CA2242412C - Activation device for the natural heart and method of doing the same - Google Patents
Activation device for the natural heart and method of doing the same Download PDFInfo
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- CA2242412C CA2242412C CA002242412A CA2242412A CA2242412C CA 2242412 C CA2242412 C CA 2242412C CA 002242412 A CA002242412 A CA 002242412A CA 2242412 A CA2242412 A CA 2242412A CA 2242412 C CA2242412 C CA 2242412C
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- natural heart
- ring
- yoke
- septal
- stint
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/24—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
- A61F2/2478—Passive devices for improving the function of the heart muscle, i.e. devices for reshaping the external surface of the heart, e.g. bags, strips or bands
- A61F2/2481—Devices outside the heart wall, e.g. bags, strips or bands
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/10—Location thereof with respect to the patient's body
- A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
- A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
- A61M60/148—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel in line with a blood vessel using resection or like techniques, e.g. permanent endovascular heart assist devices
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/10—Location thereof with respect to the patient's body
- A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
- A61M60/165—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/20—Type thereof
- A61M60/289—Devices for mechanical circulatory actuation assisting the residual heart function by means mechanically acting upon the patient's native heart or blood vessel structure, e.g. direct cardiac compression [DCC] devices
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- Health & Medical Sciences (AREA)
- Cardiology (AREA)
- Heart & Thoracic Surgery (AREA)
- Engineering & Computer Science (AREA)
- Veterinary Medicine (AREA)
- Biomedical Technology (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Vascular Medicine (AREA)
- Anesthesiology (AREA)
- Hematology (AREA)
- Mechanical Engineering (AREA)
- Transplantation (AREA)
- Oral & Maxillofacial Surgery (AREA)
- Prostheses (AREA)
- External Artificial Organs (AREA)
- Surgical Instruments (AREA)
- Diaphragms For Electromechanical Transducers (AREA)
- Finger-Pressure Massage (AREA)
- Medicines Containing Material From Animals Or Micro-Organisms (AREA)
- Medicines Containing Plant Substances (AREA)
- Percussion Or Vibration Massage (AREA)
- Massaging Devices (AREA)
Abstract
An activator device for activation of cardiac tissue having a stint for placement within the interior volume of a natural heart adjacent cardiac tissue thereof. The device also includes a yoke for placement around a portion of the exterior surface of the natural heart in general alignment with the stint and connected to the stint by at least one cord. The device provides a simple yet reliable mechanism for assisting in extended activation of a natural heart with minimal impact and intrusion.
Description
-ACTIVATION DE~ICE FOR THE NATURAL HE~RT
David Boyd Melvin, M.D.
TECHNICAL FIELD OF THE INVENTLON
The present invention relates to a device for assisting in the activation and operation of a living heart, and more specifically, for mechanically deforrning cardiac ~ tissue such that the circulation of blood is maintained.
BACKGRO~UND OF THE INVENTION
The natural heart, and specifically, the cardiac tissue of the natural heart can fai for various reasons to a point where the natural heart cannot provide suff1cient circulation of blood for a body so that life can be maintained. As a solution for the failing natural heart, several attempts have been made in the past to provide a device to m~int~in circulation.
One such approach has been to either assist or to entirely replace the existing natural heart in a patient Iwith an artificial heart, or to transplant a natural heart from - another human into a patient. Several drawbacks have limited use of prior devices to applications having far too brief of a time period to provide a real lasting benefit, and to transplant use in a tiny fraction of those afflicted with heart disease or malfunction.
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 A~ T
could occur with greater ease. Additionally, an artificial heart lining can crack, which inhibits performance, even if the crack is at a microscopic level.
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 hurnan, 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 consurning 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 enh3nced 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 wrap skeletal muscle tissue around the natural heart to use as an auxiliary contraction mechanism to pump the natural heart. As currently used, skeletal muscle cannot alone typically provide sufficient and sustained pumping power for m;~lint~ining circulation of blood through the circulatory system of the body, especially for those patients with severe heart failure.
Still another concept for m~int~ining the existing natural heart as the pumping device involves enveloping a substantial portion of the natural heart, such as the entire left and right ventricles, with a pumping device for rhythmic compression. An exarnple of this is disclosed in U.S. Patent 4,536,893 (Parravicini). Although somewhat effective as a short term treatment, the pumping device has not been suitable A~ r"r-n s~ T
for long term use. Typically, a vacuum plt;5::iui~, iS needed to o~,~,..;ollle cardiac tissue/wall stiffness so that the chambers can return to their original volume and refill with blood. This "active filling" off the chambers with blood limits the ability of the ~Ulll~illg device to respond to the need for adj-l~tment~ in the blood volume pumped through the natural heart, and can adversely affect the circ~ tion of blood to the col~llaly arteries. Natural heart valves are quite sensitive to wall and annular distortion, and movement patterns that reduce a chamber's volume do not neceYs~rily facilitate valve closure (which can lead to valve leakage). Another major obstacle with long te~n use of such pumping devices is the deleterious effect of extensive mechanical cont~ctin~ of living int~rn~l surfaces (endocai.liu~,n). In certain cases, this coaption of endoca~
tissue is probably mech~nic~lly necessary for a device that encompasses both ventricles to produce independent output ~ YUUCS, but it can colll~rull~ise the integrity of the living endothelium.
Another device developed for use with an çxi~ting heart for YIIY~ lg the circulatory function of a living being and the pUll~illg action of the natural heart is an extern~l bypass system, such as a cardiopulmonary (heart-lung) rn~rhin~ Typically, bypass devices of this type are complex and large, and, as such, are limited to short term use in an ~,~dLillg room during surgery, or to m~ itli~.g the circulation of a patient while ~w~iLiilg receipt of a transplant heart. The size and compl~xity effectively prohibit use of bypass systems as a long term solution, as they are rarely even portable devices.
Furthermore, long term use of a heart lung m~-~hin~ can damage the blood cells and blood borne products, resulting in post surgical complications such as bleeding, thromboembolism function, and increased risk of infection.
In an effort to stabilize the natural heart, supports rings have been inserted around the valve annuli. An exarnple of this is disclosed in U.S. Patent 5,201,g80 (Wright, et al.), in which ring shaped prosthesis are provided for placement adjacent atrioventricular valves to correct defects, such as dilation of the valve annulus. The teachings of Wright et al. are, however, limited to valve repair and nothing in the reference teaches or suggests providing a splint adapted to support the septal wall of the natural heart.
Consequently, none of the previous available techniques or devices for m~int~ining circulation of blood provided an adequate or practical long-term use device or technique for adequately m~int~ining sufficient blood pressure and circulation of blood through the circulatory system of the body.
SUMMARY OF THE PRESENT INVENTION
It is the object of the present invention to provide a device for activation of a natural heart that provides different independent pressures to the left and right side of the natural heart.
It is another object of the present invention to provide a device for activation of a natural heart that minimi7es damage to the coronary circulatory and the endocardium (lining tissue).
It is still a further another object of the present invention to provide a device for activation of a natural heart that allows one or more of the heart charnbers to rapidly and passively refill at low pressure after an activation stroke.
E~) S
Another object of the present invention is to provide a device for the activation of a natural heart that supports and maintains competence of the heart valves so the heart valves can function as designed.
