 | 2018-06-12 | Aptus Endosystems, Inc. | Devices, systems, and methods for endovascular staple and/or prosthesis delivery and implantation |
US8808368B2 (en) | 2008-12-22 | 2014-08-19 | Valtech Cardio, Ltd. | Implantation of repair chords in the heart |
US9011530B2 (en) | 2008-12-22 | 2015-04-21 | Valtech Cardio, Ltd. | Partially-adjustable annuloplasty structure |
US8545553B2 (en) | 2009-05-04 | 2013-10-01 | Valtech Cardio, Ltd. | Over-wire rotation tool |
US10517719B2 (en) | 2008-12-22 | 2019-12-31 | Valtech Cardio, Ltd. | Implantation of repair devices in the heart |
US8715342B2 (en) | 2009-05-07 | 2014-05-06 | Valtech Cardio, Ltd. | Annuloplasty ring with intra-ring anchoring |
US8147542B2 (en) | 2008-12-22 | 2012-04-03 | Valtech Cardio, Ltd. | Adjustable repair chords and spool mechanism therefor |
WO2010073246A2 (en) | 2008-12-22 | 2010-07-01 | Valtech Cardio, Ltd. | Adjustable annuloplasty devices and adjustment mechanisms therefor |
US8926697B2 (en) | 2011-06-23 | 2015-01-06 | Valtech Cardio, Ltd. | Closed band for percutaneous annuloplasty |
US8940044B2 (en) | 2011-06-23 | 2015-01-27 | Valtech Cardio, Ltd. | Closure element for use with an annuloplasty structure |
US8241351B2 (en) * | 2008-12-22 | 2012-08-14 | Valtech Cardio, Ltd. | Adjustable partial annuloplasty ring and mechanism therefor |
US9204965B2 (en) * | 2009-01-14 | 2015-12-08 | Lc Therapeutics, Inc. | Synthetic chord |
US20100198056A1 (en) * | 2009-01-20 | 2010-08-05 | Mariel Fabro | Diagnostic catheters, guide catheters, visualization devices and chord manipulation devices, and related kits and methods |
US20100198192A1 (en) | 2009-01-20 | 2010-08-05 | Eugene Serina | Anchor deployment devices and related methods |
US20100274227A1 (en) * | 2009-02-13 | 2010-10-28 | Alexander Khairkhahan | Delivery catheter handle cover |
US8353956B2 (en) * | 2009-02-17 | 2013-01-15 | Valtech Cardio, Ltd. | Actively-engageable movement-restriction mechanism for use with an annuloplasty structure |
WO2013069019A2 (en) | 2011-11-08 | 2013-05-16 | Valtech Cardio, Ltd. | Controlled steering functionality for implant-delivery tool |
US9968452B2 (en) | 2009-05-04 | 2018-05-15 | Valtech Cardio, Ltd. | Annuloplasty ring delivery cathethers |
US8523881B2 (en) | 2010-07-26 | 2013-09-03 | Valtech Cardio, Ltd. | Multiple anchor delivery tool |
US8449466B2 (en) | 2009-05-28 | 2013-05-28 | Edwards Lifesciences Corporation | System and method for locating medical devices in vivo using ultrasound Doppler mode |
CA2768027A1 (en) | 2009-07-20 | 2011-01-27 | Ams Research Corporation | Devices, systems, and methods for delivering fluid to tissue |
JP5489580B2 (en) * | 2009-08-04 | 2014-05-14 | キヤノン株式会社 | Image forming apparatus and control method thereof |
US9757107B2 (en) | 2009-09-04 | 2017-09-12 | Corvia Medical, Inc. | Methods and devices for intra-atrial shunts having adjustable sizes |
EP2633821B1 (en) | 2009-09-15 | 2016-04-06 | Evalve, Inc. | Device for cardiac valve repair |
WO2011041571A2 (en) | 2009-10-01 | 2011-04-07 | Kardium Inc. | Medical device, kit and method for constricting tissue or a bodily orifice, for example, a mitral valve |
WO2011056578A2 (en) | 2009-10-26 | 2011-05-12 | Cardiokinetix, Inc. | Ventricular volume reduction |
US8690939B2 (en) | 2009-10-29 | 2014-04-08 | Valtech Cardio, Ltd. | Method for guide-wire based advancement of a rotation assembly |
US8277502B2 (en) * | 2009-10-29 | 2012-10-02 | Valtech Cardio, Ltd. | Tissue anchor for annuloplasty device |
US9180007B2 (en) | 2009-10-29 | 2015-11-10 | Valtech Cardio, Ltd. | Apparatus and method for guide-wire based advancement of an adjustable implant |
US10098737B2 (en) | 2009-10-29 | 2018-10-16 | Valtech Cardio, Ltd. | Tissue anchor for annuloplasty device |
US9011520B2 (en) | 2009-10-29 | 2015-04-21 | Valtech Cardio, Ltd. | Tissue anchor for annuloplasty device |
EP2506777B1 (en) | 2009-12-02 | 2020-11-25 | Valtech Cardio, Ltd. | Combination of spool assembly coupled to a helical anchor and delivery tool for implantation thereof |
US8870950B2 (en) | 2009-12-08 | 2014-10-28 | Mitral Tech Ltd. | Rotation-based anchoring of an implant |
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 |
US9307980B2 (en) | 2010-01-22 | 2016-04-12 | 4Tech Inc. | Tricuspid valve repair using tension |
EP2528646A4 (en) | 2010-01-29 | 2017-06-28 | DC Devices, Inc. | Devices and systems for treating heart failure |
AU2011210741B2 (en) | 2010-01-29 | 2013-08-15 | Corvia Medical, Inc. | Devices and methods for reducing venous pressure |
US9107749B2 (en) | 2010-02-03 | 2015-08-18 | Edwards Lifesciences Corporation | Methods for treating a heart |
US9072603B2 (en) * | 2010-02-24 | 2015-07-07 | Medtronic Ventor Technologies, Ltd. | Mitral prosthesis and methods for implantation |
US8790394B2 (en) | 2010-05-24 | 2014-07-29 | Valtech Cardio, Ltd. | Adjustable artificial chordeae tendineae with suture loops |
US9050066B2 (en) | 2010-06-07 | 2015-06-09 | Kardium Inc. | Closing openings in anatomical tissue |
US11653910B2 (en) | 2010-07-21 | 2023-05-23 | Cardiovalve Ltd. | Helical anchor implantation |
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 |
EP2658480B1 (en) | 2010-12-29 | 2017-11-01 | Neochord Inc. | Exchangeable system for minimally invasive beating heart repair of heart valve leaflets |
CN103635226B (en) | 2011-02-10 | 2017-06-30 | 可维亚媒体公司 | Device for setting up and keeping intra-atrial pressure power release aperture |
WO2012161769A1 (en) | 2011-02-18 | 2012-11-29 | Guided Delivery Systems Inc. | Implant retrieval device |
WO2012112967A1 (en) | 2011-02-18 | 2012-08-23 | Guided Delivery Systems Inc. | Systems and methods for variable stiffness tethers |
US9072511B2 (en) | 2011-03-25 | 2015-07-07 | Kardium Inc. | Medical kit for constricting tissue or a bodily orifice, for example, a mitral valve |
WO2012167120A2 (en) | 2011-06-01 | 2012-12-06 | Neochord, Inc. | Minimally invasive repair of heart valve leaflets |
US9918840B2 (en) | 2011-06-23 | 2018-03-20 | Valtech Cardio, Ltd. | Closed band for percutaneous annuloplasty |
US10792152B2 (en) | 2011-06-23 | 2020-10-06 | Valtech Cardio, Ltd. | Closed band for percutaneous annuloplasty |
