US20020065449A1 - Cardiac reinforcement device - Google Patents
Cardiac reinforcement device Download PDFInfo
- Publication number
- US20020065449A1 US20020065449A1 US10/058,475 US5847502A US2002065449A1 US 20020065449 A1 US20020065449 A1 US 20020065449A1 US 5847502 A US5847502 A US 5847502A US 2002065449 A1 US2002065449 A1 US 2002065449A1
- Authority
- US
- United States
- Prior art keywords
- heart
- fluid
- inflation
- recited
- recoil
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Abandoned
Links
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/24—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
- A61F2/2478—Passive devices for improving the function of the heart muscle, i.e. devices for reshaping the external surface of the heart, e.g. bags, strips or bands
- A61F2/2481—Devices outside the heart wall, e.g. bags, strips or bands
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- 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
- A61M60/161—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 mechanically acting upon the outside of the patient's blood vessel structure, e.g. compressive structures placed around a vessel
-
- 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
- A61M60/247—Positive displacement blood pumps
- A61M60/253—Positive displacement blood pumps including a displacement member directly acting on the blood
- A61M60/268—Positive displacement blood pumps including a displacement member directly acting on the blood the displacement member being flexible, e.g. membranes, diaphragms or bladders
-
- 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
- A61M60/40—Details relating to driving
- A61M60/465—Details relating to driving for devices for mechanical circulatory actuation
- A61M60/468—Details relating to driving for devices for mechanical circulatory actuation the force acting on the actuation means being hydraulic or pneumatic
-
- 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
- A61M39/00—Tubes, tube connectors, tube couplings, valves, access sites or the like, specially adapted for medical use
- A61M39/02—Access sites
- A61M39/0208—Subcutaneous access sites for injecting or removing fluids
- A61M2039/0211—Subcutaneous access sites for injecting or removing fluids with multiple chambers in a single site
Definitions
- the present invention relates to devices and methods for treating cardiomyopathy, a chronic disorder of the heart muscle, and more particularly to an implantable ventricular restraint device which is adapted to confine and control ventricular diastolic expansion.
- Cardiac dilation occurs with various diseases of the heart, including heart failure.
- the dilation may be localized to only a portion of the heart.
- cardiomyopathy usually results in global impairment.
- hypertrophic cardiomyopathy there is typically increased resistance to filling of the left ventricle with accompanying dilation of the left atria.
- dilated cardiomyopathy the dilation is typically of the left ventricle with resultant failure of the heart as a pump. As the ventricles become enlarged, the situation is worsened by the resultant leakage which develops around the valvular structures. A sharply reduced ejection fraction is the hallmark of this condition.
- Dynamic cardiomyoplasty is one treatment currently being used to treat cardiomyopathy.
- One current approach being used to treat this disorder is a procedure that involves wrapping and attaching a portion of a patient's own latisimus dorsi muscle around the heart, as described, for example, in the article Reverse Remodeling from Cardiomyoplasty in Human Heart Failure, Circulation, May 1, 1995, Vol. 91, No. 9 (Kass et al.).
- a pacemaker-like electrical stimulator is then attached to both the heart and the wrapped muscle. After a healing period, the wrapped muscle is electrically stimulated in synchrony with the heart which causes the muscle to contract at the appropriate time. This action actively squeezes the ventricles of the heart, to augment their function.
- a reversal of the heart's chronic dilated condition has been found to result in many cases, and current medical opinion is that patients with chronic heart failure may be cured of symptoms by providing assistance to ventricular function using this or similar methods. Some have also considered the benefits of merely wrapping or constraining the heart with skeletal muscle without providing active systolic assist. In any event, it will be appreciated that, although this method of treatment has proven effective, it is an open surgical procedure, which involves both removal of the patient's latisimus dorsi muscle and reattachment of the same to the heart. The frequency of the electrical stimulation, if employed, is the only adjustment that a medical professional can make to optimize the treatment for individual patients using this technique.
- U.S. Pat. No. 5,702,343 to Alferness discloses a device comprising a jacket of biocompatible material, which is applied to and adjusted to fit the epicardial surface of the heart. The device, once placed, controls cardiac expansion to a predetermined size.
- an inflatable member is provided which is mounted between the jacket and the epicardium for selectively adjusting the size of the jacket as the heart remodels and reduces in size responsive to treatment, but there is no disclosed or suggested provision for regulating the size of the device without surgical intervention.
- the dilation has already occurred and the patient is in chronic disorder.
- the constraining device cannot be effectively and easily resized as the heart begins to remodel, it may not continue to be effective, and the possibility for a maximum remodeling of the heart may be reduced.
- Another drawback to the disclosed approach of Alferness is that the disclosed device applies a uniform force to both right and left ventricles. Typically, the left ventricle is the one that causes the disorder as it operates at much higher pressures. This design does not provide the medical professional with any means to accurately optimize or monitor the device's therapeutic effect.
- the optimal operating parameters for the device may vary dramatically from patient to patient, and these parameters can again change over time as the patient's heart becomes accustomed to the device or goes through a remodeling phase.
- the present invention addresses the problems outlined above by providing a unique device for treating heart disorders, and particularly cardiomyopathy, comprised of a compliant containment structure shaped in a configuration such that it surrounds and encases the heart.
- a compliant containment structure shaped in a configuration such that it surrounds and encases the heart.
- Within this containment structure are housed two or more inflation pockets that are fabricated from a non-elastic compliant material. These pockets are disposed on the interior surface of the containment structure and are configured to oppose and support the external wall of at least one of the ventricles of the heart.
- there are a plurality of relatively small, spaced inflation pockets disposed to act against each ventricle which is to be contained.
- a recoil balloon On the external surface of the containment structure, or spaced therefrom, there is disposed a recoil balloon, which is configured from an elastomeric material.
- the containment structure physically separates the inflation pockets from their associated recoil balloon(s). However, a fluid flow path is provided between the pockets and their associated balloon(s).
- Each recoil balloon has an inflation delivery tube which is in turn fluidly connected to a fluid access port which delivers fluid to the device as needed.
- FIG. 1 is a schematic, perspective view of a first embodiment of the present invention
- FIG. 2 is a schematic exploded view of the embodiment illustrated in FIG. 1;
- FIG. 2 a is a schematic exploded view similar to that of FIG. 2, illustrating a somewhat modified version of the embodiment illustrated in FIG. 1;
- FIG. 3 is a schematic perspective view of a second embodiment of the present invention.
- FIG. 4 is a schematic exploded view of the embodiment illustrated in FIG. 3;
- FIG. 5 is a cross-sectional view of a portion of the device illustrated in FIGS. 1 and 2, wherein the inflation pocket which forms a part of the invention is in an inflated state;
- FIG. 6 is a cross-sectional view similar to FIG. 5, illustrating a portion of the device shown in FIGS. 1 and 2, during the fluid exchange phase;
- FIG. 7 is a cross-sectional view similar to FIG. 6, illustrating a portion of the device shown in FIGS. 3 and 4, wherein the inflation pocket and secondary recoil balloon are in a filled state;
- FIG. 8 is a cross-sectional view similar to FIG. 7, illustrating a portion of the device shown in FIGS. 3 and 4, during the fluid exchange phase;
- FIG. 9 is a perspective view of the containment structure which forms a part of the inventive device.
- FIGS. 10A and 10B are plan views, in isolation, of the inflation pockets which form a part of the inventive device;
- FIG. 11 is a plan view, in isolation, of the recoil plate which forms a part of the second configuration of the inventive device illustrated in FIGS. 3 and 4;
- FIG. 12 is a schematic view illustrating the placement of the fluid access port which forms a part of the present invention.