Still another object of the present invention is to provide a device for the activation of the heart that functions at the proper rate.
Yet another object of the present invention is to provide an apparatus for the activation of a natural heart on a long terrn basis.
It is yet still an object of the present invention to provide a device for the activation of a natural heart to provide an implant device that does not require removal of an existing natural heart.
Additional objects, advantages, and other features of the present invention willbe set forth and will become apparent to those skilled in the art upon e~rnin~tion of the following, or may be learned with practice of the invention.
To achieve the foregoing and other objects, and in accordance with the purpose herein, the present invention comprises an activator device for use with a natural heart having an internal stint for placement within the interior volume of a natural heart adjacent cardiac tissue. The device also includes a yoke for placement around a portion of the exterior surface of the natural heart in general alignment with the stint and is connected to the stint by at least one cord.
Preferably, the activator device includes a first ring for placement around at least one of the atrioventricular valve annuli, a second ring for placement around at least one of the outflow valve or semilunar annuli, and a septal splint having a frame and sutures in a net-like configuration to stabilize the septal wall between chambers of the natural heart. The first ring, second ring, and the septal splint are connected to each other using fastening elements.
In a preferred embodiment, the yoke is sized and configured for placement adjacent at least a portion of the interventricular groove, preferably adjacent at least a portion of the anterior and posterior portions of the interventricular groove, and more preferably adjacent at least a substantial portion of the anterior and posterior portions of the interventricular groove. In another embodiment, the yoke is sized and configured for placement adjacent at least a portion of the atrioventricular groove.
The present invention also includes an activator attached to the yoke for deforming the natural heart, which preferably includes a hydraulic lateral arm.
In use, the activator deforms a portion of the cardiac tissue by moving an arm from a relaxed condition to an activated condition. As the activator is pressing against the natural heart, the volume of at least one chamber of the natural heart is decreased so that blood is pumped out of the natural heart and into the circulatory system. Thereafter, the activator releases from against a portion of the cardiac tissue returns to the relaxed condition. The combination of the stint and yoke assist in returning the volume of the chamber so that at least one of the chambers of the natural heart ref1lls with blood and thus, the steps can be repeated.
Different forces can be applied to a natural heart for reducing the volume of atleast one of the chambers. These forces can include applying a torsion force or a shearing to the natural heart, flattening a portion of the cardiac tissue, applying a uniform pressure to the natural heart, and/or applying an indentation against at least one point on the exterior wall of the natural heart.
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.
BI~Tli',F ~ESCRIPTION OF THE DRAWINGS
While the specification concludes with clairns particularly pointing out and distinctly cl~iming the present inve~tion, it is believed the same will be better nn~lerstclod from the following description taken in COllj ull~;lion with the accompanied drawings in which:
Fig. 1 is a partial frontal anterior perspective view of an exemplary natural heart;
Fig. 2 is a perspective view of an int~rns~l stint and exterior yoke made in accordance with the present invention;
Fig. 3 is a partial cross-sectional view of a natural heart with a septal splint made in accordance with the present invention placed within a natural heart;
Fig. 4 is a partial frontal pt;l~c~ e view of a natural heart with an Pxtern~l yoke placed on a natural heart;
Fig. SA is a frontal ~ e~ e view of one embodiment of the extern~l yoke and activator of the present invention;
Fig. 5B is a frontal pe,~e~ e view of another embodiment of an f~tern~l yoke and activator of the present invention;
Fig. 6 is a top sectional ~ ;c view of a natural heart with an int~rn~l splinlt and an ext~rn~l yoke of the present invention illu~Lldled being conn~c~efl by 11~ .n. ,.1 cords;
Fig. 7A is a partial schem~tic view of an exemplary activator of the present invention in a relaxed condition; and Fig. 7B is a partial schematic view of an exemplary activator of the present invention in an activated condition.
DI~TAILED DESCRIPTI(~N OF THE PREFERRED EMBODIMENT
Referring now to the figures in detail wherein like numerals indicate the same elements throughout the views, a natural heart, generally indicated in Figure 1 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. A natural heart l0 also includes an upper portion having twochambers, a left atrium 16 and a right atrium 18, which primarily serve as an entryway 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 of cardiac tissue separating the left and right ventricles 12 and 14, respectively, is defined by an interventricular groove 20 on the exterior wall of the natural heart 10. The atrioventricular wall of cardiac tissue separating the lower ventricular region from the upper atrium region is I defined by atrioventricular groove 22 on the exterior wall of the natural heart 10.
Generally, each ventricle is in fluid communication with its respective atria through an atrioventricular valve. More specifically, the left ventricle 12 is in fluid communication with the left atrium 16 through the mitral valve, while the right ventricle 14 is in fluid communication with the right atrium 18 through the tricuspid valve.
Generally, the ventricles are in fluid communication with the circulatory system (i.e., the pulmonary and peripheral circulatory system) through semilunar valves. More specifically, the left J ~) C~
ventricle 12 is in fluid cornmunication with the aorta 26 of the peripheral circulatory system, through the aortic valve, while the right ventricle 14 is in fluid communication with the p~llm~nAry artery 28 of the pulmonary, circulatory system through the pulmonic valve.
By way of a non-limiting example, the present invention will be discussed in terms of embo~liment~ that are used to primarily assist in the activation and operation o~
the left ventricular portion of the natural heart 10, however, it is noted that the present invention can also be used to assist in the activation and operation of other portions of the natural heart 10, such as the atria, or the right ventricular portion of the natural heart 10. The present invention is a mech~niçRI activator, ill1lstrAted in Figure 2 as 50, which includes an int~rnRl stint 52. Furthermore, the present invention includes an external yoke 70 fixed to the internal stint 52 by trRnemnral cords 86. The internal stint 52 is sized and configured for placement within the interior volume of the natural heart 10, and includes a generally triangular shaped frame 53 that can be assembled from a plurality of interlocking struts, preferably an anterior, a posterior and a basal strut. The stint 52 also includes at least two separate ring structures, namely a first ring 56 sized and configured for rlAeçment R~ cçnt the atrioventricular valve annuli, and preferably jR~ the mitral valve annuli in the left atriurn 16, and a second ring 58 sized and configured for plAcçm~nt R~ cent the s~mill-nRr valve annuli preferably subjacent the aortic valve annuli in the lefL ventricle 12.
Figure 3 further illustrates a septal splint 54, which can include one or more - strands of sutures affixed to the frarne 53 through loops positioned on the frame 53, preferably the loops are affixed to the inner portion of frame 53, and more preferably, at about 1.5 cm intervals. The splint 54 can take the form of a tennis racket-like shaped configuration or a sno~vshoe like shaped configuration to brace or stabilize one side of the septum, preferably the right side of the interventricular septum without distortion of the chordae. Preferably, the septal splint 54 is positioned by stringing a heavymonofilament polypropylene suture, such as a #5 polypropylene suture, under, through, and behind the trabeculae, and through the loops as will be discussed later in great detail.
The f1rst and second rings 56 and 58 and the septal splint 52 are attached at least to each other using a connector element 59, such as a pin to assist in m~int~ining the relative position so that the first and second rings 56 and 58, respectively, and the splint 52 are supported while the natural heart 10 is being activated.