US8945177B2 (en) | 2011-09-13 | 2015-02-03 | Abbott Cardiovascular Systems Inc. | Gripper pusher mechanism for tissue apposition systems |
US8900295B2 (en) | 2011-09-26 | 2014-12-02 | Edwards Lifesciences Corporation | Prosthetic valve with ventricular tethers |
BR112014007686A2 (en) | 2011-09-30 | 2017-04-18 | Bioventrix Inc | method and system for heart treatment within the patient |
US8858623B2 (en) | 2011-11-04 | 2014-10-14 | Valtech Cardio, Ltd. | Implant having multiple rotational assemblies |
WO2013096965A1 (en) | 2011-12-22 | 2013-06-27 | Dc Devices, Inc. | Methods and devices for intra-atrial devices having selectable flow rates |
US9005155B2 (en) | 2012-02-03 | 2015-04-14 | Dc Devices, Inc. | Devices and methods for treating heart failure |
US10076414B2 (en) | 2012-02-13 | 2018-09-18 | Mitraspan, Inc. | Method and apparatus for repairing a mitral valve |
AU2013221670A1 (en) | 2012-02-13 | 2014-10-02 | Mitraspan, Inc | Method and apparatus for repairing a mitral valve |
US9265514B2 (en) | 2012-04-17 | 2016-02-23 | Miteas Ltd. | Manipulator for grasping tissue |
US10588611B2 (en) | 2012-04-19 | 2020-03-17 | Corvia Medical Inc. | Implant retention attachment and method of use |
US9649480B2 (en) | 2012-07-06 | 2017-05-16 | Corvia Medical, Inc. | Devices and methods of treating or ameliorating diastolic heart failure through pulmonary valve intervention |
CA2885354A1 (en) | 2012-09-29 | 2014-04-03 | Mitralign, Inc. | Plication lock delivery system and method of use thereof |
EP2906151B1 (en) | 2012-10-12 | 2023-06-21 | Mardil, Inc. | Cardiac treatment system |
US10376266B2 (en) | 2012-10-23 | 2019-08-13 | Valtech Cardio, Ltd. | Percutaneous tissue anchor techniques |
EP3517052A1 (en) | 2012-10-23 | 2019-07-31 | Valtech Cardio, Ltd. | Controlled steering functionality for implant-delivery tool |
US9730793B2 (en) | 2012-12-06 | 2017-08-15 | Valtech Cardio, Ltd. | Techniques for guide-wire based advancement of a tool |
US9788948B2 (en) | 2013-01-09 | 2017-10-17 | 4 Tech Inc. | Soft tissue anchors and implantation techniques |
US9681952B2 (en) | 2013-01-24 | 2017-06-20 | Mitraltech Ltd. | Anchoring of prosthetic valve supports |
WO2014134183A1 (en) | 2013-02-26 | 2014-09-04 | Mitralign, Inc. | Devices and methods for percutaneous tricuspid valve repair |
US9775636B2 (en) | 2013-03-12 | 2017-10-03 | Corvia Medical, Inc. | Devices, systems, and methods for treating heart failure |
US10617425B2 (en) | 2014-03-10 | 2020-04-14 | Conformal Medical, Inc. | Devices and methods for excluding the left atrial appendage |
WO2014164572A1 (en) | 2013-03-13 | 2014-10-09 | Kaplan Aaron V | Devices and methods for excluding the left atrial appendage |
US11399842B2 (en) | 2013-03-13 | 2022-08-02 | Conformal Medical, Inc. | Devices and methods for excluding the left atrial appendage |
US10449333B2 (en) | 2013-03-14 | 2019-10-22 | Valtech Cardio, Ltd. | Guidewire feeder |
CN105208978B (en) | 2013-03-14 | 2016-12-07 | 4科技有限公司 | There is the support of tether interface |
WO2014159842A1 (en) * | 2013-03-14 | 2014-10-02 | The United States Of America, As Represented By The Secretary, Department Of Health And Human Services | Devices and methods for treating functional tricuspid valve regurgitation |
EP2968847B1 (en) | 2013-03-15 | 2023-03-08 | Edwards Lifesciences Corporation | Translation catheter systems |
CA2912653A1 (en) | 2013-05-24 | 2014-11-27 | Bioventrix, Inc. | Cardiac tissue penetrating devices, methods, and systems for treatment of congestive heart failure and other conditions |
EP3957252A1 (en) | 2013-08-30 | 2022-02-23 | Bioventrix, Inc. | Heart anchor positioning devices, methods, and systems for treatment of congestive heart failure and other conditions |
WO2015031647A2 (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 |
US10299793B2 (en) | 2013-10-23 | 2019-05-28 | Valtech Cardio, Ltd. | Anchor magazine |
CA2925667A1 (en) * | 2013-10-23 | 2015-04-30 | Lc Therapeutics, Inc. | Percutaneous or minimally invasive cardiac valve repair system and methods of using the same |
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 |
US10485545B2 (en) | 2013-11-19 | 2019-11-26 | Datascope Corp. | Fastener applicator with interlock |
US9610162B2 (en) | 2013-12-26 | 2017-04-04 | Valtech Cardio, Ltd. | Implantation of flexible implant |
US9730701B2 (en) | 2014-01-16 | 2017-08-15 | Boston Scientific Scimed, Inc. | Retrieval wire centering device |
US20170000935A1 (en) | 2014-01-27 | 2017-01-05 | Children's Medical Center Corporation | Mechanical assist device |
US10675450B2 (en) | 2014-03-12 | 2020-06-09 | Corvia Medical, Inc. | Devices and methods for treating heart failure |
US9572666B2 (en) | 2014-03-17 | 2017-02-21 | Evalve, Inc. | Mitral valve fixation device removal devices and methods |
US10390943B2 (en) | 2014-03-17 | 2019-08-27 | Evalve, Inc. | Double orifice device for transcatheter mitral valve replacement |
US9801720B2 (en) | 2014-06-19 | 2017-10-31 | 4Tech Inc. | Cardiac tissue cinching |
US10632292B2 (en) | 2014-07-23 | 2020-04-28 | Corvia Medical, Inc. | Devices and methods for treating heart failure |
AU2015321690A1 (en) | 2014-09-28 | 2017-03-23 | Cardiokinetix, Inc. | Apparatuses for treating cardiac dysfunction |
WO2016059639A1 (en) | 2014-10-14 | 2016-04-21 | Valtech Cardio Ltd. | Leaflet-restraining techniques |
JP6717820B2 (en) | 2014-12-02 | 2020-07-08 | 4テック インコーポレイテッド | Eccentric tissue anchor |
US10188392B2 (en) | 2014-12-19 | 2019-01-29 | Abbott Cardiovascular Systems, Inc. | Grasping for tissue repair |
US9480565B2 (en) * | 2015-02-02 | 2016-11-01 | On-X Life Technologies, Inc. | Rapid deployment artificial chordae tendinae system |
WO2016125160A1 (en) | 2015-02-05 | 2016-08-11 | Mitraltech Ltd. | Prosthetic valve with axially-sliding frames |
EP4292551A3 (en) | 2015-03-05 | 2024-01-31 | Ancora Heart, Inc. | Devices of visualizing and determining depth of penetration in cardiac tissue |
US20160256269A1 (en) | 2015-03-05 | 2016-09-08 | Mitralign, Inc. | Devices for treating paravalvular leakage and methods use thereof |
WO2016144391A1 (en) | 2015-03-11 | 2016-09-15 | 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 |
CN111265335B (en) | 2015-04-30 | 2022-03-15 | 瓦尔泰克卡迪欧有限公司 | Valvuloplasty techniques |
