Source: https://patents.google.com/patent/WO1999044534A1/en
Timestamp: 2018-03-23 09:45:44
Document Index: 506135760

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WO1999044534A1 - Device and method for restructuring heart chamber geometry - Google Patents
WO1999044534A1
WO1999044534A1 PCT/US1999/004978 US9904978W WO1999044534A1 WO 1999044534 A1 WO1999044534 A1 WO 1999044534A1 US 9904978 W US9904978 W US 9904978W WO 1999044534 A1 WO1999044534 A1 WO 1999044534A1
PCT/US1999/004978
David B. M. D. Melvin
A static device for use with the heart that has a plurality of members configured to be positioned adjacent the epicardial surface of the heart. The members are joined by at least one connector wherein the members are fixed in a spatial or spaced relationship relative to each other such that a portion of the heart wall is displaced inwardly. The member(s) can be configured in a rectangular shape, and preferably include(s) an inner surface having a curved configuration. In one embodiment, the device can have first and second members that are positioned in a spaced relationship relative to each other about 180 degrees apart. The first member is configured to be positioned adjacent the anterolateral surface of the chamber, and the second member configured to be positioned adjacent the posteromedial surface of the chamber.
The natural heart, and specifically, the cardiac muscle tissue of the natural heart (e.g., myocardium) can fail for various reasons to a point where the natural heart cannot provide sufficient circulation of blood for a body so that life can be maintained. More specifically, the heart and its chambers can become enlarged for a variety of causes and/or reasons, including viral disease, idiopathic disease, valvular disease (mitral, aortic and/or both), ischemic disease, Chagas' disease and so forth. As the heart and its chambers enlarge, tension of the walls of the heart's chambers increase and thus, the heart must develop more wall tensile stress to generate the needed pressure for pumping blood through the circulatory system. As a solution for the enlarged natural heart, attempts have been made in the past to provide a treatment to maintain circulation. One such approach has been to replace the existing natural heart in a patient with an artificial heart or a ventricular assist device. In using artificial hearts and/or assist devices, a particular problem stems from the fact that the materials used for the interior lining of the chambers of an artificial heart are in direct contact with the circulating blood, which can enhance undesirable clotting of the blood, build up of calcium, or otherwise inhibit the blood's normal function. Hence, thromboembolism and hemolysis could occur with greater ease. Additionally, the lining of an artificial heart or a ventricular assist device can crack, which inhibits performance, even if the crack is at a microscopic level. Moreover, these devices must be powered by a source which can be cumbersome and/or external to the body. Drawbacks have limited use of these devices to applications having too brief a time period to provide a real lasting benefit.
An alternative procedure is to transplant a heard from another human or animal into a patient. The transplant procedure requires removing an existing organ (i.e., the natural heart) for substitution with another organ (i.e., another natural heart) from another human, or potentially, from an animal. Before replacing an existing organ with another, the substitute organ must be "matched" to the recipient, which can be, at best, difficult and time consuming to accomplish. Furthermore, even if the transplanted organ matches the recipient, a risk exists that the recipient's body will reject the transplanted organ and attack it as a foreign object. Moreover, the number of potential donor hearts is far less than the number of patients in need of a transplant. Although use of animal hearts would lessen the problem with fewer donors than recipients, there is an enhanced concern with rejection of the animal heart.