- FIG. 13 is a schematic view illustrating yet a third embodiment of the inventive device.
- FIG. 14 is a perspective view illustrating a fourth preferred embodiment of the invention.
- FIG. 14 a is a perspective view illustrating a modified version of the fourth embodiment shown in FIG. 14;
- FIG. 14 b is a cross-sectional view of a portion of the embodiment illustrated in FIG. 14 a;
- FIG. 15 is a front elevational view showing the embodiment of FIG. 14 after it has been placed about a heart, with a bypass graft in place;
- FIG. 16 is a cross-sectional view of the embodiment illustrated in FIG. 14, showing in detail the inflation pockets of the invention
- FIG. 17 is a conceptual graphical plot of the cyclical pressure measured by an external pressure monitor for the device illustrated in FIG. 14 when it is installed on a heart and working full time (i.e. in contact with the heart full time);
- FIG. 18 is a conceptual graphical plot similar to that of FIG. 17 of the cyclical pressure measured by an external pressure monitor for the device illustrated in FIG. 14 when it is installed on a heart but not in contact with the external surface of the heart full time (i.e. it needs to be re-sized by addition of fluid); and
- FIG. 19 is a schematic view illustrating a system for monitoring pressure and/or providing counter-pulsating assist for any one of the embodiments illustrated in FIGS. 1 - 18 .
- FIGS. 1, 2, 5 , and 6 there is shown in FIGS. 1, 2, 5 , and 6 a first embodiment of a cardiac reinforcement device 10 of the present invention which comprises a frame or containment structure 12 preferably formed of a high strength biocompatible mesh-like material, such as polyester fully or partially encased or embedded within a flexible biocompatible material such as silicon or polyurethane, preferably using an injection process.
- the high strength mesh serves three primary purposes. First, it provides a strong, flexible non-elastic support for the containment structure. Second, it serves as a tear-resistant material which can be sutured to the heart muscle easily. Third, it is lightweight, and provide bypass graft access, as will be described more fully hereinbelow.
- silicon in particular, is that it has a long history of biocompatibility and provides a good surface to which other items may be attached.
- suitable biocompatible materials such as polyurethane, may be selected as well, as long as the resultant structure is compliant, but not elastic. It is also within the scope of the invention to employ an alternative configuration involving a polymer frame construction as opposed to the described mesh construction.
- the encasing elastomer for the frame or containment structure 12 may be transparent so that a practitioner can see and avoid suturing the device 10 too close to blood vessels.
- the containment structure 12 includes one or more slits 14 along which a series of holes 16 may be provided.
- a biocompatible lace 18 such as polyester, the slits may be laced up as illustrated in FIG. 1, for example, to optimize the size of the frame 12 for variously sized hearts.
- VELCRO hook and loop fastening straps 18 a , 18 b may be provided along each side of the slit. This alternative is illustrated in FIG. 2 a .
- the VELCRO straps 18 a are overlapped to provide an accurate fit, then sutures 19 are made through the VELCRO overlap to secure the sizing permanently.
- Port holes 20 are preferably provided in the frame 12 to provide a fluid flow path and permit the exchange of fluid from a plurality of inflation pockets 22 (FIG. 1) to a recoil balloon 24 .
- the inflation pockets 22 (in this embodiment two are provided) are preferably formed of a composite structure made from a high strength biocompatible mesh-like material such as polyester fully encased within a flexible biocompatible material such as silicon or polyurethane (this may be the same material from which the frame or containment structure 12 is fabricated). These components essentially comprise balloons which are flexible and compliant with very low elasticity. Their purpose is to support the outer wall of the heart ventricle.
- the two provided inflation pockets 22 are of different configurations, and are asymmetrically located, due to the fact that the respective ventricles which they support are different in both configuration and location, with the left ventricle being much larger than the right ventricle. It should be noted that it is within the scope of the invention to provide more than two inflation pockets 22 if desired, since configurations wherein more than one pocket 22 supports a single ventricle may be potentially beneficial in certain instances. Such an embodiment, presently preferred, is illustrated in FIGS. 14 - 16 .
- the recoil balloon 24 is preferably fabricated of a thin high elasticity biocompatible material such as silicon or polyurethane. This component comprises a balloon which may be joined to the exterior surface of the frame or containment structure 12 over the port holes 20 , as shown particularly in FIG. 2.
- a fluid access port 26 is implanted under the patient's skin 27 (FIG. 12) for providing access through which fluid can be delivered to two different device locations. It is preferably constructed of a variety of biocompatible materials, including titanium, polysulfone, polyurethane, and silicon. Similar ports are known in the prior art for use as vascular access ports which are implanted in patients for long-term infusion of medications.
- the port 26 comprises a plurality of elastomeric septums 28 which can be punctured and accessed frequently with a hypodermic needle (not shown). The septum material properties are such that they self-seal upon removal of the needle.
- a fluid line 30 conveys fluid, comprising saline or other suitable fluid, which may include both liquids and gases, from the fluid access port 26 to the recoil balloons 2 on either side of the frame 12 (only one balloon 24 is shown in FIGS. 1 and 2, but in the first embodiment there is preferably one recoil balloon associated with each inflation pocket 22 ).
- the fluid line traverses the patient's muscle 32 , adjacent to the bone 34 (FIG. 12), and preferably comprises dual lumen tubing made from a biocompatible material such as silicon or polyurethane.
- a bifurcation 36 occurs at the distal end of the fluid line 30 , and two separate tubes 38 and 40 , each communicating with one of the two lumen (not shown), carry fluid to their corresponding recoil balloons.
- each of the lumen also corresponds to one of the two elastomeric septa 28 illustrated for this embodiment, so that the result is an ability to separately control the fluid conveyed to each recoil balloon 24 .
- FIGS. 3, 4, 7 , and 8 FIGS. 9 - 12 are common to both embodiments), wherein like elements to those in the first embodiment are denoted by like reference numerals, increased by 100 .
- the primary difference between this embodiment and the embodiment of FIG. 1 is the provision of a second recoil balloon 160 (FIG. 4) which “piggy-backs” directly over the first recoil balloon 124 .
- a second set of recoil balloons 160 is preferably provided on the opposing side of the frame 112 for operation with the second inflation pocket 122 (not shown).
- a pressure isolator plate 162 having a plurality of port holes 164 , is disposed between the frame 112 and the inner recoil balloon 124 .
- the pressure isolator plate, or recoil plate 162 is preferably made of a rigid plastic material. Additionally, a second fluid access port 126 ′ is provided, having two septa 128 ′ and a fluid line 130 ′. The fluid access port 126 is arranged to supply fluid to the two recoil balloons 124 and 160 disposed on one side of the frame 112 , splitting at the bifurcation 136 (FIG. 3) so that the tube 138 from one lumen supplies the recoil balloon 124 , and the tube 140 from the other lumen supplies the recoil balloon 160 . Similarly, the fluid access port 126 ′ independently supplies the two recoil balloons (not shown) disposed on the other side of the frame 112 .
- the practitioner may independently and selectively supply differing quantities of fluid to each of the two recoil balloons disposed in a set on each side of the frame 112 , and also independently supply fluid to each set of recoil balloons.
- all of the recoil balloons, whether in the same set or in different sets, are isolated from one another, and may be independently pressurized.