EP4074285A1 (en) | 2015-05-12 | 2022-10-19 | Ancora Heart, Inc. | Device 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 |
EP3346926B1 (en) | 2015-09-10 | 2020-10-21 | Bioventrix, Inc. | Systems for deploying a cardiac anchor |
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 |
US10463492B2 (en) | 2015-11-17 | 2019-11-05 | Edwards Lifesciences Corporation | Systems and devices for setting an anchor |
US10278818B2 (en) | 2015-12-10 | 2019-05-07 | Mvrx, Inc. | Devices, systems, and methods for reshaping a heart valve annulus |
US10751182B2 (en) | 2015-12-30 | 2020-08-25 | Edwards Lifesciences Corporation | System and method for reshaping right heart |
US10828160B2 (en) | 2015-12-30 | 2020-11-10 | Edwards Lifesciences Corporation | System and method for reducing tricuspid regurgitation |
WO2017132516A1 (en) | 2016-01-29 | 2017-08-03 | Kevin Van Bladel | Percutaneous arterial access to position transmyocardial implant devices and methods |
WO2017156259A1 (en) | 2016-03-10 | 2017-09-14 | Lc Therapeutics, Inc. | Synthetic chord for cardiac valve repair applications |
US10702274B2 (en) | 2016-05-26 | 2020-07-07 | Edwards Lifesciences Corporation | Method and system for closing left atrial appendage |
WO2017210434A1 (en) | 2016-06-01 | 2017-12-07 | On-X Life Technologies, Inc. | Pull-through chordae tendineae system |
US10736632B2 (en) | 2016-07-06 | 2020-08-11 | Evalve, Inc. | Methods and devices for valve clip excision |
GB201611910D0 (en) | 2016-07-08 | 2016-08-24 | Valtech Cardio Ltd | Adjustable annuloplasty device with alternating peaks and troughs |
EP3848003A1 (en) | 2016-08-10 | 2021-07-14 | Cardiovalve Ltd. | Prosthetic valve with concentric frames |
US11071564B2 (en) | 2016-10-05 | 2021-07-27 | Evalve, Inc. | Cardiac valve cutting device |
JP7071350B2 (en) | 2016-10-27 | 2022-05-18 | コンフォーマル・メディカル・インコーポレイテッド | Devices and methods for eliminating the left atrial appendage |
US11426172B2 (en) | 2016-10-27 | 2022-08-30 | Conformal Medical, Inc. | Devices and methods for excluding the left atrial appendage |
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 |
AU2017362497B2 (en) | 2016-11-18 | 2022-07-28 | 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 |
US10390953B2 (en) | 2017-03-08 | 2019-08-27 | Cardiac Dimensions Pty. Ltd. | Methods and devices for reducing paravalvular leakage |
US10898330B2 (en) | 2017-03-28 | 2021-01-26 | Edwards Lifesciences Corporation | Positioning, deploying, and retrieving implantable devices |
US10213306B2 (en) | 2017-03-31 | 2019-02-26 | Neochord, Inc. | Minimally invasive heart valve repair in a beating heart |
US11045627B2 (en) | 2017-04-18 | 2021-06-29 | Edwards Lifesciences Corporation | Catheter system with linear actuation control mechanism |
US11065119B2 (en) | 2017-05-12 | 2021-07-20 | Evalve, Inc. | Long arm valve repair clip |
US10835221B2 (en) | 2017-11-02 | 2020-11-17 | Valtech Cardio, Ltd. | Implant-cinching devices and systems |
US11135062B2 (en) | 2017-11-20 | 2021-10-05 | Valtech Cardio Ltd. | Cinching of dilated heart muscle |
WO2019108286A1 (en) * | 2017-11-30 | 2019-06-06 | Boston Scientific Scimed, Inc. | Connected anchor delivery systems and methods for valve repair |
CN111655200B (en) | 2018-01-24 | 2023-07-14 | 爱德华兹生命科学创新(以色列)有限公司 | Contraction of annuloplasty structures |
CN110074834A (en) * | 2018-01-25 | 2019-08-02 | 上海微创医疗器械(集团)有限公司 | Medical device |
EP4248904A3 (en) | 2018-01-26 | 2023-11-29 | Edwards Lifesciences Innovation (Israel) Ltd. | Techniques for facilitating heart valve tethering and chord replacement |
EP3768176B1 (en) | 2018-03-23 | 2024-03-20 | NeoChord, Inc. | Device for suture attachment for minimally invasive heart valve repair |
WO2019191271A1 (en) | 2018-03-28 | 2019-10-03 | Datascope Corp. | Device for atrial appendage exclusion |
US11173030B2 (en) | 2018-05-09 | 2021-11-16 | Neochord, Inc. | Suture length adjustment 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 |
WO2020012481A2 (en) | 2018-07-12 | 2020-01-16 | Valtech Cardio, Ltd. | Annuloplasty systems and locking tools therefor |
US10966709B2 (en) | 2018-09-07 | 2021-04-06 | Neochord, Inc. | Device for suture attachment for minimally invasive heart valve repair |
WO2020163507A1 (en) | 2019-02-08 | 2020-08-13 | Conformal Medical, Inc. | Devices and methods for excluding the left atrial appendage |
WO2020214818A1 (en) | 2019-04-16 | 2020-10-22 | Neochord, Inc. | Transverse helical cardiac anchor for minimally invasive heart valve repair |
CA3147413A1 (en) | 2019-07-15 | 2021-01-21 | Ancora Heart, Inc. | Devices and methods for tether cutting |
US11540838B2 (en) | 2019-08-30 | 2023-01-03 | Boston Scientific Scimed, Inc. | Left atrial appendage implant with sealing disk |
EP4193934A1 (en) | 2019-10-29 | 2023-06-14 | Edwards Lifesciences Innovation (Israel) Ltd. | Annuloplasty and tissue anchor technologies |
EP4125634A1 (en) | 2020-03-24 | 2023-02-08 | Boston Scientific Scimed Inc. | Medical system for treating a left atrial appendage |
EP4259045A1 (en) | 2020-12-14 | 2023-10-18 | Cardiac Dimensions Pty. Ltd. | Modular pre-loaded medical implants and delivery systems |
Family Cites Families (318)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US34021A (en) * | 1861-12-24 | Ufacture of fibrous water | ||
US575783A (en) * | 1897-01-26 | X nofmiis peters co | ||
US963899A (en) * | 1909-11-06 | 1910-07-12 | Kistler Samuel L | Surgical clamp. |
GB583012A (en) * | 1944-09-21 | 1946-12-04 | E R Watts & Son Ltd | Improvements in magnetic compasses |
US3019790A (en) * | 1960-07-15 | 1962-02-06 | Robert J Militana | Combination hemostat and intravenous needle |
NL143127B (en) * | 1969-02-04 | 1974-09-16 | Rhone Poulenc Sa | REINFORCEMENT DEVICE FOR A DEFECTIVE HEART VALVE. |
US3868956A (en) * | 1972-06-05 | 1975-03-04 | Ralph J Alfidi | Vessel implantable appliance and method of implanting it |
US3980086A (en) * | 1974-02-28 | 1976-09-14 | Bio-Medicus, Inc. | Fluid conveying surgical instrument |
GB1492964A (en) * | 1974-04-02 | 1977-11-23 | Cav Ltd | Fuel injection pumping apparatus governor |
FR2306671A1 (en) * | 1975-04-11 | 1976-11-05 | Rhone Poulenc Ind | VALVULAR IMPLANT |