In an effort to use the existing natural heart of a patient, other attempts have been made to reduce wall tension of the heart by removing a portion of the heart wall, such as a portion of the left ventricle in a partial left ventriculectomy procedure (the Batista procedure). A wedge-shaped portion of the ventricular muscle has been removed, which extends from the apex to the base of the heart. By reducing the chamber's volume, and thus its radius, the tension of the chamber's wall is reduced as well. There are, however, several drawbacks with such a procedure. First, a valve (i.e., the mitral valve) may need to be repaired or replaced depending on the amount of cardiac muscle tissue to be removed. Second, the procedure is invasive and traumatic to the patient. As such, blood loss and bleeding can be substantial during and after the procedure. Moreover, as can be appreciated by those skilled in the industry, the procedure is not reversible. Another device developed for use with an existing heart for sustaining the circulatory function of a living being and the pumping action of the natural heart is an external bypass system, such as a cardiopulmonary (heart-lung) machine. Typically, bypass systems of this type are complex and large, and, as such, are limited to short term use in an operating room during surgery, or to maintaining the circulation of a patient while awaiting receipt of a transplant heart. The size and complexity effectively prohibit use of bypass systems as a long term solution, as they are rarely even portable devices. Furthermore, long term use of these systems can damage the blood cells and blood borne products, resulting in post surgical complications such as bleeding, thromboembolism function, and increased risk of infection. Medicines, such as vasodilators, have been used to assist in treating cardiomyopathies. For example, digoxin can increase the contractibility of the heart, and thereby enhances emptying of the chambers during systolic pumping. On the other hand, some medicines, such as beta blocking drugs, which decrease the size of the chamber of the heart, also decrease the contractibility of the heart. Other types of medicines, such as angiotensin-converting enzyme inhibitors (e.g., enalopril) can help reduce the tendency of the heart to dilate under the increased diastolic pressure experienced when the contractibility of the heart muscle decreases. Many of these medicines have side effects, such as excessive lowering of blood pressure, which make them undesirable for long term therapy.
It is still a further another object of the present invention to provide a device and method for treating cardiomyopathies that maintains the stroke volume of the heart. Another object of the present invention is to provide a device and method for treating cardiomyopathies that supports and maintains the competence of the heart valves so that the heart valves can function as intended.
The members) can be configured in a rectangular shape, and preferably includes an inner surface having a curved configuration. In one embodiment, the device can have first and second member that are positioned in a spaced relationship relative to each other about 180 degrees apart. The first member is configured to be positioned adjacent the anterolateral surface of the chamber, and the second member configured to be positioned adjacent the posteromedial surface of the chamber. In an alternative embodiment of the device having first, second and third members, the first, second, and third members are positioned in a spaced relationship relative to each other about 120 degrees apart. The first member is configured to be positioned adjacent the anteroseptal portion of the chamber, the second member is configured to be positioned adjacent the posteroseptal portion of the chamber, and a third member is configured to be positioned adjacent the posterolateral portion of the chamber.
The device also may include a pad adjacent the inner surface, and preferably interposed between the member and endocardial surface. The pad can be made of low durometer solid polymer or plastic or, alternatively, the pad could be a gel-filled or fluid- filled cushion. The connector of the present invention can also include a chord, such as a heavy braided polymer impregnated polyester suture core with a polyester sleeve, or a heavy monofilament polypropylene or an expanded polytetrafluoroethylene (PTFE, such as the brand Gortex® by W.L. Gore & Co.) suture, which can traverse the heart tissue and/or cavity. The connector of the present invention can also include a generally rigid pin or rod that is configured to be insertable through, and connect with, the members.
Fig. 1 partial frontal anterior view of an exemplar natural heart; Fig. 2 vertical cross sectional view of an exemplar natural heart and blood vessels leading to and from the natural heart;
Fig. 3 is a horizontal cross sectional view of an unrestrained left ventricle of the natural heart; Fig. 4 is a perspective view of a device made in accordance with the present invention and positioned on the left ventricle;
Fig. 5 is a cross sectional view of the device taken along line 5-5 in Fig.4;
Fig. 6 is a perspective view of an alternative embodiment of a device made in accordance with the present invention and positioned on the left ventricle; Fig. 7A is a partial horizontal cross sectional view of a pad interposed between the epicardial surface and the member while the heart is at rest;
Fig.8 is a vertical sectional view of an alternative embodiment of a device made in accordance with the present invention and positioned on the left ventricle;
Fig. 11 A is a perspective view of the embodiment of Figs. 9-10 when the device is undeformed;
Fig. 1 IB is a perspective view of the embodiment illustrated in Fig. 11 A when the device has been twisted due to ventricular contraction;
8 Fig. 13 is a vertical cross sectional view of another embodiment of an auxiliary fastener made in accordance with the present invention.