- the second recoil balloon 160 may be comprised of the same material as the first recoil balloon, or it may alternatively have different material properties.
- a second fluid chamber 166 (FIG. 6) is provided between the first and second recoil balloons.
- the pressure isolator plate, or recoil plate 162 is utilized only in the second embodiment because when the secondary recoil balloon 160 is partially inflated, it puts a compressive load on the inner recoil balloon 124 , which in turn compresses the frame wall causing increased pressure on the inflation pocket 122 .
- the purpose of the plate 162 is to isolate those forces.
- the system may be constructed as shown in either the first or second embodiments.
- the fluid access port 26 , 126 , 126 ′ is augmented by a pressurized fluid reservoir system 280 having a one-way valve 281 , such as a duckbill valve, for example.
- a pressurized fluid reservoir system 280 having a one-way valve 281 , such as a duckbill valve, for example.
- fluid from the reservoir 280 may be automatically added to each of the inflation pockets 22 , 122 if and when the pressure in the inflation pockets drops below a predetermined value.
- the fluid reservoir system 280 comprises a biasing device, such as a constant force spring 283 , a fluid reservoir 284 , and a seal 284 a disposed between the fluid reservoir 284 and the spring 283 .
- a biasing device such as a constant force spring 283 , a fluid reservoir 284 , and a seal 284 a disposed between the fluid reservoir 284 and the spring 283 .
- the spring 283 moves back as fluid enters from the fluid access port 26 , 126 , 126 ′, and moves forward to push fluid out of the device.
- the fluid reservoir pressure equals the spring force, which is always maintained as long as fluid is present.
- a cardiac reinforcement device 310 constructed in accordance with this embodiment comprises a containment structure 312 which is preferably fabricated entirely of a high strength biocompatible mesh-like material, such as polyester.
- This construction as compared to the mesh and frame construction disclosed in connection with the prior embodiments, provides a benefit of a lighter weight structure with less bulk, and therefore greater compliance, which minimizes the impairment of cardiac function.
- the mesh construction for this preferred embodiment may be constructed with a square pattern, if desired, and could resemble a hair net in appearance.
- this embodiment is particularly suited to the accommodation of one or more existing bypass grafts 384 (FIG. 15) which may be present on the patient's heart 385 .
- a device constructed as illustrated in the first three embodiments may not be as suited to this type of condition, because the inflation pocket may cover and compress the bypass vessel, causing a restriction in the blood flow.
- cardiomyopathy large dilation of the heart
- the present embodiment comprises a plurality of multiple small inflation pockets 322 , rather than the fewer, larger inflation pockets disclosed in the previous embodiments.
- the multiple inflation pockets 322 simulate the appearance of bubble wrap, but are spaced apart enough to provide a sufficient clearance between them to accommodate an existing bypass graft 384 , or to allow a subsequent bypass graft 384 to be attached. Because the inflation pockets 322 are spaced, and small, no one pocket 322 should cover and compress the bypass vessel sufficiently to cause undesirable blood flow restriction. If, however, that is the case, because of the number of inflation pockets 322 , one or more of them can be removed during the installation procedure to accommodate the existing bypass graft 384 .
- this preferred embodiment overcomes the problems discussed supra, related to the unavailability of sufficient space for the recoil balloons of the prior embodiments in the event of a severely enlarged heart, by reducing the side profile and relocating the recoil balloons away to a location where space is not at a premium.
- the device otherwise functions in substantially the same manner as in the previous embodiments.
- the bypass graft is routed around the exterior surface of the structure 312 .
- the large number of access holes 320 provided in the mesh material increase the likelihood that the graft can be attached without removing the device 310 .
- the material comprising the structure 312 is capable of being cut to provide additional access holes without compromising the mechanical integrity of the device. In some instances, it may even be preferably to provide fewer and/or smaller access holes 320 , and to just be prepared to cut additional holes during a later bypass procedure, for the purpose of access. In the prior embodiments illustrated in FIGS.
- the multiple inflation pockets 322 associated with each ventricle are linked together, in that they are all attached to one of the septums 328 of the fluid access port 326 , as illustrated in FIG. 14.
- the fluid line 330 attached to each of the septums 328 which is preferably of a dual lumen construction, as discussed supra in connection with the prior embodiments, includes at its distal end a plurality of smaller fluid delivery tubes 386 , which are each individually fluidly connected to a separate inflation pocket 322 disposed over an associated ventricle.
- the inventive system may be adapted to fill the inflation pockets 322 for a particular ventricle in parallel, or in series, as desired, so that the pockets 322 may be, for example, filled in series from the base to the top of the structure 312 as the associated ventricle expands in a similar manner, or, alternatively, may be filled simultaneously.
- the recoil balloons 324 are disposed in each fluid line, remote from the structure 312 , rather than being attached to the exterior surface of the frame 312 , as in prior embodiments.
- the balloons 324 are preferably fabricated of a thin high elasticity biocompatible material such as silicon or polyurethane. This arrangement offers the benefit of reducing the space that the device occupies immediately around the heart, and instead permits the disposition of the balloons 324 elsewhere in the chest cavity where space may not be as restricted.
- One other advantage of this construction is that the balloons may be changed out by utilization of only a minor surgical procedure, involving only the removal of easily detachable fittings 387 (FIG. 14), such as Luer Locks, in the event that balloons with different pressure capacity or recoil properties would be of benefit.
- FIGS. 14 a and 14 b Another version of this preferred embodiment is illustrated particularly in FIGS. 14 a and 14 b .
- This embodiment is very similar to that of FIG. 14, except that a double recoil balloon, comprised of a pair of inner and outer recoil balloons 324 , 360 is utilized, rather than a single recoil balloon 324 .
- This is similar in concept to the embodiment illustrated in FIG. 4, with back-to-back recoil balloons 124 , 160 .
- the detachable fitting 387 comprises a male Luer Lock 387 a and a female Luer Lock 387 b .
- Lumen 330 a provides a fluid line for filling the inner balloon 324
- lumen 330 b provides a fluid line for filling the exterior balloon 360 .
- a fluid line block 330 c forces fluid to enter the outer balloon 360 through an entry port 330 d .
- Passage 387 c in the female Luer Lock 387 b provides an exit port for fluid exiting the interior recoil balloon 324 for the inflation pockets.
- the exterior balloon 360 becomes distended and causes an increase in the filling pressure for the interior balloon 324 .
- a third elastomeric septum 388 is provided in the fluid access port 326 (FIG. 14), which is attached to a drug delivery line 389 .
- a distal portion 390 of the drug delivery line 389 is arranged to wrap around the exterior surface of the structure 312 , as illustrated in FIG. 14, and is provided with a plurality of drug flow holes 391 spaced therealong where the distal portion 390 is in proximity to the pericardium, to ensure the uniform delivery of the drug at its intended site.
- the drug flow holes 391 may also be used to remove fluid from the pericardium area if this become necessary.
- the device 10 , 110 , 310 is installed for operation on a patient's heart by first removing or opening up the pericardium (not shown).
- the frame or containment structure 12 , 112 , 312 is then placed over the heart with the inflation pockets 22 , 122 , 322 disposed adjacent to one or both of the ventricles.
- the device can be accurately sized to the heart (the frame 312 is sufficiently elastic, being comprised entirely of flexible mesh material, that no slits are required).
- the frame is then securely sutured to heart muscle to ensure that it cannot migrate from its intended location and also to isolate the forces on the right and left sides of the device during use.
- the fluid access ports 26 , 126 , 126 ′, 326 are then attached to the chest just under the patient's skin 27 , as illustrated in FIG. 12.