FR2298313A1 (en) * | 1975-06-23 | 1976-08-20 | Usifroid | LINEAR REDUCER FOR VALVULOPLASTY |
US4035849A (en) * | 1975-11-17 | 1977-07-19 | William W. Angell | Heart valve stent and process for preparing a stented heart valve prosthesis |
US4048990A (en) * | 1976-09-17 | 1977-09-20 | Goetz Robert H | Heart massage apparatus |
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 |
US4281659A (en) * | 1979-03-12 | 1981-08-04 | Roche Medical Electronics Inc. | Applying and securing percutaneous or transcutaneous probes to the skin especially for fetal monitoring |
GB2056023B (en) * | 1979-08-06 | 1983-08-10 | Ross D N Bodnar E | Stent for a cardiac valve |
US4306319A (en) * | 1980-06-16 | 1981-12-22 | Robert L. Kaster | Heart valve with non-circular body |
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 |
DE3227984C2 (en) | 1982-07-27 | 1985-10-17 | Abdoll-Hossein Dr. med. 4330 Mülheim Towfigh | Device for producing a tendon butt seam |
US4579120A (en) * | 1982-09-30 | 1986-04-01 | Cordis Corporation | Strain relief for percutaneous lead |
US4592342A (en) * | 1983-05-02 | 1986-06-03 | Salmasian Samuel S | Method for appetite suppression and weight loss maintenance and device |
US4629459A (en) * | 1983-12-28 | 1986-12-16 | Shiley Inc. | Alternate stent covering for tissue valves |
US4632101A (en) * | 1985-01-31 | 1986-12-30 | Yosef Freedland | Orthopedic fastener |
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 |
CA1303298C (en) * | 1986-08-06 | 1992-06-16 | Alain Carpentier | Flexible cardiac valvular support prosthesis |
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 |
GB2214428B (en) | 1988-01-09 | 1991-06-26 | Ali Waqar Majeed | Surgical device |
US5156621A (en) * | 1988-03-22 | 1992-10-20 | Navia Jose A | Stentless bioprosthetic cardiac valve |
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 |
US4990424A (en) * | 1988-08-12 | 1991-02-05 | Xerox Corporation | Toner and developer compositions with semicrystalline polyolefin resin blends |
US4944753A (en) * | 1988-09-26 | 1990-07-31 | Burgess Frank M | Method for producing retro-sternal space |
EP0595791B1 (en) | 1989-02-13 | 1999-06-30 | Baxter International Inc. | Anuloplasty ring prosthesis |
US4991578A (en) | 1989-04-04 | 1991-02-12 | Siemens-Pacesetter, Inc. | Method and system for implanting self-anchoring epicardial defibrillation electrodes |
US5484885A (en) | 1989-07-05 | 1996-01-16 | Emory University | Chemotactic, antibiotic and lipopolysaccharide-binding peptide fragments of CAP37 |
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 |
US5129906A (en) | 1989-09-08 | 1992-07-14 | Linvatec Corporation | Bioabsorbable tack for joining bodily tissue and in vivo method and apparatus for deploying same |
US5131905A (en) * | 1990-07-16 | 1992-07-21 | Grooters Ronald K | External cardiac assist device |
US5389096A (en) * | 1990-12-18 | 1995-02-14 | Advanced Cardiovascular Systems | System and method for percutaneous myocardial revascularization |
US5245102A (en) | 1990-11-29 | 1993-09-14 | Uop | Isomerization with distillation and psa recycle streams |
CA2059245C (en) * | 1991-02-08 | 2004-07-06 | Michael P. Chesterfield | Method and apparatus for calendering and coating/filling sutures |
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 |
US5258015A (en) * | 1991-05-03 | 1993-11-02 | American Cyanamid Company | Locking filament caps |
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 |
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 |
US5344385A (en) * | 1991-09-30 | 1994-09-06 | Thoratec Laboratories Corporation | Step-down skeletal muscle energy conversion system |
DK168419B1 (en) * | 1991-11-25 | 1994-03-28 | Cook Inc A Cook Group Company | Abdominal wall support device and apparatus for insertion thereof |
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 |
DE69331315T2 (en) * | 1992-01-27 | 2002-08-22 | Medtronic Inc | ANULOPLASTIC AND SEAM RINGS |
US5258021A (en) * | 1992-01-27 | 1993-11-02 | Duran Carlos G | Sigmoid valve annuloplasty ring |
US5758663A (en) | 1992-04-10 | 1998-06-02 | Wilk; Peter J. | Coronary artery by-pass method |
US5332402A (en) * | 1992-05-12 | 1994-07-26 | Teitelbaum George P | Percutaneously-inserted cardiac valve |
NL9200878A (en) | 1992-05-19 | 1993-12-16 | Dirk Wouter Meijer En Joannes | Medical-instrument-insertion equipment in body cavity - has devices detachably securing tube distal end to wall of hollow organ |
US5383840A (en) * | 1992-07-28 | 1995-01-24 | Vascor, Inc. | Biocompatible ventricular assist and arrhythmia control device including cardiac compression band-stay-pad assembly |
US5256132A (en) * | 1992-08-17 | 1993-10-26 | Snyders Robert V | Cardiac assist envelope for endoscopic application |
DE4234127C2 (en) * | 1992-10-09 | 1996-02-22 | Herbert Dr Vetter | Heart valve prosthesis |
US5814097A (en) * | 1992-12-03 | 1998-09-29 | Heartport, Inc. | Devices and methods for intracardiac procedures |
US5718725A (en) * | 1992-12-03 | 1998-02-17 | 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 |
US5522884A (en) * | 1993-02-19 | 1996-06-04 | Medtronic, Inc. | Holder for adjustable mitral & tricuspid annuloplasty rings |
US6010531A (en) * | 1993-02-22 | 2000-01-04 | Heartport, Inc. | Less-invasive devices and methods for cardiac valve surgery |
US5797960A (en) * | 1993-02-22 | 1998-08-25 | Stevens; John H. | Method and apparatus for thoracoscopic intracardiac procedures |
US5972030A (en) | 1993-02-22 | 1999-10-26 | Heartport, Inc. | Less-invasive devices and methods for treatment of cardiac valves |
US20020029783A1 (en) * | 1993-02-22 | 2002-03-14 | Stevens John H. | Minimally-invasive devices and methods for treatment of congestive heart failure |
US6125852A (en) | 1993-02-22 | 2000-10-03 | Heartport, Inc. | Minimally-invasive devices and methods for treatment of congestive heart failure |
US5728151A (en) * | 1993-02-22 | 1998-03-17 | Heartport, Inc. | Intercostal access devices for less-invasive cardiovascular surgery |
DE4306277C2 (en) | 1993-03-01 | 2000-11-02 | Leibinger Gmbh | Operation marking tool |
DE4317752C2 (en) * | 1993-05-27 | 1997-10-16 | Peter Dr Feindt | Device for supporting cardiac function |
US6258021B1 (en) | 1993-06-17 | 2001-07-10 | Peter J. Wilk | Intrapericardial assist method |