Referring now to the figures in detail wherein like numerals indicate the same elements throughout the views, an exemplary natural heart, generally indicated in Figures
1 and 2 as 10, has a lower portion comprising two chambers, namely a left ventricle 12 and a right ventricle 14, which function primarily to supply the main force that propels blood through the circulatory system, namely the pulmonary circulatory system, which propels blood to and from the lungs, and the peripheral circulatory system, which propels blood through the remainder of the body. A natural heart 10 also includes an upper portion having two chambers, a left atrium 16 and a right atrium 18, which primarily serve as an entiyway to the left and right ventricles 12 and 14, respectively, and assist in moving blood into the left and right ventricles 12 or 14. The interventricular wall 40 of cardiac tissue 32 separates
the left and right ventricles 12 and 14, and the atrioventricular wall 42 of cardiac tissue 32 separates the lower ventricular region from the upper atrium region.
Generally, the left and right ventricles 12 and 14, respectively, each has a cavity 13 and 15, respectively, that is in fluid communication with cavities 17 and 19, respectively, of the atria (e.g., 16 and 18) through an atrioventricular valve 50 (which are each illustrated as closed in Fig.2). More specifically, the left ventricle cavity 13 is in fluid communication with the left atrium cavity 17 through the mitral valve 52, while the right ventricle cavity
15 is in fluid communication with the right atrium cavity 19 through the tricuspid valve 54. Generally, the cavities of the ventricles (e.g., 13 and 15) are each in fluid communication with the circulatory system (i.e., the pulmonary and peripheral circulatory systems) through a semilunar valve 44 (which are each illustrated as opened in Fig. 2). More specifically, the left ventricle cavity 13 is in fluid communication with the aorta 26 of the peripheral circulatory system through the aortic valve 46, while the right ventricle cavity 15 is in fluid communication with the pulmonary artery 28 of the pulmonary circulatory system through the pulmonic valve 48.
Blood is returned to the heart 10 through the atria (e.g., 16 and 18). More specifically, the superior vena cava 22 and inferior vena cava 24 are in fluid communication and deliver blood, as it returns from the peripheral circulatory system, to the right atrium
18 and its cavity 19. The pulmonary vein 30 is in fluid communication and delivers blood, as it returns from the pulmonary circulatory system, to the left atrium 16, and its cavity 17.
The heart 10 is enclosed in the thoracic cavity within a double walled sac commonly referred to as the pericardium. Its inner layer is the visceral pericardium or epicardium, and its outer layer is the parietal pericardium. The structure heart 10 is generally made up of, among other materials, cardiac muscle or tissue 32, which has an exterior surface commonly known as the epicardial surface 34 and an interior surface, or endocardial surface
38, that generally defines the cavities (e.g., ventricular cavities 13 and 15, respectively, and atrial cavities 17 and 19, respectively). Coronary arteries 36 on the epicardial surface 34 of the heart 10 provide blood and nourishment (e.g., oxygen) to the heart 10 and its cardiac tissue 32.
By way of a non-limiting example, the present invention will be discussed in terms of embodiments that are used to primarily assist in the restructuring or reconfiguring, and/or operation of the left ventricle (e.g., 12) of the natural heart 10, however, it is noted that the
10 present invention can also be used to assist in the restructuring or reconfiguring, and/or operation of other portions of the natural heart 10, such as either atria (16 and/or 18), or the right ventricle (e.g., 14) of the natural heart 10.
Turning now to Fig. 3, the chambers of the heart 10, including the left ventricle 12, is generally shaped as a hollow truncated ellipsoid having, at any circular cross-section perpendicular to its long axis, a center point "C," and a radius "R," extending from center point C, to the endocardial surface 38. The cardiac tissue 32 of the heart 10 has a thickness "w," which is generally the distance between the epicardial surface 34 and the endocardial surface 38. The static device or brace 60 of the present invention exemplified in Figs. 4 and 5 preferably is configured and positioned relative to the natural heart 10 to displace at least two portions of the cardiac tissue 32 inwardly (see, e.g., Fig. 5) from the unrestricted position, as exemplified in Fig. 3. By displacing portions of the cardiac tissue 32 inwardly, the shape of the chamber (e.g., the left ventricle 12) of the heart 10 is generally restructured or reconfigured from a generally hollow truncated ellipsoid (see, e.g., Fig. 3) to a chamber generally shaped as having at least two continuous communicating portions of truncated ellipsoids (see, e.g., Fig.5). In generally reconfiguring or restructuring the heart 10 as such, each of the truncated ellipsoids has an adjusted radius "R2," which is preferably shorter than radius "R,." The device or brace 60 can be static in that it does not actuate or pump the heart 10, but rather, displaces and holds portions of the cardiac tissue 32 in a generally predetermined fixed position as the heart 10 continues to contract (e.g., beat) and pump blood through its chambers and through the body's circulatory system.