- the pressurized fluid reservoir 280 and one-way valve 282 are appropriately positioned within the patient's thoracic cavity (not shown).
- the inflation pockets 22 , 122 , 322 are empty and completely collapsed.
- the device is actuated by introducing fluid into the inflation pockets. In the FIG. 12 embodiment, this is accomplished by the employment of a pressure monitoring syringe filled with saline or another suitable fluid.
- a needle is attached to the syringe and then inserted through the patient's skin 27 and into the septum 28 , 128 , 128 ′, 328 of the fluid access port 26 , 126 , 126 ′, 326 and the fluid is injected.
- FIGS. 5 and 7 illustrate each of the first and second disclosed embodiments wherein the inflation pockets 22 and 122 , respectively, are in their filled state.
- pressurized fluid will initially be introduced into the system from the pressurized fluid reservoir 280 , through the one-way valve 282 , rather than manually via a syringe.
- operation of the third embodiment is substantially similar to that described above with respect to the first, second, and fourth embodiments, and, in fact, any of the first, second, and fourth embodiments can utilize an automated fluid pressurization system as shown in the third embodiment.
- the device 10 , 110 , 310 functions by assisting the failing and dilating heart muscle.
- the device provides a substantially constant external restraining force, which increases as the ventricle goes from a systolic to a diastolic state.
- a ventricle As a ventricle is filled, it dilates and compresses its adjacent inflation pockets 22 , 122 , 322 . This, in turn, reduces the volume of the inflation pockets. This is because, in the first two embodiments, the fluid is permitted to escape through the port holes 20 , 120 in the frame 12 , 112 into the recoil balloon 24 , 124 on the external surface of the frame 12 , 112 , as shown in FIGS.
- the fourth embodiment operates a little differently, because the recoil balloons 324 are disposed remotely from the containment structure 312 , in the fluid lines 330 .
- the fluid is displaced from the inflation pockets and is permitted to escape in a backwards direction through the fluid tubes 386 into the fluid line 330 , which leads to the recoil balloon 324 .
- the volume of the inflation pockets decreases, the volume of the recoil balloon increases by an equal amount.
- the volume of the recoil balloons in order for the fluid to enter the recoil balloons, the volume of the recoil balloons must increase.
- the wall of the balloons 24 , 124 , 324 must be forced to stretch and dilate.
- the force required to dilate these balloons increases as the volume increases, which in turn places a larger restraining force on the heart.
- the inflation pockets 22 , 122 , 322 will no longer be assisting the ventricle through the full operating cycle. This condition can be easily corrected by repeating the set-up procedure and observing the pressure wave. If a reduction of the size of the heart has occurred, the pressure wave will not be constant and, by simply adding additional fluid to the inflation pockets 22 , 122 , 322 via the fluid access ports 26 , 126 , 326 , the inner boundary size of the device will shrink and it can again be made to assist the heart through its full operating cycle.
- the third embodiment illustrated in FIG. 13 offers a means for accomplishing the foregoing re-sizing process automatically.
- the practitioner can leave the patient for longer durations without making pressure volume adjustments to the inflation pockets 22 , 122 , 322 .
- fluid is automatically added to the inflation pockets whenever a predetermined pressure low occurs, and is therefore self-adjusting until the reservoir is emptied.
- the second disclosed embodiment offers a particular benefit in that if the practitioner determines that a patient would benefit from the application of a higher restraining force, such can be done by introducing additional fluid into the second fluid cavity 166 between the first and second recoil balloons, via the additional available fluid access port. Fluid forced into this space 166 will stretch the surface of the balloon 160 , as illustrated in FIG. 7, thereby creating a greater resistance to the filling of the inner recoil balloon 124 , which in turn increases the restraining force placed upon the heart. This adjustment may be made to any or all recoil balloons, as desired.
- a major advantage of this design is that if a patient has an adverse reaction to the restraining forces of the frame 12 , 112 , 312 immediate relief may be obtained by removing fluid from the inflation pockets via the fluid access ports 26 , 126 , 126 ′, 326 .
- the inflation pockets disclosed in any of the foregoing embodiments may be coated, if desired, with a drug infused osmosis material. If this is the case, the drug may leach out slowly for a term immediately after placement of the inventive device over a patient's heart, thereby aiding recovery.
- FIGS. 17 - 19 there is illustrated a minimally invasive arrangement for monitoring and accurately measuring diastolic and systolic pressures and performance in an entirely new way.
- This data can be used for diagnostic purposes, to optimize the adjustment of the device, and/or to monitor therapy.
- the fluid access port 26 , 126 , 326 of the device 10 , 110 , 310 is directly attached, via a connecting flow line 492 , to an external pressure monitoring system 493 (FIG. 19).
- This system may comprise a monitor, or a pulsating pump.
- a needle 494 is placed into the elastomeric septum 28 , 128 , 328 , which, in turn, is attached to the connecting flow line 492 using, for example, a Luer lock connector 494 a .
- diastolic expansion will cause the pressure inside the device to increase, and systolic contraction will cause the pressure to decrease.
- This pressure change occurs along the entire fluid path between the device and the pressure monitoring system, so that the monitoring system 493 receives data that translates into a complete pressure wave, as illustrated in FIGS. 17 and 18, which each represent generalized plots of pressure change over time.
- FIGS. 17 and 18 each represent generalized plots of pressure change over time.
- the data plots a full pressure SIN wave 495 , with a peak diastolic pressure 496 and a minimum systolic pressure 497 .
- the pressure only changes while a compressive force between the device and the ventricle is in effect.
- This results in a partial pressure wave 498 with a flat spot 499 which represents the period of time x during which the device is not in contact with the ventricle, and thus is doing no work.
- the practitioner viewing the plot on the monitoring device 493 , would recognize the need to add fluid to resize the device to optimize its fit, as described supra, in order to ensure that it is working full time.
- the inventive device has been disclosed as primarily having utility as a passive heart restraining or constraining device, it is within the scope of this invention to also provide direct active assistance to the heart if cardiac dysfunction occurs. This may happen immediately after installation of the device or at any time thereafter. In this mode of use, the device is used to provide systolic assistance instead of diastolic restraint. In order to achieve this, the fluid access ports of the device are directly attached to an external pump monitoring system 493 , as illustrated in FIG. 19, for the purpose of controlling systolic inflation of the inflation pockets 322 by means of counter pressure pulsation.
- a needle 494 is placed into and attached to each fluid access port, which in turn is attached to an independent flow line 492 which is connected to the pump/monitoring system. Due to the rapid pulse rate required to achieve success with this procedure, it is preferred to use a low inertia medium, such as helium, as the fluid for activating the device 310 .
Abstract
A unique device is provided for treating heart disorders, and particularly cardiomyopathy. The inventive device is comprised of a compliant containment structure shaped in a configuration such that it surrounds and encases the heart. Within this containment structure are housed two or more inflation pockets that are fabricated from a non-elastic compliant material. These pockets are disposed on the interior surface of the containment structure and are configured to oppose and support the external wall of at least one of the ventricles of the heart. In the preferred embodiment, there are a plurality of relatively small, spaced inflation pockets disposed to act against each ventricle which is to be contained.
Description
- This application claims the benefit of U.S. Provisional Application Serial No. 60/113,232, filed Dec. 21, 1998, which is commonly owned and the contents of which are expressly incorporated herein by reference.