US5800334A (en) * | 1993-06-17 | 1998-09-01 | Wilk; Peter J. | Intrapericardial assist device and associated 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 |
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 |
US6776754B1 (en) | 2000-10-04 | 2004-08-17 | Wilk Patent Development Corporation | Method for closing off lower portion of heart ventricle |
US6155968A (en) | 1998-07-23 | 2000-12-05 | Wilk; Peter J. | Method and device for improving cardiac function |
FR2708458B1 (en) * | 1993-08-03 | 1995-09-15 | Seguin Jacques | Prosthetic ring for cardiac surgery. |
US5450860A (en) * | 1993-08-31 | 1995-09-19 | W. L. Gore & Associates, Inc. | Device for tissue repair and method for employing same |
CA2181045C (en) * | 1993-12-17 | 2004-08-31 | John H. Stevens | 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 |
US5445600A (en) * | 1994-04-29 | 1995-08-29 | Abdulla; Ra-Id | Flow control systemic to pulmonary arterial shunt |
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 |
US5593435A (en) * | 1994-07-29 | 1997-01-14 | Baxter International Inc. | Distensible annuloplasty ring for surgical remodelling of an atrioventricular valve and nonsurgical method for post-implantation distension thereof to accommodate patient growth |
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 |
US5749839A (en) * | 1994-08-18 | 1998-05-12 | Duke University | Direct mechanical bi-ventricular cardiac assist device |
DE29500381U1 (en) | 1994-08-24 | 1995-07-20 | Schneidt Bernhard Ing Grad | Device for closing a duct, in particular the ductus arteriosus |
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 |
IL115680A (en) * | 1994-10-21 | 1999-03-12 | St Jude Medical | Rotatable cuff assembly for a heart valve prosthesis |
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 |
US5840059A (en) * | 1995-06-07 | 1998-11-24 | Cardiogenesis Corporation | Therapeutic and diagnostic agent delivery |
US6132438A (en) * | 1995-06-07 | 2000-10-17 | Ep Technologies, Inc. | Devices for installing stasis reducing means in body tissue |
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 |
US5716399A (en) * | 1995-10-06 | 1998-02-10 | Cardiomend Llc | Methods of heart valve repair |
DE19538796C2 (en) | 1995-10-18 | 1999-09-23 | Fraunhofer Ges Forschung | Device for supporting the heart function with elastic filling chambers |
AU720907B2 (en) * | 1995-12-01 | 2000-06-15 | Medtronic, Inc. | Annuloplasty prosthesis |
US6520904B1 (en) * | 1996-01-02 | 2003-02-18 | The University Of Cincinnati | Device and method for restructuring heart chamber geometry |
US6592619B2 (en) * | 1996-01-02 | 2003-07-15 | University Of Cincinnati | Heart wall actuation device for the natural heart |
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 |
EP0792621A1 (en) | 1996-02-29 | 1997-09-03 | Munir Dr. Uwaydah | Cannulated clamp |
US6814700B1 (en) * | 1996-03-04 | 2004-11-09 | Heartport, Inc. | Soft tissue retractor and method for providing surgical access |
US5800478A (en) * | 1996-03-07 | 1998-09-01 | Light Sciences Limited Partnership | Flexible microcircuits for internal light therapy |
US5853422A (en) * | 1996-03-22 | 1998-12-29 | Scimed Life Systems, Inc. | Apparatus and method for closing a septal defect |
US5738649A (en) * | 1996-04-16 | 1998-04-14 | Cardeon Corporation | Peripheral entry biventricular catheter system for providing access to the heart for cardiopulmonary surgery or for prolonged circulatory support of the heart |
US6488706B1 (en) | 1996-05-08 | 2002-12-03 | Carag Ag | Device for plugging an opening such as in a wall of a hollow or tubular organ |
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 |
EP0930857B1 (en) * | 1996-09-13 | 2003-05-02 | Medtronic, Inc. | Prosthetic heart valve with suturing member having non-uniform radial width |
US5655548A (en) * | 1996-09-16 | 1997-08-12 | Circulation, Inc. | Method for treatment of ischemic heart disease by providing transvenous myocardial perfusion |
US5800531A (en) | 1996-09-30 | 1998-09-01 | Baxter International Inc. | Bioprosthetic heart valve implantation device |
US6123662A (en) | 1998-07-13 | 2000-09-26 | Acorn Cardiovascular, Inc. | Cardiac disease treatment and device |
US5702343A (en) | 1996-10-02 | 1997-12-30 | Acorn Medical, Inc. | Cardiac reinforcement device |
WO1998017347A1 (en) | 1996-10-18 | 1998-04-30 | Cardio Technologies, Inc. | Method and apparatus for assisting a heart |
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 |
DE29619294U1 (en) * | 1996-11-07 | 1997-07-17 | Caic Pero | Heart cuff |
US5865749A (en) * | 1996-11-07 | 1999-02-02 | Data Sciences International, Inc. | Blood flow meter apparatus and method of use |
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 |
US7883539B2 (en) | 1997-01-02 | 2011-02-08 | Edwards Lifesciences Llc | Heart wall tension reduction apparatus and method |
US6050936A (en) * | 1997-01-02 | 2000-04-18 | Myocor, Inc. | Heart wall tension reduction apparatus |
US6406420B1 (en) * | 1997-01-02 | 2002-06-18 | Myocor, Inc. | Methods and devices for improving cardiac function in hearts |
US6045497A (en) | 1997-01-02 | 2000-04-04 | 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 |
US5961440A (en) * | 1997-01-02 | 1999-10-05 | 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 |
US6077214A (en) | 1998-07-29 | 2000-06-20 | Myocor, Inc. | Stress reduction apparatus and method |
US5961539A (en) | 1997-01-17 | 1999-10-05 | Segmed, Inc. | Method and apparatus for sizing, stabilizing and/or reducing the circumference of an anatomical structure |
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 |
US5776189A (en) | 1997-03-05 | 1998-07-07 | Khalid; Naqeeb | Cardiac valvular support prosthesis |
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 |
US6090096A (en) * | 1997-04-23 | 2000-07-18 | Heartport, Inc. | Antegrade cardioplegia catheter and method |
US6432059B2 (en) | 1997-06-12 | 2002-08-13 | The Research Foundation Of State University Of New York | Method and apparatus for more precisely determined mean left atrial pressure |
JP2002504841A (en) | 1997-06-21 | 2002-02-12 | ハインドル・ハンス | A bag surrounding at least part of the heart |