11 The device 60 can include at least two members 62 to assist in restraining or restructuring the left ventricle 12 that are preferably spaced about 180 degrees apart adjacent or on the epicardial surface 34 so as to restructure or reconfigure the left ventricle 12 as having the shape of at least two continuous communicating portions of truncated ellipsoids. One of the members 62 can be configured to be positioned adjacent the anterolateral surface of a chamber (e.g., the left ventricle 12) and the other member 62 can be configured to be positioned adjacent the posteromedial surface of a chamber (e.g., the left ventricle 12).
Each member 62 includes a contact or an inner surface 64 that is preferably curved convex outwardly in a longitudinal plane (see, e.g., Fig. 5) and curved convex inwardly in the transverse plane (see, e.g., Fig. 4) so that member 62 is configured to be positioned adjacent or on the epicardial surface 34 whereby intimate contact can be established and maintained, even during the contraction or beating of the heart 10. Member 62, and its inner surface 64, should be configured so that it is tangent to the portion of the epicardial surface 32 where contact is made and so that the cardiac tissue 32 is altered or displaced in a transverse plane, from its unrestructured inwardly convex shape (see, e.g., Fig. 3) to its restructured concave shape (see, e.g., Fig. 5). The inner surface 64 can be provided as a smooth curved surface having lateral portions 67 such that the epicardial surface 34 may slide along the member 62 during contraction and expansion of the heart 10. Members 62 are each preferably made of a light weight, generally rigid material that has as a low bending strain under expected levels of stress so that the material has sufficient wear resistance in use while the heart 10 beats, and maintains its desired shape in use adjacent the heart 10. Illustrative examples of materials which may be employed as member 62 include any biocompatible materials such as metals, including titanium or
12 stainless steel, or as a suitable polymer, including polyacetal or an ultra high molecular weight polyethylene.
Member 62 can be any desired shape, and can vary according to anatomy and the desired application. Preferably, member 62 has rounded edges and is a generally rectangular shaped object with the length extending in the transverse plane or along the longer axis of the chamber (i.e., extending between the basal portion near the atrioventricular groove 43 (see, e.g., Fig. 1) and apical portion 20 of the heart 10). In a preferred embodiment, member 62 can have a length that varies from about 50% to about 100% of the vertical long axis of the chamber (e.g., 12), approximately from about 4 to about 12 cm, and can vary preferably about 80% of the vertical long axis of the chamber
(e.g., 12). Moreover, the member 62 can have a thickness that varies from about 1 mm to about 10 mm, depending on the modules and strength of the material chosen. When metal is used for member 62, the member 62 can preferably have a thickness of about 1 mm, and when a high strength polymer is used for member 62, the member 62 can have a thickness that varies from about 6 mm to about 8 mm.
Member 62 preferably has one or more small apertures 63 extending through its body (e.g., from the inner surface 64 to the outer surface 65) so that a connector 70 can be inserted or threaded therethrough and connected or secured to member 62, as will be explained in detail below. A plurality of apertures 63 can be provided along the length of member 62 to enhance customization of the present invention in a particular use, as desired.
Aperture 63 preferably can have a counterbore opening 66 on the outer surface 65 of the member 62 so that, as will be discussed below, the connector 70 can be seated or recessed therein.
13 Turning now to Fig. 6, three separate members 62 can also be used in accordance with the present invention to assist in restructuring or reconfiguring the chamber 12 as three continuous communicating truncated portions of ellipsoids, as desired. In such an embodiment, the members 62 are spaced about 120° around the epicardial surface 34. For example, one member 62 is preferably configured to be positioned adjacent the anteroseptal portion of the chamber 12, a second member 62 is preferably configured to be positioned adjacent the posteroseptal portion of the chamber 12, and the third member 62 is preferably configured to be positioned adjacent the posterolateral portion of the chamber 12.