So that the components of the stint 52 (e.g., the septal splint 54 and f1rst andsecond rings 56 and 58) are not totally rigid and can exhibit an elastic quality, the components are preferably made of a stiff coil spring material covered with braided polyester. Localized adjustments can be made to the elasticity of the various components of the stint 52 to reduce the potential for problerns, such as ~l~m~ging the cardiac tissue or compromising the coronary circulation.
As illustrated in Figure 4, the device 50 also includes an external yoke 70 for placement around a portion of the exterior surface of a natural heart 10. The generally stirrup shaped yoke 70 restricts free motion of the natural heart 10 so that the natural heart 10 can be ac:tivated. Preferably, the yoke 70 can be between about 1 and 2 cm wide and includes a semi-rigid collar portion, preferably made of polypropylene, for providing lI
rigidity to the yoke 70. Additionally, the yoke 70 can include a gel-filled cu~hinn portion that is positioned imrnediately ad3acent exterior surface of the natural heart 10 for providing equalized pressure over the irregularities in the epicardial surface of the natural ~ heart 10, and preferably, any of the coronary arteries 30 within each region under the yoke 70. Preferably, the yoke 70 is sized and configured for plac~m~nt adjacent at least a portion of the atrioventricular groove 22, more preferably, at least a portion of the anterior and posterior portions of the interventricular groove 20, and most preferably, at least a substantial portion of the anterior and posterior portion of the interventricular groove. In yet another embodiment~ the yoke 70 is sized and configured for pl~cement adjacent at least a portion of the atrioventricular groove 22.
Referring now to Fig. 6, general alignment of the yoke 70 is m~ e~ by at least one ll;~ .ldl cord 86, and preferably, a plurality of cords 86 that penetrate the walls ofthe natural heart 10 and connect to the stint 52. The cord 86 is preferably made of a heavy braided, polymer-impregn~t~d polyester suture core (such as # 5 Ethiband~) by Ethicon, Inc.) covered in the h~ ocardial portion with a braided sleeve of polyester yarn to promote firm tissue growth around the cord 86. When it is necessary to utilize more than one cord 86 with the present invention, spacing of the cords 86 should preferably be at intervals of between about 15 mm to 20 mm along the yoke 70, from the septal splint 54 and the first ring 56 ext~n-ling obliquely outwardly toward the left ventricle exterior wall for inserl:ion into the left ventricle margin of the yoke 70.
More preferably, the cords 86 should be positioned for avoiding contact with the- coronary vessels 30. The cords 86 vary in length such that the splint 54 ~nd first ring 56 CA 022424l2 l998-06-30 are oriented beneath the gel-filled cushion portion while the septurn stint 52 and the first ring 56 are held stable in general ~ nment with the natural heart 10, and are generally not allowed to move away from the ventricular exterior wall when ples~ul~ iS applied to a natural heart 10 via by activator 74.
As mentioned above, the present invention also includes an activator 74 ~tt~-h~dto at least a portion of the yoke 70, preferably the apical portion 70a, as illustrated in Figures 5A and 5B. The activator 74 includes a lateral flexible arrn 75 generally having an "L" shaped configuration that extends approximately two-thirds of the distance between the apical portion 70a and base portion 70b of the yoke 70.
Connected to the arm 75 is at least one, and preferably a plurality of, bands 84~-xt~n~1ing away from the arm 75 sized and configured for p~ .çment ~ .ent the exterior surface of the natural heart 10. The distal ends of the bands 84 are tvpically affixed and secured along portions of yoke 70.
One embodiment of the yoke 70 and activator 74 is illustrated in Figure 5A in which the bands 84 extend perpendicularly away from the arm 75 and connect to the anterior and posterior portions of yoke 70. In another embodiment of the yoke 70 and activator 74 as illustrated in Figure 5B, bands 84 extend radially away from the distal end of the arm 75.
Pceferring now to Figures 7A and 7B, the activator 74 preferably has a hydrauliclateral arm 75 having a tubed-shape corrugated configuration with rings 77 affixed to the inner aspect of each corrugation. A plurality of longit~lin~lly exten~linF cords 76, preferably three or more, are affixed to the inner portion of arm 75, preferably the distal wo 97/24101 PCT/US97/00374 end of arrn 75 and also preferably to each of the rings 77. The cords 76 can vary in length, especially between the fixation points to each ring 77 for controlling the se~ ion distance between rings 77. In fluid comrnunication with the arm 75 via a- driveline 92 is a pump unit "P", such as pneumatic or a hydraulic pump for controlling or altering the fluid volume within the arm 75.
Figure 7A illustrates the arm 75 in a relaxed condition when fluid ~ Ule within arm 75 is at or below ambient levels and where the shape of arrn 75 is ~letçnnin~ by the ext~rn~l forces and the intrinsic stiffn~oc,s of arm 75. To utilize the present invention~
S~ within the arm 75 can be increased, preferably above ambient levels, so that the shape of the arm 75 is altered to an activated condition, as illustrated in Fig. 7B. The length dirr~ ce of the various cords 76 between the rings 77 controls the radius of curvature of the arm 75 and the direction of curvature at various portions along the longitudinal length of the arm 75. The amount of P1~ UI~. required within the arrn 75 must be sufficient to overcome the intrinsic stif~c of the arm 75 at arnbient con~ition~
and to facilitate the proper deform~tion of both the arm 75 and bands 84 so that the proper amount of pressure is applied to the exterior wall of the natural heart 10 to assist in s~l~ring (i.e., reducing) the volume of one or more rh~mh~r of a natural heart 10 (e.g., the left ventricle 12) to ,,,~ circ~ tinn ofthe blood through the circulatory system.
In a pler~ d embodiment, the arm 75 can be customized to apply dirrel~nl pressure to dirre~ portions of the natural heart 10. For example, varying the ~ meter of arm 75 along the longi~l~lin~l length can assist in controlling the curvature of arm 75.
Regions of the arm 75 needing less bending moment can have a smaller diameter and CA 022424l2 l998-06-30 WO 97/24101 PCT/USg7/00374 regions of the arm 75 where greater bending moments are ~l~fcllcd can have a larger diameter.
Various embo~liment~ of an activator 74 can be utilized with the present invention to achieve a change in the volume of one or more heart chambers. It is noted that any activator 74 used with the present invention should be sufficient so that the cardiac output of a typical adult is between about 3 l/min and about 30 l/min, and preferably bt;lwee about 5 l/min and 20 l/min.
In addition, there are various possible forces which can be used for activating, and thus altering the chamber volumes of the natural heart 10. The present invention can be ~ltili7~d to flatten the exterior wall of the natural heart 10 in a plane s~lbst~ntiS-lly perpendicular to the plane of the atrioventricular valves (e.g., a mitral valve) or ~lbs~ lly parallel to the septum. When utili7in~ such a force, the activator 74 should be configured to produce a flexion in the convex direction limited to between about 2.5 to 3.0 times the CU~ lul~ value of the exterior wall of the natural heart 10 during the diastolic portion of the cardiac cycle. Deflection in a concave direction is restricted only to those bands 84 extPn-ling away from the arm 75 and conn~ctin~ to the base portion 70b of yoke 70.
Also, an activator 74 can be used to apply a ~irOllll pl~ UlC; to ~ul~s~ lly theentire exterior wall of the natural heart 10.