DE29824017U1 (en) | 1997-06-21 | 2000-05-25 | Haindl Hans | Pouch for at least partially enclosing 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 |
US20030105519A1 (en) | 1997-09-04 | 2003-06-05 | Roland Fasol | 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 |
US6019722A (en) | 1997-09-17 | 2000-02-01 | Guidant Corporation | Device to permit offpump beating heart coronary bypass surgery |
US6338712B2 (en) | 1997-09-17 | 2002-01-15 | Origin Medsystems, Inc. | Device to permit offpump beating heart coronary bypass surgery |
US6361545B1 (en) | 1997-09-26 | 2002-03-26 | Cardeon Corporation | Perfusion filter catheter |
US6086532A (en) | 1997-09-26 | 2000-07-11 | Ep Technologies, Inc. | Systems for recording use of structures deployed in association with heart tissue |
CA2308426A1 (en) | 1997-11-03 | 1999-05-14 | William A. Easterbrook, Iii | Method and apparatus for assisting a heart to pump blood |
US6113636A (en) | 1997-11-20 | 2000-09-05 | St. Jude Medical, Inc. | Medical article with adhered antimicrobial metal |
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 |
ES2293473T3 (en) | 1998-02-05 | 2008-03-16 | Biosense Webster, Inc. | INTRACARDIAC ADMINISTRATION OF FARMACO. |
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 |
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 |
US6221104B1 (en) | 1998-05-01 | 2001-04-24 | Cor Restore, Inc. | Anterior and interior segment cardiac 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 |
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 |
US5967990A (en) | 1998-08-13 | 1999-10-19 | President And Fellows Of Harvard College | Surgical probe comprising visible markings on an elastic membrane |
US6251061B1 (en) | 1998-09-09 | 2001-06-26 | Scimed Life Systems, Inc. | Cardiac assist device using field controlled fluid |
US6113536A (en) | 1998-09-30 | 2000-09-05 | A-Med Systems, Inc. | Device and method of attaching a blood pump and tubes to a surgical retractor |
DE19947885B4 (en) | 1998-10-05 | 2009-04-09 | Cardiothoracic Systems, Inc., Cupertino | Device for positioning the heart during cardiac surgery while maintaining cardiac output |
US6685627B2 (en) | 1998-10-09 | 2004-02-03 | Swaminathan Jayaraman | Modification of properties and geometry of heart tissue to influence heart function |
US6360749B1 (en) | 1998-10-09 | 2002-03-26 | Swaminathan Jayaraman | Modification of properties and geometry of heart tissue to influence heart 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 |
US6230714B1 (en) | 1998-11-18 | 2001-05-15 | Acorn Cardiovascular, Inc. | Cardiac constraint with prior venus occlusion methods |
US6432039B1 (en) | 1998-12-21 | 2002-08-13 | Corset, Inc. | Methods and apparatus for reinforcement of the heart ventricles |
US6155972A (en) | 1999-02-02 | 2000-12-05 | Acorn Cardiovascular, Inc. | Cardiac constraint jacket construction |
US6701929B2 (en) | 1999-03-03 | 2004-03-09 | Hany Hussein | Device and method for treatment of congestive heart failure |
US6695768B1 (en) | 1999-03-30 | 2004-02-24 | Robert A. Levine | Adjustable periventricular ring/ring like device/method for control of ischemic mitral regurgitation and congestive heart disease |
US7563267B2 (en) | 1999-04-09 | 2009-07-21 | Evalve, Inc. | Fixation device and methods for engaging tissue |
AU770243B2 (en) | 1999-04-09 | 2004-02-19 | 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 |
US6331157B2 (en) | 1999-04-15 | 2001-12-18 | Heartport, Inc. | Apparatus and methods for off-pump cardiac surgery |
US6994669B1 (en) | 1999-04-15 | 2006-02-07 | Heartport, Inc. | Apparatus and method for cardiac surgery |
US6183512B1 (en) | 1999-04-16 | 2001-02-06 | Edwards Lifesciences Corporation | Flexible annuloplasty system |
US6577902B1 (en) | 1999-04-16 | 2003-06-10 | Tony R. Brown | Device for shaping infarcted heart tissue and method of using the device |
US6231602B1 (en) | 1999-04-16 | 2001-05-15 | Edwards Lifesciences Corporation | Aortic annuloplasty ring |
US6260820B1 (en) | 1999-05-21 | 2001-07-17 | Nordstrom Valves, Inc. | Valve with rotatable valve member and method for forming same |
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 |
US6258023B1 (en) | 1999-07-08 | 2001-07-10 | Chase Medical, Inc. | Device and method for isolating a surface of a beating heart during surgery |
US7264587B2 (en) | 1999-08-10 | 2007-09-04 | Origin Medsystems, Inc. | Endoscopic subxiphoid surgical procedures |
US6231561B1 (en) | 1999-09-20 | 2001-05-15 | Appriva Medical, Inc. | Method and apparatus for closing a body lumen |
US6179791B1 (en) | 1999-09-21 | 2001-01-30 | Acorn Cardiovascular, Inc. | Device for heart measurement |
US6174279B1 (en) | 1999-09-21 | 2001-01-16 | Acorn Cardiovascular, Inc. | Cardiac constraint with tension indicator |
US6193648B1 (en) | 1999-09-21 | 2001-02-27 | Acorn Cardiovascular, Inc. | Cardiac constraint with draw string tensioning |
US6312447B1 (en) | 1999-10-13 | 2001-11-06 | The General Hospital Corporation | Devices and methods for percutaneous mitral valve repair |
US6626930B1 (en) | 1999-10-21 | 2003-09-30 | Edwards Lifesciences Corporation | Minimally invasive mitral valve repair method and apparatus |
US20010041914A1 (en) | 1999-11-22 | 2001-11-15 | Frazier Andrew G.C. | Tissue patch deployment catheter |
US6702732B1 (en) | 1999-12-22 | 2004-03-09 | Paracor Surgical, Inc. | Expandable cardiac harness for treating congestive heart failure |
US6409759B1 (en) | 1999-12-30 | 2002-06-25 | St. Jude Medical, Inc. | Harvested tissue heart valve with sewing rim |
US6293906B1 (en) | 2000-01-14 | 2001-09-25 | Acorn Cardiovascular, Inc. | Delivery of cardiac constraint jacket |
US6769434B2 (en) | 2000-06-30 | 2004-08-03 | Viacor, Inc. | Method and apparatus for performing a procedure on a cardiac valve |
US6989028B2 (en) | 2000-01-31 | 2006-01-24 | Edwards Lifesciences Ag | Medical system and method for remodeling an extravascular tissue structure |
US6402781B1 (en) | 2000-01-31 | 2002-06-11 | Mitralife | Percutaneous mitral annuloplasty and cardiac reinforcement |
US7296577B2 (en) | 2000-01-31 | 2007-11-20 | Edwards Lifescience Ag | Transluminal mitral annuloplasty with active anchoring |