So that the epicardial surface 34 may separate from member 62 adjacent or at the lateral portions 67 of inner surface 64 without creating substantial negative pressure, a pad
56 can be positioned and/or interposed between the epicardial surface 34 and the inner surface 64. Pad 56 can be, as exemplified in Figs. 7A and 7B, a fluid-filled or gel-filled pad or cushion, which generally will occupy space laterally beyond the member 62 and the lateral portions 67 of inner surface 64 while the heart 10 is in as a relaxed state. However, as the heart 10 contracts and the wall shortens (see, e.g., Fig. 7B), generally circumferentially (reducing cavity radius), the epicardial surface 34 will "peel away" from the members 62 and the lateral portions 67 of inner surface 64 and thus, fluid or gel in the pads 56 can fill this space so that the inner surface 64 and epicardial surface 34 remain in contact and effect focal restraint whereby the chamber 12 is restructured, as detailed above. In one embodiment, the pad 56 is a closed system. Alternatively, it is contemplated that pad 56 can be configured such that fluid and/or gel can be added or removed to enhance functionality of the device 60 of the present invention, as desired. For example, one or more lines 58 can be in fluid communication with a chamber in pad 56. Line 58 can extend from pad 56 to an injection port 59, which can be positioned subcutaneous or elsewhere,
14 as desired, for enhanced access. As will be appreciated by those skilled in the art, fluid or gel can be injected into the injection port 59 using a standard syringe and needle, or other device, to increase the size of the pad 56 and/or the pressure within the pad 56, as desired. Alternatively, fluid or gel can be withdrawn as desired. Alternatively, pad 56 can be as a low durometer polymer such as a plastic or other material (e.g., rubber). In use, as detailed above, the material accommodates and maintains the contact between the member 62, and more specifically its inner surface 64, and epicardial surface 34 and thus, the desired reconfiguration of the heart 10 as the heart 10 beats or deforms. So that members 62 remains fixed in a spatial or spaced relationship to each other and adjacent or on the epicardial surface 34, as desired, one or more connectors 70 connect or otherwise join the members 62 together. Connector 70 can take the form of various mechanical connectors used in the industry to attach and position prosthetic devices in the body. Exemplar connectors 70 which will be discussed below in some detail, may include a chord (e.g., 72), a pin (e.g., 73 , 76) and the like.
15 Chord 72 is generally made of a biocompatible material that preferably inhibits the formation of blood clots and/or enhances tissue integration around the chord 72. Illustrative examples of materials which may be employed as chord 72 may include expanded PTFE, polyester, or polypropylene. Preferably, chord 72 may include PTFE, a braided polymer, such as polyester or a monofilament polypropylene.
Basal connector 96 preferably is configured to traverse or lie adjacent or on the atrial surface of the anterior annulus of an atrioventricular valve 50, such as the mitral valve
52, so as to assist in connecting or joining together end portions 68 of members 62 to assist in maintaining the position of the device 60 relative to itself and heart 10. It is further contemplated that a prosthetic valve and/or an annuloplasty ring may be used to assist in attaching and/or securing the basal connector 96 to the heart 10. Basal connector 96 may take the form of a portion of the prosthetic valve or annulus ring attached to the anterior annulus. Basal connector 96 is generally made of a suitable rigid biocompatible material, similar to member 62 as discussed above, and preferably includes a porous covering or outer surface to enhance tissue integrations, such as polyester fabric.
Basal pin 72, as exemplified in Fig. 8, preferably is an elongated screw, bolt, connector, or the like with a body portion 74, which can be sized to be insertable through aperture 63. Head portion 73 of the pin 72 preferably has a diameter greater than aperture 93 in the basal connector 96 so that pin 72 cannot be pulled therethrough. Moreover, head portion 73 can preferably be a rounded shape so that it can be seated and can assist in rotating and/or pivoting in counterbore opening 97. The body 74 can have an external
16 threaded portion 75, which preferably extends along a portion of the body 74 opposite the head 73, or alternatively, along its entire length.