Furtherrnore, the activator 74 can be used to indent the exterior wall of the natural heart 10 at more than one location, and preferably at two or three locations on either an exterior wall or the septum in a hemispheric or hemiellipsoid profile.
WO 97/24101 PC'r/lJS97/00374 Additionally, an activator 74 can apply a torsion force to at least a part of the natural heart 10 at various angles.
In yet another embodiment, the activator 74 can apply a shearing force to a portion of the lateral exterior wall, which is directed apically and is a basal sheer force applied on the right side of the stint 52.
When the orientation of the arm 75 is altered from the relaxed condition, which.is illu~lldled in Fig. 7A, to the activated condition, which is illustr~tP~d in Fig 7B, the arm 75 and the bands 84 deform and apply pressure against the exterior wall of the natural heart 10 for ~,ci~tin~ with or facilitating activation ofthe natural heart 10 (the systolic portion of the cardiac cycle). As a result, the volume of one or more chambers of the natural heart 10 is reduced and blood is pumped out of the natural heart 10 and into the circulatory system.
Following the activation (i.e., systolic portion of the cardiac cycle), the arm 75 and bands 84 release from against the cardiac tissue and return to their relaxed conllition The combin~tion ofthe stint 52 and the yoke 70 assists in retl-rning the deforrned portion of the natural heart 10 back to its pre-activation volume so that it can refill with blood during the diastolic portion of the cardiac cycle, so that the entire cardiac cycle can be repeated.
To posltion the device 50 into and around an Pxi~ting natural heart 10, open heart thoracic ~ul~ely is required. Clinically, sufficient ~n~Sth~ci~ is ~rlmini~tP~red to the patient and the thoracic cavity is opened using standard thoracic procedures.
Once the thoracic cavity is opened, circulation of blood to the natural heart 10must be bypassed so the present invention can be inserted into the patient. Referring initially to Fig. 2, the superior vena cava 26, the inferior vena cava (not shown), and aorta 26 are c~nn~ te~l The circulatory system is connected to a cardiopulmonary bypass machine so that circulation and oxidation of the blood are m~int~in~l during theprocedure. By way of example, the procedure ~liecl-eeed in detail will be for insertion of the present invention to assist in the activation and operation of the left ventricle 12.
Through an aortotomy and an interatrial groove left atriotomy, the first and second rings 56 and 58, le~e.;lively, are inserted and sutured in position. Preferably, the first ring 56 is positioned suprajacent the mitral annuli and the second ring 58 is positioned subjacent the aortic annuli.
The interlocking struts ofthe septal frame 53 (e.g., anterior, posterior, basal struts) are inserted into the right ventricle 14 through an apical ventriculotomy, a right atriotomy with partial teml~oldly ~letzl-~hm~nt of the septal tricuspid leaflet of the tricuspid valve, and an outflow tract ventriculotomy, respectively. Suture strands are then passed back and forth against the interventricular septum, threading through loops to provide a septal splint 54. In placement of both the various struts of frame 53 and the strands that form splint 54, care is taken to maneuver behind chordae and behind or through major trabeculae and bases of papillaTy muscles. The suture strands are tied to form the net-like configuration of the septal splint 54 that lies snugly against the septum, but allows it to ) norrnal ri~lLw~d collv~;~ily. Separate connector elements 59, preferably pins, Next, the left pleural cavity is opened and the yoke 70 is positioned behind thenatural heart lO. Cords 86 are assembled as 12" (30.5 cm) strands of suture with a polyester bead fused to one end and blunt straight needle on the other. Each suture is passed through a hole in the margin of the yoke 70, through the cardiac tissue, and S preferably the ventricular wall, and through the internal stint 52 (i.e., first ring 56 or septal splint 54) and anchored after length adjustment, with the excess portion of the sutures cut and. removed. Cords 86 are tightened to render the intrinsically flexible stint 52 relatively taut and control bulging, preferably in a rightwardly direction.
Cardiotomies are closed, and the activator 74 is attached to the yoke 70. The driveline 92 is attached to the drive unit "P" and all indicated monitoring lines are positioned. Preferably, Heparin-filled Teflon-coated polyurethane S Fr. catheters are brought through the posterior cervical incision into the chest and into the atrial appendages and an identical one into a branch of the innominate artery. Termination of a cardiopulmonary bypass 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, as discussed above, and auto-transplanting the natural heart l (~ back into the patient using standard cardiectomy and cardiac transplant techniques known in the industry.
~"~-?~ T
Having shown and described the preferred embodiments to the present invention, further adaptations of the activation device for the living heart as described herein can be accomplished by appropriate modifications by one of ordinary skill in the art without departing from the scope of the present invention. For example, the present invention can be used with any one or even a plurality of the various chambers of a living heart, and also could be used with different activators 74. Other examples of an activator 74 usable with the present invention include a girdle assembly that can be activated by hydraulics forces or other forces, such as an electromagnetic for using magnets and electrical current. Several such potential modifications have been discussed and others will be apparent to those skilled in the art. Accordingly, the scope of the present invention should be considered in terms of the following claims and is understood not to be limited in the details, structure and operation shown and described in its specification and drawmgs.
~ ~s ~
David Boyd Melvin, M.D.
TECHNICAL FIELD OF THE INVENTLON
The present invention relates to a device for assisting in the activation and operation of a living heart, and more specifically, for mechanically deforrning cardiac ~ tissue such that the circulation of blood is maintained.
BACKGRO~UND OF THE INVENTION
The natural heart, and specifically, the cardiac tissue of the natural heart can fai for various reasons to a point where the natural heart cannot provide suff1cient circulation of blood for a body so that life can be maintained. As a solution for the failing natural heart, several attempts have been made in the past to provide a device to m~int~in circulation.
One such approach has been to either assist or to entirely replace the existing natural heart in a patient Iwith an artificial heart, or to transplant a natural heart from - another human into a patient. Several drawbacks have limited use of prior devices to applications having far too brief of a time period to provide a real lasting benefit, and to transplant use in a tiny fraction of those afflicted with heart disease or malfunction.
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 A~ T
could occur with greater ease. Additionally, an artificial heart lining can crack, which inhibits performance, even if the crack is at a microscopic level.
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 hurnan, 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 consurning 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 enh3nced 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 wrap skeletal muscle tissue around the natural heart to use as an auxiliary contraction mechanism to pump the natural heart. As currently used, skeletal muscle cannot alone typically provide sufficient and sustained pumping power for m;~lint~ining circulation of blood through the circulatory system of the body, especially for those patients with severe heart failure.
Still another concept for m~int~ining the existing natural heart as the pumping device involves enveloping a substantial portion of the natural heart, such as the entire left and right ventricles, with a pumping device for rhythmic compression. An exarnple of this is disclosed in U.S. Patent 4,536,893 (Parravicini). Although somewhat effective as a short term treatment, the pumping device has not been suitable A~ r"r-n s~ T
for long term use. Typically, a vacuum plt;5::iui~, iS needed to o~,~,..;ollle cardiac tissue/wall stiffness so that the chambers can return to their original volume and refill with blood. This "active filling" off the chambers with blood limits the ability of the ~Ulll~illg device to respond to the need for adj-l~tment~ in the blood volume pumped through the natural heart, and can adversely affect the circ~ tion of blood to the col~llaly arteries. Natural heart valves are quite sensitive to wall and annular distortion, and movement patterns that reduce a chamber's volume do not neceYs~rily facilitate valve closure (which can lead to valve leakage). Another major obstacle with long te~n use of such pumping devices is the deleterious effect of extensive mechanical cont~ctin~ of living int~rn~l surfaces (endocai.liu~,n). In certain cases, this coaption of endoca~
tissue is probably mech~nic~lly necessary for a device that encompasses both ventricles to produce independent output ~ YUUCS, but it can colll~rull~ise the integrity of the living endothelium.