- The present invention relates to devices and methods for treating cardiomyopathy, a chronic disorder of the heart muscle, and more particularly to an implantable ventricular restraint device which is adapted to confine and control ventricular diastolic expansion.
- Cardiac dilation occurs with various diseases of the heart, including heart failure. In some instances, such as ischemic heart disease, the dilation may be localized to only a portion of the heart. On the other hand, cardiomyopathy usually results in global impairment. In the case of hypertrophic cardiomyopathy, there is typically increased resistance to filling of the left ventricle with accompanying dilation of the left atria. In dilated cardiomyopathy, the dilation is typically of the left ventricle with resultant failure of the heart as a pump. As the ventricles become enlarged, the situation is worsened by the resultant leakage which develops around the valvular structures. A sharply reduced ejection fraction is the hallmark of this condition.
- Dynamic cardiomyoplasty is one treatment currently being used to treat cardiomyopathy. One current approach being used to treat this disorder is a procedure that involves wrapping and attaching a portion of a patient's own latisimus dorsi muscle around the heart, as described, for example, in the articleReverse Remodeling from Cardiomyoplasty in Human Heart Failure, Circulation, May 1, 1995, Vol. 91, No. 9 (Kass et al.). A pacemaker-like electrical stimulator is then attached to both the heart and the wrapped muscle. After a healing period, the wrapped muscle is electrically stimulated in synchrony with the heart which causes the muscle to contract at the appropriate time. This action actively squeezes the ventricles of the heart, to augment their function. A reversal of the heart's chronic dilated condition has been found to result in many cases, and current medical opinion is that patients with chronic heart failure may be cured of symptoms by providing assistance to ventricular function using this or similar methods. Some have also considered the benefits of merely wrapping or constraining the heart with skeletal muscle without providing active systolic assist. In any event, it will be appreciated that, although this method of treatment has proven effective, it is an open surgical procedure, which involves both removal of the patient's latisimus dorsi muscle and reattachment of the same to the heart. The frequency of the electrical stimulation, if employed, is the only adjustment that a medical professional can make to optimize the treatment for individual patients using this technique.
- Another approach which has been considered to address this disorder is disclosed in U.S. Pat. No. 5,702,343 to Alferness. This patent discloses a device comprising a jacket of biocompatible material, which is applied to and adjusted to fit the epicardial surface of the heart. The device, once placed, controls cardiac expansion to a predetermined size. In one embodiment, an inflatable member is provided which is mounted between the jacket and the epicardium for selectively adjusting the size of the jacket as the heart remodels and reduces in size responsive to treatment, but there is no disclosed or suggested provision for regulating the size of the device without surgical intervention. In many cases, by the time it becomes evident that the patient is in need of treatment for cardiomyopathy, the dilation has already occurred and the patient is in chronic disorder. If the constraining device cannot be effectively and easily resized as the heart begins to remodel, it may not continue to be effective, and the possibility for a maximum remodeling of the heart may be reduced. Another drawback to the disclosed approach of Alferness is that the disclosed device applies a uniform force to both right and left ventricles. Typically, the left ventricle is the one that causes the disorder as it operates at much higher pressures. This design does not provide the medical professional with any means to accurately optimize or monitor the device's therapeutic effect. The optimal operating parameters for the device may vary dramatically from patient to patient, and these parameters can again change over time as the patient's heart becomes accustomed to the device or goes through a remodeling phase. There is typically a very small imbalance in operating forces that causes the problem and therefore a very small force is sometimes all that is required to correct the condition. Consequently, in the event that the patient were to have an adverse reaction to the device's preset configuration, an urgent surgical intervention would need to be performed to remedy the problem.
- What is needed, therefore, is an improved ventricular reinforcement device which may be conveniently re-sized without surgical intervention as the heart remodels to its normal size, and which is capable of independently applying selectively differing forces against the right and left ventricles of the diseased heart.
- The present invention addresses the problems outlined above by providing a unique device for treating heart disorders, and particularly cardiomyopathy, comprised of a compliant containment structure shaped in a configuration such that it surrounds and encases the heart. Within this containment structure are housed two or more inflation pockets that are fabricated from a non-elastic compliant material. These pockets are disposed on the interior surface of the containment structure and are configured to oppose and support the external wall of at least one of the ventricles of the heart. In the preferred embodiment, there are a plurality of relatively small, spaced inflation pockets disposed to act against each ventricle which is to be contained.
- On the external surface of the containment structure, or spaced therefrom, there is disposed a recoil balloon, which is configured from an elastomeric material. The containment structure physically separates the inflation pockets from their associated recoil balloon(s). However, a fluid flow path is provided between the pockets and their associated balloon(s). Each recoil balloon has an inflation delivery tube which is in turn fluidly connected to a fluid access port which delivers fluid to the device as needed.
- The invention, together with additional features and advantages thereof, may best be understood by reference to the following description taken in conjunction with the accompanying illustrative drawing.
- FIG. 1 is a schematic, perspective view of a first embodiment of the present invention;
- FIG. 2 is a schematic exploded view of the embodiment illustrated in FIG. 1;
- FIG. 2a is a schematic exploded view similar to that of FIG. 2, illustrating a somewhat modified version of the embodiment illustrated in FIG. 1;
- FIG. 3 is a schematic perspective view of a second embodiment of the present invention;
- FIG. 4 is a schematic exploded view of the embodiment illustrated in FIG. 3;
- FIG. 5 is a cross-sectional view of a portion of the device illustrated in FIGS. 1 and 2, wherein the inflation pocket which forms a part of the invention is in an inflated state;
- FIG. 6 is a cross-sectional view similar to FIG. 5, illustrating a portion of the device shown in FIGS. 1 and 2, during the fluid exchange phase;
- FIG. 7 is a cross-sectional view similar to FIG. 6, illustrating a portion of the device shown in FIGS. 3 and 4, wherein the inflation pocket and secondary recoil balloon are in a filled state;
- FIG. 8 is a cross-sectional view similar to FIG. 7, illustrating a portion of the device shown in FIGS. 3 and 4, during the fluid exchange phase;
- FIG. 9 is a perspective view of the containment structure which forms a part of the inventive device;
- FIGS. 10A and 10B are plan views, in isolation, of the inflation pockets which form a part of the inventive device;
- FIG. 11 is a plan view, in isolation, of the recoil plate which forms a part of the second configuration of the inventive device illustrated in FIGS. 3 and 4;
- FIG. 12 is a schematic view illustrating the placement of the fluid access port which forms a part of the present invention;
- FIG. 13 is a schematic view illustrating yet a third embodiment of the inventive device;
- FIG. 14 is a perspective view illustrating a fourth preferred embodiment of the invention;
- FIG. 14a is a perspective view illustrating a modified version of the fourth embodiment shown in FIG. 14;
- FIG. 14b is a cross-sectional view of a portion of the embodiment illustrated in FIG. 14a;
- FIG. 15 is a front elevational view showing the embodiment of FIG. 14 after it has been placed about a heart, with a bypass graft in place;
- FIG. 16 is a cross-sectional view of the embodiment illustrated in FIG. 14, showing in detail the inflation pockets of the invention;
- FIG. 17 is a conceptual graphical plot of the cyclical pressure measured by an external pressure monitor for the device illustrated in FIG. 14 when it is installed on a heart and working full time (i.e. in contact with the heart full time);
- FIG. 18 is a conceptual graphical plot similar to that of FIG. 17 of the cyclical pressure measured by an external pressure monitor for the device illustrated in FIG. 14 when it is installed on a heart but not in contact with the external surface of the heart full time (i.e. it needs to be re-sized by addition of fluid); and
- FIG. 19 is a schematic view illustrating a system for monitoring pressure and/or providing counter-pulsating assist for any one of the embodiments illustrated in FIGS.1-18.