Pins 72 and 76 and fastener 98 are each preferably made of a biocompatible material such as 3/6 stainless steel or CP titanium. Moreover, use of the same metal materials for the pins 72 and 76 and fastener 98, and member 62 can minimize the electrolytic corrosive action that can occur when dissimilar metal materials are used adjacent or in contact with
17 each other. Moreover, the exterior surfaces of pins 72 and 76 and fastener 98 are preferably a porous material or have a porous finish or coating so as to enhance tissue integration.
In an alternative embodiment of the present invention exemplified in Figs. 9-10, a generally horseshoe or U-shaped harness or brace 90 can be used as device 60 to assist in reconfiguring or restructuring the heart 10, as detailed above. Brace 90 has at least two generally rigid portions 92, which are each generally similar to member 62 detailed above. The brace 90 can also include as a connector portion 94, which is generally flexible only in a plane tangent to the epicardial surface 34, and is generally configured to be positioned adjacent the epicardial surface 34 and extends around or spans the apical portion 20 of the heart 10. Connector portion 94 should be sufficiently flexible so that, as exemplified in
Figs. 11 A and 1 IB, impedance to ventricular torsion during contraction is minimized and the heart 10 can twist as the heart 10 beats or contracts. While illustrated as generally a panel, connector portion 94 can take the form of any shape so long as it has an elastic quality, yet permits flexion only in the plane tangential to the epicardial surface 34. The brace 90 also can preferably include a basal connector 96, which assists in connecting or joining the brace 90 to the heart 10. In the illustrated embodiment, basal connector 96 is joined to the brace 90 at or adjacent its end portions 91 using the apparatus and techniques discussed above.
One or more auxiliary connectors 80, as exemplified in Figs. 12 and 13, can also be used with the present invention to assist in maintaining the position of the device 60 relative to itself and to the heart 10, and more specifically, so that sideways displacement of the heart 10 relative to the brace 90 is minimized. Auxiliary connector 80 can take the form of a spike shaped object or pin 82 that is configured to penetrate the epicardial surface 34 into the cardiac tissue 32. Also, auxiliary connector 80 can take the form of a button 84 and
18 cord 86. One end of the cord 86 can be attached or otherwise secured to the member 62 or brace 90, and it can extend inwardly into and through the cardiac tissue 32. A button 84 can be attached to or adjacent the other end of the cord 86 adjacent the endocardial surface 38. Button 84 can be made of any biocompatible material, and is preferably made of a material that enhances tissue growth around the button 84 to minimize the possibility of the formation of blood clots. It is further contemplated that other surgical attachment articles and techniques can be used in accordance with the present invention, such as screws, surgical staples and the like, to assist in fastening and securing the device in position, as desired. In accordance with the teachings of the present invention, the device 60 should be so configured and positioned adjacent the heart 10 whereby the wall tension is reduced in accordance with LaPlace's theory of a chamber, which is as follows:
Chamber pressure = K * (tension of wall)/(radius of chamber), wherein K is a proportionality constant. As an illustrative example of one embodiment in accordance with the teachings of the present invention, calculations will be performed based on the following model as exemplified in Figs. 3 and 5. It is assumed that the long axis of the left ventricle 12 of the heart 10 is 100 mm, that the equatorial or short axis of the chamber 12 is 70 mm, that the equatorial wall thickness "w" of the chamber is about 10 mm and the basal diameter of the heart 10 is 60 mm. An arbitrary slice or plane of the left ventricle 12 will be analyzed to illustrate local dimensional computations for the present invention.