Another device developed for use with an çxi~ting heart for YIIY~ lg the circulatory function of a living being and the pUll~illg action of the natural heart is an extern~l bypass system, such as a cardiopulmonary (heart-lung) rn~rhin~ Typically, bypass devices of this type are complex and large, and, as such, are limited to short term use in an ~,~dLillg room during surgery, or to m~ itli~.g the circulation of a patient while ~w~iLiilg receipt of a transplant heart. The size and compl~xity effectively prohibit use of bypass systems as a long term solution, as they are rarely even portable devices.
Furthermore, long term use of a heart lung m~-~hin~ can damage the blood cells and blood borne products, resulting in post surgical complications such as bleeding, thromboembolism function, and increased risk of infection.
In an effort to stabilize the natural heart, supports rings have been inserted around the valve annuli. An exarnple of this is disclosed in U.S. Patent 5,201,g80 (Wright, et al.), in which ring shaped prosthesis are provided for placement adjacent atrioventricular valves to correct defects, such as dilation of the valve annulus. The teachings of Wright et al. are, however, limited to valve repair and nothing in the reference teaches or suggests providing a splint adapted to support the septal wall of the natural heart.
Consequently, none of the previous available techniques or devices for m~int~ining circulation of blood provided an adequate or practical long-term use device or technique for adequately m~int~ining sufficient blood pressure and circulation of blood through the circulatory system of the body.
SUMMARY OF THE PRESENT INVENTION
It is the object of the present invention to provide a device for activation of a natural heart that provides different independent pressures to the left and right side of the natural heart.
It is another object of the present invention to provide a device for activation of a natural heart that minimi7es damage to the coronary circulatory and the endocardium (lining tissue).
It is still a further another object of the present invention to provide a device for activation of a natural heart that allows one or more of the heart charnbers to rapidly and passively refill at low pressure after an activation stroke.
E~) S
Another object of the present invention is to provide a device for the activation of a natural heart that supports and maintains competence of the heart valves so the heart valves can function as designed.
Still another object of the present invention is to provide a device for the activation of the heart that functions at the proper rate.
Yet another object of the present invention is to provide an apparatus for the activation of a natural heart on a long terrn basis.
It is yet still an object of the present invention to provide a device for the activation of a natural heart to provide an implant device that does not require removal of an existing natural heart.
Additional objects, advantages, and other features of the present invention willbe set forth and will become apparent to those skilled in the art upon e~rnin~tion of the following, or may be learned with practice of the invention.
To achieve the foregoing and other objects, and in accordance with the purpose herein, the present invention comprises an activator device for use with a natural heart having an internal stint for placement within the interior volume of a natural heart adjacent cardiac tissue. The device also includes a yoke for placement around a portion of the exterior surface of the natural heart in general alignment with the stint and is connected to the stint by at least one cord.
Preferably, the activator device includes a first ring for placement around at least one of the atrioventricular valve annuli, a second ring for placement around at least one of the outflow valve or semilunar annuli, and a septal splint having a frame and sutures in a net-like configuration to stabilize the septal wall between chambers of the natural heart. The first ring, second ring, and the septal splint are connected to each other using fastening elements.
In a preferred embodiment, the yoke is sized and configured for placement adjacent at least a portion of the interventricular groove, preferably adjacent at least a portion of the anterior and posterior portions of the interventricular groove, and more preferably adjacent at least a substantial portion of the anterior and posterior portions of the interventricular groove. In another embodiment, the yoke is sized and configured for placement adjacent at least a portion of the atrioventricular groove.
The present invention also includes an activator attached to the yoke for deforming the natural heart, which preferably includes a hydraulic lateral arm.
In use, the activator deforms a portion of the cardiac tissue by moving an arm from a relaxed condition to an activated condition. As the activator is pressing against the natural heart, the volume of at least one chamber of the natural heart is decreased so that blood is pumped out of the natural heart and into the circulatory system. Thereafter, the activator releases from against a portion of the cardiac tissue returns to the relaxed condition. The combination of the stint and yoke assist in returning the volume of the chamber so that at least one of the chambers of the natural heart ref1lls with blood and thus, the steps can be repeated.
Different forces can be applied to a natural heart for reducing the volume of atleast one of the chambers. These forces can include applying a torsion force or a shearing to the natural heart, flattening a portion of the cardiac tissue, applying a uniform pressure to the natural heart, and/or applying an indentation against at least one point on the exterior wall of the natural heart.
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.
BI~Tli',F ~ESCRIPTION OF THE DRAWINGS
While the specification concludes with clairns particularly pointing out and distinctly cl~iming the present inve~tion, it is believed the same will be better nn~lerstclod from the following description taken in COllj ull~;lion with the accompanied drawings in which:
Fig. 1 is a partial frontal anterior perspective view of an exemplary natural heart;
Fig. 2 is a perspective view of an int~rns~l stint and exterior yoke made in accordance with the present invention;
Fig. 3 is a partial cross-sectional view of a natural heart with a septal splint made in accordance with the present invention placed within a natural heart;
Fig. 4 is a partial frontal pt;l~c~ e view of a natural heart with an Pxtern~l yoke placed on a natural heart;
Fig. SA is a frontal ~ e~ e view of one embodiment of the extern~l yoke and activator of the present invention;
Fig. 5B is a frontal pe,~e~ e view of another embodiment of an f~tern~l yoke and activator of the present invention;
Fig. 6 is a top sectional ~ ;c view of a natural heart with an int~rn~l splinlt and an ext~rn~l yoke of the present invention illu~Lldled being conn~c~efl by 11~ .n. ,.1 cords;
Fig. 7A is a partial schem~tic view of an exemplary activator of the present invention in a relaxed condition; and Fig. 7B is a partial schematic view of an exemplary activator of the present invention in an activated condition.
DI~TAILED DESCRIPTI(~N OF THE PREFERRED EMBODIMENT
Referring now to the figures in detail wherein like numerals indicate the same elements throughout the views, a natural heart, generally indicated in Figure 1 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. A natural heart l0 also includes an upper portion having twochambers, a left atrium 16 and a right atrium 18, which primarily serve as an entryway 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 of cardiac tissue separating the left and right ventricles 12 and 14, respectively, is defined by an interventricular groove 20 on the exterior wall of the natural heart 10. The atrioventricular wall of cardiac tissue separating the lower ventricular region from the upper atrium region is I defined by atrioventricular groove 22 on the exterior wall of the natural heart 10.
Generally, each ventricle is in fluid communication with its respective atria through an atrioventricular valve. More specifically, the left ventricle 12 is in fluid communication with the left atrium 16 through the mitral valve, while the right ventricle 14 is in fluid communication with the right atrium 18 through the tricuspid valve.