- Referring now more particularly to the drawings, there is shown in FIGS. 1, 2,5, and 6 a first embodiment of a
cardiac reinforcement device 10 of the present invention which comprises a frame orcontainment structure 12 preferably formed of a high strength biocompatible mesh-like material, such as polyester fully or partially encased or embedded within a flexible biocompatible material such as silicon or polyurethane, preferably using an injection process. The high strength mesh serves three primary purposes. First, it provides a strong, flexible non-elastic support for the containment structure. Second, it serves as a tear-resistant material which can be sutured to the heart muscle easily. Third, it is lightweight, and provide bypass graft access, as will be described more fully hereinbelow. The advantage of silicon, in particular, is that it has a long history of biocompatibility and provides a good surface to which other items may be attached. Of course, other suitable biocompatible materials, such as polyurethane, may be selected as well, as long as the resultant structure is compliant, but not elastic. It is also within the scope of the invention to employ an alternative configuration involving a polymer frame construction as opposed to the described mesh construction. - The encasing elastomer for the frame or
containment structure 12 may be transparent so that a practitioner can see and avoid suturing thedevice 10 too close to blood vessels. In this first embodiment, thecontainment structure 12 includes one ormore slits 14 along which a series ofholes 16 may be provided. Using abiocompatible lace 18, such as polyester, the slits may be laced up as illustrated in FIG. 1, for example, to optimize the size of theframe 12 for variously sized hearts. - It should be noted that, for example, as an alternative to lacing up the
slits 14, VELCRO hook and loop fastening straps 18 a, 18 b may be provided along each side of the slit. This alternative is illustrated in FIG. 2a. During the placement of the device, the VELCRO straps 18 a are overlapped to provide an accurate fit, then sutures 19 are made through the VELCRO overlap to secure the sizing permanently. - Port holes20 are preferably provided in the
frame 12 to provide a fluid flow path and permit the exchange of fluid from a plurality of inflation pockets 22 (FIG. 1) to arecoil balloon 24. The inflation pockets 22 (in this embodiment two are provided) are preferably formed of a composite structure made from a high strength biocompatible mesh-like material such as polyester fully encased within a flexible biocompatible material such as silicon or polyurethane (this may be the same material from which the frame orcontainment structure 12 is fabricated). These components essentially comprise balloons which are flexible and compliant with very low elasticity. Their purpose is to support the outer wall of the heart ventricle. Very low elasticity is desirable because in use there is a requirement that fluid contained within the inflation pockets 22 be expelled through theframe 12 when thepockets 22 are compressed. Consequently, a volume change due to volumetric expansion would be undesirable, as it would compromise the fit of the device on the heart. Preferably, the two providedinflation pockets 22 are of different configurations, and are asymmetrically located, due to the fact that the respective ventricles which they support are different in both configuration and location, with the left ventricle being much larger than the right ventricle. It should be noted that it is within the scope of the invention to provide more than twoinflation pockets 22 if desired, since configurations wherein more than onepocket 22 supports a single ventricle may be potentially beneficial in certain instances. Such an embodiment, presently preferred, is illustrated in FIGS. 14-16. - The
recoil balloon 24 is preferably fabricated of a thin high elasticity biocompatible material such as silicon or polyurethane. This component comprises a balloon which may be joined to the exterior surface of the frame orcontainment structure 12 over the port holes 20, as shown particularly in FIG. 2. - In the preferred embodiments, a
fluid access port 26 is implanted under the patient's skin 27 (FIG. 12) for providing access through which fluid can be delivered to two different device locations. It is preferably constructed of a variety of biocompatible materials, including titanium, polysulfone, polyurethane, and silicon. Similar ports are known in the prior art for use as vascular access ports which are implanted in patients for long-term infusion of medications. Theport 26 comprises a plurality ofelastomeric septums 28 which can be punctured and accessed frequently with a hypodermic needle (not shown). The septum material properties are such that they self-seal upon removal of the needle. - A
fluid line 30 conveys fluid, comprising saline or other suitable fluid, which may include both liquids and gases, from thefluid access port 26 to the recoil balloons 2 on either side of the frame 12 (only oneballoon 24 is shown in FIGS. 1 and 2, but in the first embodiment there is preferably one recoil balloon associated with each inflation pocket 22). The fluid line traverses the patient'smuscle 32, adjacent to the bone 34 (FIG. 12), and preferably comprises dual lumen tubing made from a biocompatible material such as silicon or polyurethane. Abifurcation 36 occurs at the distal end of thefluid line 30, and twoseparate tubes elastomeric septa 28 illustrated for this embodiment, so that the result is an ability to separately control the fluid conveyed to eachrecoil balloon 24. - A second embodiment is illustrated in FIGS. 3, 4,7, and 8 (FIGS. 9-12 are common to both embodiments), wherein like elements to those in the first embodiment are denoted by like reference numerals, increased by 100. The primary difference between this embodiment and the embodiment of FIG. 1 is the provision of a second recoil balloon 160 (FIG. 4) which “piggy-backs” directly over the
first recoil balloon 124. A second set of recoil balloons 160 is preferably provided on the opposing side of theframe 112 for operation with the second inflation pocket 122 (not shown). Apressure isolator plate 162, having a plurality of port holes 164, is disposed between theframe 112 and theinner recoil balloon 124. The pressure isolator plate, orrecoil plate 162, is preferably made of a rigid plastic material. Additionally, a secondfluid access port 126′ is provided, having twosepta 128′ and afluid line 130′. Thefluid access port 126 is arranged to supply fluid to the tworecoil balloons frame 112, splitting at the bifurcation 136 (FIG. 3) so that thetube 138 from one lumen supplies therecoil balloon 124, and thetube 140 from the other lumen supplies therecoil balloon 160. Similarly, thefluid access port 126′ independently supplies the two recoil balloons (not shown) disposed on the other side of theframe 112. Thus, the practitioner may independently and selectively supply differing quantities of fluid to each of the two recoil balloons disposed in a set on each side of theframe 112, and also independently supply fluid to each set of recoil balloons. In other words, all of the recoil balloons, whether in the same set or in different sets, are isolated from one another, and may be independently pressurized. - The
second recoil balloon 160 may be comprised of the same material as the first recoil balloon, or it may alternatively have different material properties. A second fluid chamber 166 (FIG. 6) is provided between the first and second recoil balloons. - The pressure isolator plate, or
recoil plate 162 is utilized only in the second embodiment because when thesecondary recoil balloon 160 is partially inflated, it puts a compressive load on theinner recoil balloon 124, which in turn compresses the frame wall causing increased pressure on theinflation pocket 122. The purpose of theplate 162 is to isolate those forces. - In yet a third embodiment of the invention, the system may be constructed as shown in either the first or second embodiments. The only change is that, as illustrated in FIG. 13, in this embodiment the
fluid access port fluid reservoir system 280 having a one-way valve 281, such as a duckbill valve, for example. With this configuration, rather than manually adding fluid, fluid from thereservoir 280 may be automatically added to each of the inflation pockets 22, 122 if and when the pressure in the inflation pockets drops below a predetermined value. Preferably, in this embodiment, thefluid reservoir system 280 comprises a biasing device, such as aconstant force spring 283, afluid reservoir 284, and aseal 284 a disposed between thefluid reservoir 284 and thespring 283. In operation, thespring 283 moves back as fluid enters from thefluid access port - There is shown in FIGS.14-16 a fourth presently preferred embodiment of the invention, wherein like elements to those of the first embodiment are designated by like reference numerals, increased by 300. Elements which are the same as in prior embodiments, having similar structure and function, may not be again described. Thus, a
cardiac reinforcement device 310 constructed in accordance with this embodiment comprises acontainment structure 312 which is preferably fabricated entirely of a high strength biocompatible mesh-like material, such as polyester. This construction, as compared to the mesh and frame construction disclosed in connection with the prior embodiments, provides a benefit of a lighter weight structure with less bulk, and therefore greater compliance, which minimizes the impairment of cardiac function. It also improves visibility, and provides ready access for a bypass graft, as will be discussed infra. As in the prior embodiments, there are provided a plurality of port holes 320 in thestructure 312, but they are preferably greater in number and distributed about the entire circumference of thestructure 312, as illustrated. - It should be noted that the mesh construction for this preferred embodiment may be constructed with a square pattern, if desired, and could resemble a hair net in appearance.