Furthermore, this model will assume that the inner radius "R," (of the slice or plane) of the unrestricted heart 10 (see, e.g., Fig. 3) is about 28.982 mm and that the heart 10 has an outer radius of about 38.406 mm. As is known to those skilled in the industry, the width
19 "w" and radius "R," can be directly obtained from high-resolution imaging, such as an echocardiogram, or preferably, by computation based on an assumed geometric model. The ratio of the restraint contract pressure of the left ventricle 12 of the device 60 to the cavity pressure can vary from 1 to about 2. This example will further assume that the allowed ratio of the restraint contact pressure of the left ventricle 12 of device 60 to the cavity pressure is to be limited to a maximum of about 1.5, which is represented by symbol K in the mathematical formulas below. Also, it is desired to achieve an altered radius "R2" of the left ventricle 12 to 80% of its original radius R„ and as such: R2 = .8*R, R2 = .8*28.982 mm
Now that the value of radius of curvature of the inner surface 64 "g" has been calculated, the angle "θ" between the line g, (joining the center of curvature of the member 62 with one margin, in this plane, of the contact area between inner surface 64 and the epicardial surface 34) and line g2 (joining the same center of curvature with the center of the inner surface 64 in the same plane) can be calculated using the following formula: θ = (π/2) * [R2-R,] ÷ (R2+w+g) θ = (π/2) * [28.982 mm -23.186 mm] ÷ (28.982 mm+9.424 mm + 65.22 mm)
20 θ = (π/2) * [5.796 mm] ÷ (103.636 mm) θ = .09063 radius or 5.332 degrees
Using the formula below, the distance inwardly that the heart 10 should be displaced can be calculated so that the desired restructuring can be achieved. If "e" is the distance that the center of either member 62 is to be separated from the absolute center of a remodeled ventricle in this plane, then: e = [(g+w+R2) * cosθ] - g e = [(65.22 mm + 9.424 mm + 23.186 mm) * cos 5.332 degrees] - 65.22 mm e = 32.21 mm. As such, twice e or (2*e) is 64.42 mm, and this is the preferred distance separating the oppositely disposed inner surfaces 64.
To position the device 60 into a body (e.g., the thoracic cavity) and around an existing natural heart 10, a high resolution image, such as a standard echocardiogram, or other analysis of the heart 10 is preferred so that certain anatomical measurements can be recorded and calculated, as detailed above. While the present application only includes one set of mathematic calculations to optimize the present invention, it is contemplated that measurements will need to be taken along several axes, planes, locations or positions along the longer axis of the chamber. Pre-surgical calculations are preferred so that the device
21 60 can be optimally configured and sized, as desired, before surgery to minimize surgical time.
Turning now to Figs.4-6, members 62, which may be customized according to the anatomical measurements and calculations, are preferably positioned adjacent or against the epicardial surface 34 in predetermined locations relative to each other and relative to the chamber (e.g., left ventricle 12). 'As exemplified in Fig. 4, the members 62 can be positioned about 180 degrees relative to each other, and in Fig. 6, about 120 degrees relative to each other, as desired. The members 62 can be temporarily attached to the heart 10 using temporary sutures or a suitable adhesive so that the connectors 70 can be attached and secured without moving members 62.
22 Connector 70 is attached or secured to member 62 so that portions of the heart 10 are urged inwardly, as desired. In one embodiment, chord 72 can be inserted through an aperture 63 in one of the members 62, and inserted through the cardiac tissue 32, preferably using a surgical needle, whereby the chord 72 can be extended across the cavity 13, into the cardiac tissue 32 on the other side of the chamber (e.g., left ventricle 12), and then finally, through a corresponding aperture 63 in the oppositely disposed member 62. This can be repeated with as many connectors 70 as necessary so that the members 62 are positioned and secured, as desired. Chord 72 can be either cut or sized, or can be provided pre-sized and then secured to the member 62, such as by tying a suture knot, so that chord 72 is taut between or among the members 62, and so that members 62 are positioned as a predetermined distance apart, (2*e), as detailed above, so that the heart 10 is restructured or reconfigured, as desired.
In an alternative embodiment utilizing a basal connector 96, the basal connector 96 can be secured to the annulus of the mitral valve 52, using sutures and/or a suitable adhesive. The basal pin 72 can have a needle or other sharp instrument attached to the end opposite the head 73. A suture can be interposed between the needle and pin 72 to assist in inserting the pin 72 through the cardiac tissue 32. The needle can be inserted through aperture 93 in basal connector 96, through cardiac tissue (e.g., the ventricular free wall and or the atrioventricular wall 42), and then through aperture 63. The protruding threaded
23 portion 75 can have a fastener 98 attached, preferably screw on and attached to the pin 72. To enhance attachment and to minimize the opportunity for fastener 98 to become unsecured, an adhesive or additional fastening device may be used to assist in securing the members 62 in place, as desired. The portion of pin 72 extending beyond the fastener 98 can be removed. Fastener 98 is preferably attached to pin 72 so that it is seated in the counterbore opening 66 and head 73 is preferably seated in counterbore opening 97 so as to assist in providing a ball and socket like and/or pivot joint, which can allow some rotational movement of the device 60 during contraction of the heart 10.