US6406422B1 (en) | 2000-03-02 | 2002-06-18 | Levram Medical Devices, Ltd. | Ventricular-assist method and apparatus |
EP1261294B1 (en) | 2000-03-10 | 2006-11-29 | Paracor Medical, Inc. | Expandable cardiac harness for treating 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 |
US6454799B1 (en) | 2000-04-06 | 2002-09-24 | Edwards Lifesciences Corporation | Minimally-invasive heart valves and methods of use |
ITPC20000013A1 (en) | 2000-04-13 | 2000-07-13 | Paolo Ferrazzi | INTROVENTRICULAR DEVICE AND RELATED METHOD FOR THE TREATMENT AND CORRECTION OF MYOCARDIOPATHIES. |
US7083628B2 (en) | 2002-09-03 | 2006-08-01 | Edwards Lifesciences Corporation | Single catheter mitral valve repair device and method for use |
US6425856B1 (en) | 2000-05-10 | 2002-07-30 | Acorn Cardiovascular, Inc. | Cardiac disease treatment and device |
US20030023132A1 (en) | 2000-05-31 | 2003-01-30 | Melvin David B. | Cyclic device for restructuring heart chamber geometry |
US6730016B1 (en) | 2000-06-12 | 2004-05-04 | Acorn Cardiovascular, Inc. | Cardiac disease treatment and device |
US6482146B1 (en) | 2000-06-13 | 2002-11-19 | Acorn Cardiovascular, Inc. | Cardiac disease treatment and device |
US6951534B2 (en) | 2000-06-13 | 2005-10-04 | Acorn Cardiovascular, Inc. | Cardiac support device |
US6702826B2 (en) | 2000-06-23 | 2004-03-09 | Viacor, Inc. | Automated annular plication for mitral valve repair |
US6343605B1 (en) | 2000-08-08 | 2002-02-05 | Scimed Life Systems, Inc. | Percutaneous transluminal myocardial implantation device and method |
SE0002878D0 (en) | 2000-08-11 | 2000-08-11 | Kimblad Ola | Device and method of treatment of atrioventricular regurgitation |
US6572533B1 (en) | 2000-08-17 | 2003-06-03 | Acorn Cardiovascular, Inc. | Cardiac disease treatment and device |
WO2004030570A2 (en) | 2002-10-01 | 2004-04-15 | Ample Medical, Inc. | Devices for retaining native heart valve leaflet |
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 |
US6673009B1 (en) | 2000-11-08 | 2004-01-06 | Acorn Cardiovascular, Inc. | Adjustment clamp |
US6602182B1 (en) | 2000-11-28 | 2003-08-05 | Abiomed, Inc. | Cardiac assistance systems having multiple fluid plenums |
US6616596B1 (en) | 2000-11-28 | 2003-09-09 | Abiomed, Inc. | Cardiac assistance systems having multiple layers of inflatable elements |
US6755779B2 (en) | 2000-12-01 | 2004-06-29 | Acorn Cardiovascular, Inc. | Apparatus and method for delivery of cardiac constraint jacket |
US6564094B2 (en) | 2000-12-22 | 2003-05-13 | Acorn Cardiovascular, Inc. | Cardiac disease treatment and device |
US7591826B2 (en) | 2000-12-28 | 2009-09-22 | Cardiac Dimensions, Inc. | Device implantable in the coronary sinus to provide mitral valve therapy |
US6786898B2 (en) | 2003-01-15 | 2004-09-07 | Medtronic, Inc. | Methods and tools for accessing an anatomic space |
US6810882B2 (en) | 2001-01-30 | 2004-11-02 | Ev3 Santa Rosa, Inc. | Transluminal mitral annuloplasty |
CA2437824C (en) | 2001-02-05 | 2008-09-23 | Viacor, Inc. | Apparatus and method for reducing mitral regurgitation |
AU2002240288B2 (en) | 2001-02-05 | 2006-05-18 | Viacor, Inc. | Method and apparatus for improving mitral valve function |
US6575921B2 (en) | 2001-02-09 | 2003-06-10 | Acorn Cardiovascular, Inc. | Device for heart measurement |
US6702763B2 (en) | 2001-02-28 | 2004-03-09 | Chase Medical, L.P. | Sizing apparatus and method for use during ventricular restoration |
AU2002327224A1 (en) | 2001-03-05 | 2002-12-09 | Viacor, Incorporated | Apparatus and method for reducing mitral regurgitation |
US6733525B2 (en) | 2001-03-23 | 2004-05-11 | Edwards Lifesciences Corporation | Rolled minimally-invasive heart valves and methods of use |
CA2441886C (en) | 2001-03-23 | 2009-07-21 | Viacor, Incorporated | Method and apparatus for reducing mitral regurgitation |
US7186264B2 (en) | 2001-03-29 | 2007-03-06 | Viacor, Inc. | Method and apparatus for improving mitral valve function |
US6619291B2 (en) | 2001-04-24 | 2003-09-16 | Edwin J. Hlavka | Method and apparatus for catheter-based annuloplasty |
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 |
US7526112B2 (en) | 2001-04-30 | 2009-04-28 | Chase Medical, L.P. | System and method for facilitating cardiac intervention |
US7327862B2 (en) | 2001-04-30 | 2008-02-05 | Chase Medical, L.P. | System and method for facilitating cardiac intervention |
US6800090B2 (en) | 2001-05-14 | 2004-10-05 | Cardiac Dimensions, Inc. | Mitral valve therapy device, system and method |
US6676702B2 (en) | 2001-05-14 | 2004-01-13 | Cardiac Dimensions, Inc. | Mitral valve therapy assembly and method |
ITMI20011012A1 (en) | 2001-05-17 | 2002-11-17 | Ottavio Alfieri | ANNULAR PROSTHESIS FOR MITRAL VALVE |
US6626821B1 (en) | 2001-05-22 | 2003-09-30 | Abiomed, Inc. | Flow-balanced cardiac wrap |
US20040064014A1 (en) | 2001-05-31 | 2004-04-01 | Melvin David B. | Devices and methods for assisting natural heart function |
WO2002102237A2 (en) | 2001-06-15 | 2002-12-27 | The Cleveland Clinic Foundation | Tissue engineered mitral valve chrodae and methods of making and using same |
US6726716B2 (en) | 2001-08-24 | 2004-04-27 | Edwards Lifesciences Corporation | Self-molding annuloplasty ring |
WO2003022131A2 (en) | 2001-09-07 | 2003-03-20 | Mardil, Inc. | Method and apparatus for external heart stabilization |
WO2003022176A2 (en) | 2001-09-10 | 2003-03-20 | Paracor Medical, Inc. | Cardiac harness |
US6685620B2 (en) | 2001-09-25 | 2004-02-03 | The Foundry Inc. | Ventricular infarct assist device and methods for using it |
US7144363B2 (en) | 2001-10-16 | 2006-12-05 | Extensia Medical, Inc. | Systems for heart treatment |
US7052487B2 (en) | 2001-10-26 | 2006-05-30 | Cohn William E | Method and apparatus for reducing mitral regurgitation |
US7311729B2 (en) | 2002-01-30 | 2007-12-25 | Cardiac Dimensions, Inc. | Device and method for modifying the shape of a body organ |
US6824562B2 (en) | 2002-05-08 | 2004-11-30 | Cardiac Dimensions, Inc. | Body lumen device anchor, device and assembly |
US6908478B2 (en) | 2001-12-05 | 2005-06-21 | Cardiac Dimensions, Inc. | Anchor and pull mitral valve device and method |
US7179282B2 (en) | 2001-12-05 | 2007-02-20 | Cardiac Dimensions, Inc. | Device and method for modifying the shape of a body organ |