- Unlike the prior disclosed embodiments, this embodiment is particularly suited to the accommodation of one or more existing bypass grafts384 (FIG. 15) which may be present on the patient's
heart 385. A device constructed as illustrated in the first three embodiments may not be as suited to this type of condition, because the inflation pocket may cover and compress the bypass vessel, causing a restriction in the blood flow. In addition, in severe cases of cardiomyopathy (large dilation of the heart), there may not be sufficient space for the recoil balloons to expand without being compressed against the surrounding anatomy if they are attached to the side of the inventive device, as shown in the embodiments of FIGS. 1, 2, and 3. This compression would, of course, affect the pressures at which the device operates. - In contrast, the present embodiment comprises a plurality of multiple
small inflation pockets 322, rather than the fewer, larger inflation pockets disclosed in the previous embodiments. Themultiple inflation pockets 322 simulate the appearance of bubble wrap, but are spaced apart enough to provide a sufficient clearance between them to accommodate an existingbypass graft 384, or to allow asubsequent bypass graft 384 to be attached. Because the inflation pockets 322 are spaced, and small, no onepocket 322 should cover and compress the bypass vessel sufficiently to cause undesirable blood flow restriction. If, however, that is the case, because of the number ofinflation pockets 322, one or more of them can be removed during the installation procedure to accommodate the existingbypass graft 384. - Furthermore, this preferred embodiment overcomes the problems discussed supra, related to the unavailability of sufficient space for the recoil balloons of the prior embodiments in the event of a severely enlarged heart, by reducing the side profile and relocating the recoil balloons away to a location where space is not at a premium. The device otherwise functions in substantially the same manner as in the previous embodiments.
- Preferably, when it is necessary to perform a bypass procedure subsequent to installation of the
device 310, the bypass graft is routed around the exterior surface of thestructure 312. The large number of access holes 320 provided in the mesh material increase the likelihood that the graft can be attached without removing thedevice 310. However, in the event that additional access is required, the material comprising thestructure 312 is capable of being cut to provide additional access holes without compromising the mechanical integrity of the device. In some instances, it may even be preferably to provide fewer and/or smaller access holes 320, and to just be prepared to cut additional holes during a later bypass procedure, for the purpose of access. In the prior embodiments illustrated in FIGS. 1-13, if the device were already implanted and a bypass procedure became necessary, it is highly likely that the device would need to be removed in order to gain access to the artery and make the attachment of the vessel, as the site would likely be substantially covered by one of the inflation pockets. This is a difficult prospect, because of the tendency of the frame orcontainment structure more inflation pockets 322 are in the way, they can be removed to accommodate the procedure without materially affecting the overall operating effectiveness of the device. - Preferably, the
multiple inflation pockets 322 associated with each ventricle are linked together, in that they are all attached to one of theseptums 328 of thefluid access port 326, as illustrated in FIG. 14. Thefluid line 330 attached to each of theseptums 328, which is preferably of a dual lumen construction, as discussed supra in connection with the prior embodiments, includes at its distal end a plurality of smallerfluid delivery tubes 386, which are each individually fluidly connected to aseparate inflation pocket 322 disposed over an associated ventricle. With this advantageous arrangement, the inventive system may be adapted to fill the inflation pockets 322 for a particular ventricle in parallel, or in series, as desired, so that thepockets 322 may be, for example, filled in series from the base to the top of thestructure 312 as the associated ventricle expands in a similar manner, or, alternatively, may be filled simultaneously. - In one version of this preferred embodiment, illustrated in FIGS. 14, 15, and16, the recoil balloons 324 are disposed in each fluid line, remote from the
structure 312, rather than being attached to the exterior surface of theframe 312, as in prior embodiments. As in the prior embodiments, theballoons 324 are preferably fabricated of a thin high elasticity biocompatible material such as silicon or polyurethane. This arrangement offers the benefit of reducing the space that the device occupies immediately around the heart, and instead permits the disposition of theballoons 324 elsewhere in the chest cavity where space may not be as restricted. One other advantage of this construction is that the balloons may be changed out by utilization of only a minor surgical procedure, involving only the removal of easily detachable fittings 387 (FIG. 14), such as Luer Locks, in the event that balloons with different pressure capacity or recoil properties would be of benefit. - Another version of this preferred embodiment is illustrated particularly in FIGS. 14a and 14 b. This embodiment is very similar to that of FIG. 14, except that a double recoil balloon, comprised of a pair of inner and outer recoil balloons 324, 360 is utilized, rather than a
single recoil balloon 324. This is similar in concept to the embodiment illustrated in FIG. 4, with back-to-back recoil balloons 124, 160. As shown, thedetachable fitting 387 comprises amale Luer Lock 387 a and afemale Luer Lock 387 b.Lumen 330 a provides a fluid line for filling theinner balloon 324, while lumen 330 b provides a fluid line for filling theexterior balloon 360. A fluid line block 330 c forces fluid to enter theouter balloon 360 through anentry port 330 d. Passage 387 c in thefemale Luer Lock 387 b provides an exit port for fluid exiting theinterior recoil balloon 324 for the inflation pockets. In operation, when fluid is injected into thecavity 360 a between the exterior balloon and the interior balloon, theexterior balloon 360 becomes distended and causes an increase in the filling pressure for theinterior balloon 324. This configuration thus, as is apparent, provides a convenient method for increasing operating pressures, if desired, and thereby perhaps avoiding undue intervention. - Another advantageous feature of the present embodiment is its capability to directly deliver Trans echocardial drugs to the pericardium. In a preferred configuration, a third
elastomeric septum 388 is provided in the fluid access port 326 (FIG. 14), which is attached to adrug delivery line 389. Adistal portion 390 of thedrug delivery line 389 is arranged to wrap around the exterior surface of thestructure 312, as illustrated in FIG. 14, and is provided with a plurality of drug flow holes 391 spaced therealong where thedistal portion 390 is in proximity to the pericardium, to ensure the uniform delivery of the drug at its intended site. The drug flow holes 391 may also be used to remove fluid from the pericardium area if this become necessary. - In operation, the
device containment structure laces frame line 27 to page 7, line 4, the device can be accurately sized to the heart (theframe 312 is sufficiently elastic, being comprised entirely of flexible mesh material, that no slits are required). This is achieved in a similar manner as one would tighten a shoelace. The frame is then securely sutured to heart muscle to ensure that it cannot migrate from its intended location and also to isolate the forces on the right and left sides of the device during use. Thefluid access ports skin 27, as illustrated in FIG. 12. Alternatively, with respect to the third embodiment shown in FIG. 13, thepressurized fluid reservoir 280 and one-way valve 282 are appropriately positioned within the patient's thoracic cavity (not shown). - When the
device skin 27 and into theseptum fluid access port inflation delivery line - In the third embodiment, shown in FIG. 13, pressurized fluid will initially be introduced into the system from the pressurized
fluid reservoir 280, through the one-way valve 282, rather than manually via a syringe. In all other respects, operation of the third embodiment is substantially similar to that described above with respect to the first, second, and fourth embodiments, and, in fact, any of the first, second, and fourth embodiments can utilize an automated fluid pressurization system as shown in the third embodiment. - Once the
device frame recoil balloon frame containment structure 312, in the fluid lines 330. In this embodiment, as the fluid pressure increases, the fluid is displaced from the inflation pockets and is permitted to escape in a backwards direction through thefluid tubes 386 into thefluid line 330, which leads to therecoil balloon 324. As the volume of the inflation pockets decreases, the volume of the recoil balloon increases by an equal amount. - In any event, in all of the embodiments, in order for the fluid to enter the recoil balloons, the volume of the recoil balloons must increase. Thus, the wall of the
balloons - Over the course of time, as the patient responds to the action of the inventive device and the heart shrinks in size, the inflation pockets22, 122, 322 will no longer be assisting the ventricle through the full operating cycle. This condition can be easily corrected by repeating the set-up procedure and observing the pressure wave. If a reduction of the size of the heart has occurred, the pressure wave will not be constant and, by simply adding additional fluid to the inflation pockets 22, 122, 322 via the
fluid access ports - Again, it should be noted, as discussed supra, that the third embodiment illustrated in FIG. 13 offers a means for accomplishing the foregoing re-sizing process automatically. By using this embodiment, the practitioner can leave the patient for longer durations without making pressure volume adjustments to the inflation pockets22, 122, 322. In this configuration, fluid is automatically added to the inflation pockets whenever a predetermined pressure low occurs, and is therefore self-adjusting until the reservoir is emptied.