Generally, the ventricles are in fluid communication with the circulatory system (i.e., the pulmonary and peripheral circulatory system) through semilunar valves. More specifically, the left J ~) C~
ventricle 12 is in fluid cornmunication with the aorta 26 of the peripheral circulatory system, through the aortic valve, while the right ventricle 14 is in fluid communication with the p~llm~nAry artery 28 of the pulmonary, circulatory system through the pulmonic valve.
By way of a non-limiting example, the present invention will be discussed in terms of embo~liment~ that are used to primarily assist in the activation and operation o~
the left ventricular portion of the natural heart 10, however, it is noted that the present invention can also be used to assist in the activation and operation of other portions of the natural heart 10, such as the atria, or the right ventricular portion of the natural heart 10. The present invention is a mech~niçRI activator, ill1lstrAted in Figure 2 as 50, which includes an int~rnRl stint 52. Furthermore, the present invention includes an external yoke 70 fixed to the internal stint 52 by trRnemnral cords 86. The internal stint 52 is sized and configured for placement within the interior volume of the natural heart 10, and includes a generally triangular shaped frame 53 that can be assembled from a plurality of interlocking struts, preferably an anterior, a posterior and a basal strut. The stint 52 also includes at least two separate ring structures, namely a first ring 56 sized and configured for rlAeçment R~ cçnt the atrioventricular valve annuli, and preferably jR~ the mitral valve annuli in the left atriurn 16, and a second ring 58 sized and configured for plAcçm~nt R~ cent the s~mill-nRr valve annuli preferably subjacent the aortic valve annuli in the lefL ventricle 12.
Figure 3 further illustrates a septal splint 54, which can include one or more - strands of sutures affixed to the frarne 53 through loops positioned on the frame 53, preferably the loops are affixed to the inner portion of frame 53, and more preferably, at about 1.5 cm intervals. The splint 54 can take the form of a tennis racket-like shaped configuration or a sno~vshoe like shaped configuration to brace or stabilize one side of the septum, preferably the right side of the interventricular septum without distortion of the chordae. Preferably, the septal splint 54 is positioned by stringing a heavymonofilament polypropylene suture, such as a #5 polypropylene suture, under, through, and behind the trabeculae, and through the loops as will be discussed later in great detail.
The f1rst and second rings 56 and 58 and the septal splint 52 are attached at least to each other using a connector element 59, such as a pin to assist in m~int~ining the relative position so that the first and second rings 56 and 58, respectively, and the splint 52 are supported while the natural heart 10 is being activated.
So that the components of the stint 52 (e.g., the septal splint 54 and f1rst andsecond rings 56 and 58) are not totally rigid and can exhibit an elastic quality, the components are preferably made of a stiff coil spring material covered with braided polyester. Localized adjustments can be made to the elasticity of the various components of the stint 52 to reduce the potential for problerns, such as ~l~m~ging the cardiac tissue or compromising the coronary circulation.
As illustrated in Figure 4, the device 50 also includes an external yoke 70 for placement around a portion of the exterior surface of a natural heart 10. The generally stirrup shaped yoke 70 restricts free motion of the natural heart 10 so that the natural heart 10 can be ac:tivated. Preferably, the yoke 70 can be between about 1 and 2 cm wide and includes a semi-rigid collar portion, preferably made of polypropylene, for providing lI
rigidity to the yoke 70. Additionally, the yoke 70 can include a gel-filled cu~hinn portion that is positioned imrnediately ad3acent exterior surface of the natural heart 10 for providing equalized pressure over the irregularities in the epicardial surface of the natural ~ heart 10, and preferably, any of the coronary arteries 30 within each region under the yoke 70. Preferably, the yoke 70 is sized and configured for plac~m~nt adjacent at least a portion of the atrioventricular groove 22, more preferably, at least a portion of the anterior and posterior portions of the interventricular groove 20, and most preferably, at least a substantial portion of the anterior and posterior portion of the interventricular groove. In yet another embodiment~ the yoke 70 is sized and configured for pl~cement adjacent at least a portion of the atrioventricular groove 22.
Referring now to Fig. 6, general alignment of the yoke 70 is m~ e~ by at least one ll;~ .ldl cord 86, and preferably, a plurality of cords 86 that penetrate the walls ofthe natural heart 10 and connect to the stint 52. The cord 86 is preferably made of a heavy braided, polymer-impregn~t~d polyester suture core (such as # 5 Ethiband~) by Ethicon, Inc.) covered in the h~ ocardial portion with a braided sleeve of polyester yarn to promote firm tissue growth around the cord 86. When it is necessary to utilize more than one cord 86 with the present invention, spacing of the cords 86 should preferably be at intervals of between about 15 mm to 20 mm along the yoke 70, from the septal splint 54 and the first ring 56 ext~n-ling obliquely outwardly toward the left ventricle exterior wall for inserl:ion into the left ventricle margin of the yoke 70.
More preferably, the cords 86 should be positioned for avoiding contact with the- coronary vessels 30. The cords 86 vary in length such that the splint 54 ~nd first ring 56 CA 022424l2 l998-06-30 are oriented beneath the gel-filled cushion portion while the septurn stint 52 and the first ring 56 are held stable in general ~ nment with the natural heart 10, and are generally not allowed to move away from the ventricular exterior wall when ples~ul~ iS applied to a natural heart 10 via by activator 74.
As mentioned above, the present invention also includes an activator 74 ~tt~-h~dto at least a portion of the yoke 70, preferably the apical portion 70a, as illustrated in Figures 5A and 5B. The activator 74 includes a lateral flexible arrn 75 generally having an "L" shaped configuration that extends approximately two-thirds of the distance between the apical portion 70a and base portion 70b of the yoke 70.
Connected to the arm 75 is at least one, and preferably a plurality of, bands 84~-xt~n~1ing away from the arm 75 sized and configured for p~ .çment ~ .ent the exterior surface of the natural heart 10. The distal ends of the bands 84 are tvpically affixed and secured along portions of yoke 70.
One embodiment of the yoke 70 and activator 74 is illustrated in Figure 5A in which the bands 84 extend perpendicularly away from the arm 75 and connect to the anterior and posterior portions of yoke 70. In another embodiment of the yoke 70 and activator 74 as illustrated in Figure 5B, bands 84 extend radially away from the distal end of the arm 75.
Pceferring now to Figures 7A and 7B, the activator 74 preferably has a hydrauliclateral arm 75 having a tubed-shape corrugated configuration with rings 77 affixed to the inner aspect of each corrugation. A plurality of longit~lin~lly exten~linF cords 76, preferably three or more, are affixed to the inner portion of arm 75, preferably the distal wo 97/24101 PCT/US97/00374 end of arrn 75 and also preferably to each of the rings 77. The cords 76 can vary in length, especially between the fixation points to each ring 77 for controlling the se~ ion distance between rings 77. In fluid comrnunication with the arm 75 via a- driveline 92 is a pump unit "P", such as pneumatic or a hydraulic pump for controlling or altering the fluid volume within the arm 75.