When device 60 is provided as brace 90, brace 90 and its rigid portions 92 are positioned adjacent or against the epicardial surface 34, as were the members 62 while connector portion 94 is positioned or wrapped around the apical portion 20 of the heart 10
24 to assist in connecting or joining the rigid portions 92 together, and to assist in maintaining the brace 90 properly positioned adjacent the heart 10 to provide the desired restructuring.
Once the device 60 is properly positioned and secured, termination of a cardiopulmonary bypass, if used, is attempted and, if successful, the thoracotomy is closed. An alternative method for positioning the present invention includes removing the natural heart 10 from the patient, positioning all the components of the present invention 60, as discussed above, and auto-transplanting the natural heart 10 back into the patient using standard cardiectomy and cardiac transplant techniques known in the industry.
2. A static device for use with a heart having at least one chamber, said device comprising: a plurality of members configured to be positioned adjacent the epicardial surface
of the heart; and at least one connector for extending through the chamber joining the members
3. A static device for use with an unrestricted heart having an outer wall and at least one chamber, said device comprising: a plurality of members configured to be positioned adjacent the epicardial surface of the heart; and a connector joining the members;
26 wherein said members are fixed in a spaced relationship relative to each other such that at least two portions of the outer wall are displaced inwardly from the unrestricted position.
4. The device of claim 3, wherein said member comprises a rectangular shape.
5. The device of claim 3, wherein said member comprises an inner surface having an outwardly convex curved configuration.
6. The device of claim 3, having first and second members, wherein said first and second member are positioned in a spaced relationship relative to each other about 180 degrees apart.
9. The device of claim 3, wherein the first member is configured to be positioned adjacent the anteroseptal portion of the chamber, the second member is configured to be
27 positioned adjacent the posteroseptal portion of the chamber, and a third member is" configured to be positioned adjacent the posterolateral portion of the chamber.
10. The device of claim 3, wherein said device comprises a pad adjacent the inner surface.
17. The device of claim 15, wherein said connector comprises a heavy monof╧èlament polypropylene suture.
20. The device of claim 19, wherein said member each comprise an aperture and wherein said pin comprises a threaded portion adjacent one end of said pin, and a fastener receivable by said pin.
21. The device of claim 3, comprising at least one fixation device on said member configured for insertion into the heart.
22. The device of claim 21, wherein the fixation device comprises a pin for penetrating the wall of the heart
23. The device of claim 21, wherein the fixation device comprises a button for
positioning adjacent the interior surface of the heart and a cord joining said connector and said button.
affixing a static brace to the heart to provide the chamber of the heart as at least two contiguous portions of truncated ellipsoids.
29. A method for reducing the wall tension on one of the chambers of un unrestricted heart, comprising the steps of: affixing a static brace having at least two members and a connector to the heart to urge at least two portions of the chamber wall inwardly from the unrestricted position.
30. The method of claim 29, comprising the steps of providing fastener on the member and inserting the fastener into the wall of the heart.
31. The method of claim 29, comprising the step of positioning the connector adjacent the endothelium of the heart.
32. The method of claim 29, comprising the step of attaching the connector to an atrioventricular valve.
287173.01
PCT/US1999/004978 1998-03-05 1999-03-05 Device and method for restructuring heart chamber geometry WO1999044534A1 (en)
US09/035,710 1998-03-05
WO1999044534A1 true true WO1999044534A1 (en) 1999-09-10
JP2003521310A (en) * 2000-01-31 2003-07-15 イーヴィー３ サンタ ローザ インコーポレイテッド Percutaneous mitral valve annuloplasty and cardiac reinforcement
US6190408B1 (en) 2001-02-20 grant
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