US6976995B2 (en) | 2002-01-30 | 2005-12-20 | Cardiac Dimensions, Inc. | Fixed length anchor and pull mitral valve device and method |
US6793673B2 (en) | 2002-12-26 | 2004-09-21 | Cardiac Dimensions, Inc. | System and method to effect mitral valve annulus of a heart |
US6740107B2 (en) | 2001-12-19 | 2004-05-25 | Trimedyne, Inc. | Device for treatment of atrioventricular valve regurgitation |
US20030120340A1 (en) | 2001-12-26 | 2003-06-26 | Jan Liska | Mitral and tricuspid valve repair |
US6764510B2 (en) | 2002-01-09 | 2004-07-20 | Myocor, Inc. | Devices and methods for heart valve treatment |
US6960229B2 (en) | 2002-01-30 | 2005-11-01 | Cardiac Dimensions, Inc. | Device and method for modifying the shape of a body organ |
US7125420B2 (en) | 2002-02-05 | 2006-10-24 | Viacor, Inc. | Method and apparatus for improving mitral valve function |
US7004958B2 (en) | 2002-03-06 | 2006-02-28 | Cardiac Dimensions, Inc. | Transvenous staples, assembly and method for mitral valve repair |
US6797001B2 (en) | 2002-03-11 | 2004-09-28 | Cardiac Dimensions, Inc. | Device, assembly and method for mitral valve repair |
US20030229260A1 (en) | 2002-06-05 | 2003-12-11 | Acorn Cardiovascular, Inc. | Cardiac support device with tension indicator |
US20030229261A1 (en) | 2002-06-06 | 2003-12-11 | Acorn Cardiovascular, Inc. | Cardiac support devices and methods of producing same |
US6682475B2 (en) | 2002-06-11 | 2004-01-27 | Acorn Cardiovascular, Inc. | Tension indicator for cardiac support device and method therefore |
US20030233022A1 (en) | 2002-06-12 | 2003-12-18 | Vidlund Robert M. | Devices and methods for heart valve treatment |
US8287555B2 (en) | 2003-02-06 | 2012-10-16 | Guided Delivery Systems, Inc. | Devices and methods for heart valve repair |
AU2003245507A1 (en) | 2002-06-13 | 2003-12-31 | Guided Delivery Systems, Inc. | 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 |
US20040015041A1 (en) | 2002-07-18 | 2004-01-22 | The University Of Cincinnati | Protective sheath apparatus and method for use with a heart wall actuation system for the natural heart |
US20040059180A1 (en) | 2002-09-23 | 2004-03-25 | The University Of Cincinnati | Basal mounting cushion frame component to facilitate extrinsic heart wall actuation |
US20040015040A1 (en) | 2002-07-18 | 2004-01-22 | The University Of Cincinnati | Flexible, torsionable cardiac framework for heart wall actuation of the natural heart |
US8172856B2 (en) | 2002-08-02 | 2012-05-08 | Cedars-Sinai Medical Center | Methods and apparatus for atrioventricular valve repair |
EP1534146B1 (en) | 2002-08-13 | 2008-01-23 | The General Hospital Corporation | Cardiac devices for percutaneous repair of atrioventricular valves |
US6988982B2 (en) | 2002-08-19 | 2006-01-24 | Cardioenergetics | Heart wall actuation system for the natural heart with shape limiting elements |
EP1562522B1 (en) | 2002-10-01 | 2008-12-31 | Ample Medical, Inc. | Devices and systems for reshaping a heart valve annulus |
US7591847B2 (en) | 2002-10-10 | 2009-09-22 | The Cleveland Clinic Foundation | Stentless bioprosthetic valve having chordae for replacing a mitral valve |
US20040133062A1 (en) | 2002-10-11 | 2004-07-08 | Suresh Pai | Minimally invasive cardiac force transfer structures |
BR0315392A (en) | 2002-10-21 | 2005-08-23 | Mitralign Inc | Incrementing catheters and methods of performing annuloplasty |
US7112219B2 (en) | 2002-11-12 | 2006-09-26 | Myocor, Inc. | Devices and methods for heart valve treatment |
US7247134B2 (en) | 2002-11-12 | 2007-07-24 | Myocor, Inc. | Devices and methods for heart valve treatment |
US7485143B2 (en) | 2002-11-15 | 2009-02-03 | Abbott Cardiovascular Systems Inc. | Apparatuses and methods for heart valve repair |
US20040098116A1 (en) | 2002-11-15 | 2004-05-20 | Callas Peter L. | Valve annulus constriction apparatus and method |
US7316708B2 (en) | 2002-12-05 | 2008-01-08 | Cardiac Dimensions, Inc. | Medical device delivery system |
US20040133240A1 (en) | 2003-01-07 | 2004-07-08 | Cardiac Dimensions, Inc. | Electrotherapy system, device, and method for treatment of cardiac valve dysfunction |
US6997950B2 (en) | 2003-01-16 | 2006-02-14 | Chawla Surendra K | Valve repair device |
US20040158321A1 (en) | 2003-02-12 | 2004-08-12 | Cardiac Dimensions, Inc. | Method of implanting a mitral valve therapy device |
US7381210B2 (en) | 2003-03-14 | 2008-06-03 | Edwards Lifesciences Corporation | Mitral valve repair system and method for use |
EP1608297A2 (en) | 2003-03-18 | 2005-12-28 | St. Jude Medical, Inc. | Body tissue remodeling apparatus |
-
1997
- 1997-01-02 US US08/778,277 patent/US6050936A/en not_active Expired - Lifetime
- 1997-12-31 WO PCT/US1997/024116 patent/WO1998029041A1/en active IP Right Grant
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- 1999-01-04 US US09/224,348 patent/US6059715A/en not_active Expired - Lifetime
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- 2000-01-28 US US09/492,777 patent/US6162168A/en not_active Expired - Lifetime
- 2000-04-04 US US09/543,155 patent/US6165120A/en not_active Expired - Lifetime
- 2000-10-27 US US09/697,596 patent/US6332863B1/en not_active Expired - Lifetime
- 2000-10-27 US US09/697,597 patent/US6332864B1/en not_active Expired - Lifetime
-
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- 2001-11-02 US US09/985,361 patent/US6589160B2/en not_active Expired - Lifetime
- 2001-11-02 US US09/985,362 patent/US6514194B2/en not_active Expired - Lifetime
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- 2002-01-23 US US09/985,361 patent/US20020068849A1/en active Granted
- 2002-02-14 US US10/073,968 patent/US20020077524A1/en not_active Abandoned
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- 2004-02-17 US US10/778,176 patent/US7695425B2/en not_active Expired - Fee Related
- 2004-12-24 JP JP2004373661A patent/JP4177324B2/en not_active Expired - Lifetime
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- 2007-11-28 JP JP2007308058A patent/JP4339909B2/en not_active Expired - Lifetime
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- 2008-12-02 US US12/314,004 patent/US20090137863A1/en not_active Abandoned
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