Figure 7A illustrates the arm 75 in a relaxed condition when fluid ~ Ule within arm 75 is at or below ambient levels and where the shape of arrn 75 is ~letçnnin~ by the ext~rn~l forces and the intrinsic stiffn~oc,s of arm 75. To utilize the present invention~
S~ within the arm 75 can be increased, preferably above ambient levels, so that the shape of the arm 75 is altered to an activated condition, as illustrated in Fig. 7B. The length dirr~ ce of the various cords 76 between the rings 77 controls the radius of curvature of the arm 75 and the direction of curvature at various portions along the longitudinal length of the arm 75. The amount of P1~ UI~. required within the arrn 75 must be sufficient to overcome the intrinsic stif~c of the arm 75 at arnbient con~ition~
and to facilitate the proper deform~tion of both the arm 75 and bands 84 so that the proper amount of pressure is applied to the exterior wall of the natural heart 10 to assist in s~l~ring (i.e., reducing) the volume of one or more rh~mh~r of a natural heart 10 (e.g., the left ventricle 12) to ,,,~ circ~ tinn ofthe blood through the circulatory system.
In a pler~ d embodiment, the arm 75 can be customized to apply dirrel~nl pressure to dirre~ portions of the natural heart 10. For example, varying the ~ meter of arm 75 along the longi~l~lin~l length can assist in controlling the curvature of arm 75.
Regions of the arm 75 needing less bending moment can have a smaller diameter and CA 022424l2 l998-06-30 WO 97/24101 PCT/USg7/00374 regions of the arm 75 where greater bending moments are ~l~fcllcd can have a larger diameter.
Various embo~liment~ of an activator 74 can be utilized with the present invention to achieve a change in the volume of one or more heart chambers. It is noted that any activator 74 used with the present invention should be sufficient so that the cardiac output of a typical adult is between about 3 l/min and about 30 l/min, and preferably bt;lwee about 5 l/min and 20 l/min.
In addition, there are various possible forces which can be used for activating, and thus altering the chamber volumes of the natural heart 10. The present invention can be ~ltili7~d to flatten the exterior wall of the natural heart 10 in a plane s~lbst~ntiS-lly perpendicular to the plane of the atrioventricular valves (e.g., a mitral valve) or ~lbs~ lly parallel to the septum. When utili7in~ such a force, the activator 74 should be configured to produce a flexion in the convex direction limited to between about 2.5 to 3.0 times the CU~ lul~ value of the exterior wall of the natural heart 10 during the diastolic portion of the cardiac cycle. Deflection in a concave direction is restricted only to those bands 84 extPn-ling away from the arm 75 and conn~ctin~ to the base portion 70b of yoke 70.
Also, an activator 74 can be used to apply a ~irOllll pl~ UlC; to ~ul~s~ lly theentire exterior wall of the natural heart 10.
Furtherrnore, the activator 74 can be used to indent the exterior wall of the natural heart 10 at more than one location, and preferably at two or three locations on either an exterior wall or the septum in a hemispheric or hemiellipsoid profile.
WO 97/24101 PC'r/lJS97/00374 Additionally, an activator 74 can apply a torsion force to at least a part of the natural heart 10 at various angles.
In yet another embodiment, the activator 74 can apply a shearing force to a portion of the lateral exterior wall, which is directed apically and is a basal sheer force applied on the right side of the stint 52.
When the orientation of the arm 75 is altered from the relaxed condition, which.is illu~lldled in Fig. 7A, to the activated condition, which is illustr~tP~d in Fig 7B, the arm 75 and the bands 84 deform and apply pressure against the exterior wall of the natural heart 10 for ~,ci~tin~ with or facilitating activation ofthe natural heart 10 (the systolic portion of the cardiac cycle). As a result, the volume of one or more chambers of the natural heart 10 is reduced and blood is pumped out of the natural heart 10 and into the circulatory system.
Following the activation (i.e., systolic portion of the cardiac cycle), the arm 75 and bands 84 release from against the cardiac tissue and return to their relaxed conllition The combin~tion ofthe stint 52 and the yoke 70 assists in retl-rning the deforrned portion of the natural heart 10 back to its pre-activation volume so that it can refill with blood during the diastolic portion of the cardiac cycle, so that the entire cardiac cycle can be repeated.
To posltion the device 50 into and around an Pxi~ting natural heart 10, open heart thoracic ~ul~ely is required. Clinically, sufficient ~n~Sth~ci~ is ~rlmini~tP~red to the patient and the thoracic cavity is opened using standard thoracic procedures.
Once the thoracic cavity is opened, circulation of blood to the natural heart 10must be bypassed so the present invention can be inserted into the patient. Referring initially to Fig. 2, the superior vena cava 26, the inferior vena cava (not shown), and aorta 26 are c~nn~ te~l The circulatory system is connected to a cardiopulmonary bypass machine so that circulation and oxidation of the blood are m~int~in~l during theprocedure. By way of example, the procedure ~liecl-eeed in detail will be for insertion of the present invention to assist in the activation and operation of the left ventricle 12.
Through an aortotomy and an interatrial groove left atriotomy, the first and second rings 56 and 58, le~e.;lively, are inserted and sutured in position. Preferably, the first ring 56 is positioned suprajacent the mitral annuli and the second ring 58 is positioned subjacent the aortic annuli.
The interlocking struts ofthe septal frame 53 (e.g., anterior, posterior, basal struts) are inserted into the right ventricle 14 through an apical ventriculotomy, a right atriotomy with partial teml~oldly ~letzl-~hm~nt of the septal tricuspid leaflet of the tricuspid valve, and an outflow tract ventriculotomy, respectively. Suture strands are then passed back and forth against the interventricular septum, threading through loops to provide a septal splint 54. In placement of both the various struts of frame 53 and the strands that form splint 54, care is taken to maneuver behind chordae and behind or through major trabeculae and bases of papillaTy muscles. The suture strands are tied to form the net-like configuration of the septal splint 54 that lies snugly against the septum, but allows it to ) norrnal ri~lLw~d collv~;~ily. Separate connector elements 59, preferably pins, Next, the left pleural cavity is opened and the yoke 70 is positioned behind thenatural heart lO. Cords 86 are assembled as 12" (30.5 cm) strands of suture with a polyester bead fused to one end and blunt straight needle on the other. Each suture is passed through a hole in the margin of the yoke 70, through the cardiac tissue, and S preferably the ventricular wall, and through the internal stint 52 (i.e., first ring 56 or septal splint 54) and anchored after length adjustment, with the excess portion of the sutures cut and. removed. Cords 86 are tightened to render the intrinsically flexible stint 52 relatively taut and control bulging, preferably in a rightwardly direction.
Cardiotomies are closed, and the activator 74 is attached to the yoke 70. The driveline 92 is attached to the drive unit "P" and all indicated monitoring lines are positioned. Preferably, Heparin-filled Teflon-coated polyurethane S Fr. catheters are brought through the posterior cervical incision into the chest and into the atrial appendages and an identical one into a branch of the innominate artery. Termination of a cardiopulmonary bypass 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, as discussed above, and auto-transplanting the natural heart l (~ back into the patient using standard cardiectomy and cardiac transplant techniques known in the industry.
~"~-?~ T
Having shown and described the preferred embodiments to the present invention, further adaptations of the activation device for the living heart as described herein can be accomplished by appropriate modifications by one of ordinary skill in the art without departing from the scope of the present invention. For example, the present invention can be used with any one or even a plurality of the various chambers of a living heart, and also could be used with different activators 74. Other examples of an activator 74 usable with the present invention include a girdle assembly that can be activated by hydraulics forces or other forces, such as an electromagnetic for using magnets and electrical current. Several such potential modifications have been discussed and others will be apparent to those skilled in the art. Accordingly, the scope of the present invention should be considered in terms of the following claims and is understood not to be limited in the details, structure and operation shown and described in its specification and drawmgs.
~ ~s ~
Claims (21)
1. An activation device for use with a natural heart for placement within the interior volume of a natural heart, said device characterized by the combination of a first ring configured for placement adjacent at least one of the valve annuli, a second ring configured for placement adjacent another of the valve annuli, and a first connector element joining said first and second rings.
2. The activation device of claim 1, wherein said device further comprises a septal splint configured for supporting at least a portion of a septal wall of the natural heart.
3. The activation device of claim 2, wherein said septal splint comprises a second connector element joining said first ring and said septal splint.
4. The activation device of claim 2, wherein said septal splint comprises a third connector element joining said second ring and said septal splint.
5. The activation device of claim 1, wherein said activation device further comprises a septal splint comprising a second connector element joining said first ring and said septal splint, and a third connector joining said second ring and said septal splint.
6. The activation device of claim 1, further comprising:
(a) a yoke configured for placement around a portion of the exterior surface of the natural heart in general alignment with said natural heart; and (b) at least one cord connecting one of said first ring and said second ring to said yoke.
(a) a yoke configured for placement around a portion of the exterior surface of the natural heart in general alignment with said natural heart; and (b) at least one cord connecting one of said first ring and said second ring to said yoke.
7. The activation device of claim 6, wherein said yoke is sized and configured for placement adjacent at least a portion of an atrioventricular groove of the natural heart.
8. The activation device of claim 6, wherein said yoke is sized and configured for placement adjacent at least a portion of an interventricular groove of the natural heart.
9. The activation device of claim 8, wherein said yoke is sized and configured for placement adjacent at least a portion of the anterior and posterior portions of said interventricular groove.
10. A mechanical ventricular activation device for use with a natural heart, said device comprising:
(a) a yoke configured for placement around a portion of the exterior surface of the natural heart in general alignment with said natural heart;
(b) an activator attached to said yoke;
(c) a stint configured for placement within the interior volume of a natural heart adjacent cardiac tissue thereof; and (d) at least one cord connecting said stint to said yoke.
(a) a yoke configured for placement around a portion of the exterior surface of the natural heart in general alignment with said natural heart;
(b) an activator attached to said yoke;
(c) a stint configured for placement within the interior volume of a natural heart adjacent cardiac tissue thereof; and (d) at least one cord connecting said stint to said yoke.
11. The device of claim 10, wherein said yoke comprises, an arm and;
a plurality of bands connected to said arm.
a plurality of bands connected to said arm.
12. The device of claim 11, wherein said plurality of bands extend away from said arm.
13. The device of claim 12, wherein said plurality of bands extend radially away from the distal end of said arm.
14. The device of claim 12, wherein said plurality of bands extend perpendicularly away from the distal end of said arm.
15. The device of claim 10, wherein said stint comprises a first ring configured for placement adjacent at least one of the atrioventricular annuli to stabilize and facilitate operation of a atrioventricular valve of the natural heart.
16. The device of claim 10, wherein said stint comprises a second ring configured for placement adjacent at least one of the semilunar annuli to stabilize and facilitate operation of a semilunar valve of the natural heart.
17. The device of claim 10, wherein said stint comprises a septal splint configured for stabilizing a septal wall of the natural heart.
18. The activation device of claim 10, wherein said stint comprises a first ring configured for placement adjacent at least one atrioventricular annuli, a second ring configured for placement adjacent at least one semilunar annuli, and a connector element joining said first and second rings.
19. The device of claim 15, wherein said stint comprises a septal splint configured for stabilizing a septal wall of the natural heart and a connector element joining said first ring and said septal splint.
20. The device of claim 16, wherein said stint comprises a septal splint configured for stabilizing a septal wall of the natural heart and a connector element joining said second ring and said septal splint.
21. The activation device of claim 10, wherein said stint comprises a septal splint configured for stabilizing a wall of the natural heart, a first ring configured for placement adjacent at least one atrioventricular annuli, a second ring configured for placement adjacent at least one semilunar annuli, a first connector element joining said first ring and said septal splint, and a second connector joining said second ring and said septal splint.
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US08/581,914 | 1996-01-02 | ||
| US08/581,914 US5957977A (en) | 1996-01-02 | 1996-01-02 | Activation device for the natural heart including internal and external support structures |
| PCT/US1997/000374 WO1997024101A1 (en) | 1996-01-02 | 1997-01-02 | Activation device for the natural heart and method of doing the same |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2242412A1 CA2242412A1 (en) | 1997-07-10 |
| CA2242412C true CA2242412C (en) | 2002-04-30 |
Family
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Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002242412A Expired - Fee Related CA2242412C (en) | 1996-01-02 | 1997-01-02 | Activation device for the natural heart and method of doing the same |
Country Status (7)
| Country | Link |
|---|---|
| US (3) | US5957977A (en) |
| EP (2) | EP0874614B1 (en) |
| AT (1) | ATE253346T1 (en) |
| AU (1) | AU1532597A (en) |
| CA (1) | CA2242412C (en) |
| DE (1) | DE69725962T2 (en) |
| WO (1) | WO1997024101A1 (en) |
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-
1996
- 1996-01-02 US US08/581,914 patent/US5957977A/en not_active Expired - Fee Related
-
1997
- 1997-01-02 EP EP97901421A patent/EP0874614B1/en not_active Expired - Lifetime
- 1997-01-02 EP EP03075901A patent/EP1332766A3/en not_active Withdrawn
- 1997-01-02 WO PCT/US1997/000374 patent/WO1997024101A1/en active IP Right Grant
- 1997-01-02 CA CA002242412A patent/CA2242412C/en not_active Expired - Fee Related
- 1997-01-02 AU AU15325/97A patent/AU1532597A/en not_active Abandoned
- 1997-01-02 DE DE69725962T patent/DE69725962T2/en not_active Expired - Fee Related
- 1997-01-02 AT AT97901421T patent/ATE253346T1/en not_active IP Right Cessation
-
1998
- 1998-09-30 US US09/165,887 patent/US6221103B1/en not_active Expired - Fee Related
-
2001
- 2001-04-13 US US09/834,339 patent/US20020022880A1/en not_active Abandoned
Also Published As
| Publication number | Publication date |
|---|---|
| ATE253346T1 (en) | 2003-11-15 |
| EP0874614A1 (en) | 1998-11-04 |
| AU1532597A (en) | 1997-07-28 |
| US20020022880A1 (en) | 2002-02-21 |
| DE69725962D1 (en) | 2003-12-11 |
| WO1997024101A1 (en) | 1997-07-10 |
| EP1332766A2 (en) | 2003-08-06 |
| DE69725962T2 (en) | 2004-05-06 |
| US5957977A (en) | 1999-09-28 |
| US6221103B1 (en) | 2001-04-24 |
| CA2242412A1 (en) | 1997-07-10 |
| EP1332766A3 (en) | 2004-01-07 |
| EP0874614B1 (en) | 2003-11-05 |
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Legal Events
| Date | Code | Title | Description |
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| EEER | Examination request | ||
| MKLA | Lapsed |