- The second disclosed embodiment offers a particular benefit in that if the practitioner determines that a patient would benefit from the application of a higher restraining force, such can be done by introducing additional fluid into the second fluid cavity166 between the first and second recoil balloons, via the additional available fluid access port. Fluid forced into this space 166 will stretch the surface of the
balloon 160, as illustrated in FIG. 7, thereby creating a greater resistance to the filling of theinner recoil balloon 124, which in turn increases the restraining force placed upon the heart. This adjustment may be made to any or all recoil balloons, as desired. - A major advantage of this design is that if a patient has an adverse reaction to the restraining forces of the
frame fluid access ports - It should be noted, as another advantageous feature of the invention, that the inflation pockets disclosed in any of the foregoing embodiments may be coated, if desired, with a drug infused osmosis material. If this is the case, the drug may leach out slowly for a term immediately after placement of the inventive device over a patient's heart, thereby aiding recovery.
- Referring now, in particular, to FIGS.17-19, there is illustrated a minimally invasive arrangement for monitoring and accurately measuring diastolic and systolic pressures and performance in an entirely new way. This data can be used for diagnostic purposes, to optimize the adjustment of the device, and/or to monitor therapy. In order to achieve this, the
fluid access port device flow line 492, to an external pressure monitoring system 493 (FIG. 19). This system may comprise a monitor, or a pulsating pump. To create a closed loop, aneedle 494 is placed into theelastomeric septum flow line 492 using, for example, aLuer lock connector 494 a. Under normal operating conditions, diastolic expansion will cause the pressure inside the device to increase, and systolic contraction will cause the pressure to decrease. This pressure change occurs along the entire fluid path between the device and the pressure monitoring system, so that themonitoring system 493 receives data that translates into a complete pressure wave, as illustrated in FIGS. 17 and 18, which each represent generalized plots of pressure change over time. In FIG. 17, which represents a situation where the device is working full time, the data plots a fullpressure SIN wave 495, with a peakdiastolic pressure 496 and a minimumsystolic pressure 497. On the other hand, as illustrated in FIG. 18, if the device is only in contact with a ventricle for a portion of the cardiac cycle, the pressure only changes while a compressive force between the device and the ventricle is in effect. This results in apartial pressure wave 498, with aflat spot 499 which represents the period of time x during which the device is not in contact with the ventricle, and thus is doing no work. In such an instance, the practitioner, viewing the plot on themonitoring device 493, would recognize the need to add fluid to resize the device to optimize its fit, as described supra, in order to ensure that it is working full time. - Although the inventive device has been disclosed as primarily having utility as a passive heart restraining or constraining device, it is within the scope of this invention to also provide direct active assistance to the heart if cardiac dysfunction occurs. This may happen immediately after installation of the device or at any time thereafter. In this mode of use, the device is used to provide systolic assistance instead of diastolic restraint. In order to achieve this, the fluid access ports of the device are directly attached to an external
pump monitoring system 493, as illustrated in FIG. 19, for the purpose of controlling systolic inflation of the inflation pockets 322 by means of counter pressure pulsation. To create a closed loop control between the device and the pump/monitoring system 493, aneedle 494 is placed into and attached to each fluid access port, which in turn is attached to anindependent flow line 492 which is connected to the pump/monitoring system. Due to the rapid pulse rate required to achieve success with this procedure, it is preferred to use a low inertia medium, such as helium, as the fluid for activating thedevice 310. - While this invention has been described with respect to various specific examples and embodiments, it is to be understood that the invention is not limited thereto and that it can be variously practiced within the scope of the following claims. For example, while the foregoing embodiments are disclosed as being adapted for restraining both ventricles of the heart, it is clearly within the scope of this invention to install the
device
Claims (36)
1. A device for treating a heart disorder, comprising:
a first structure for placement over a patient's heart;
a second structure for applying pressure against a first portion of said heart during a portion of the pumping cycle of said heart; and
a third structure for applying pressure against a second portion of said heart during a portion of the pumping cycle of said heart;
wherein the pressure applied by said second and third structures may be independently controllable so that the different pressures may be selectively applied against said first and second heart portions.
2. The device as recited in claim 1 , wherein said first structure comprises a containment structure for enclosing a substantial portion of said heart.
3. The device as recited in claim 1 , wherein said second structure comprises a first inflation pocket.
4. The device as recited in claim 3 , wherein said third structure comprises a second inflation pocket disposed in a spaced relationship from said first inflation pocket.
5. The device as recited in claim 3 , and further comprising a recoil balloon disposed outwardly of said inflation pocket and a fluid passage disposed between said inflation pocket and said recoil balloon to permit fluid to be exchanged therebetween.
6. The device as recited in claim 5 , wherein said inflation pocket is filled with fluid, and said first portion of said heart is the left ventricle, wherein when the heart enters a diastolic state, the left ventricle expands against said inflation pocket, thereby forcing fluid from said inflation pocket through said fluid passage and into said recoil balloon.
7. The device as recited in claim 6 , wherein when said heart enters a systolic state, said fluid returns through said fluid passage from the recoil balloon into the inflation pocket, so that the inflation pocket becomes pressurized and exerts pressure against said left ventricle.
8. The device as recited in claim 4 , and further comprising a fluid injection port for injecting fluid into each of said first and second inflation pockets, wherein differing amounts of fluid may be injected into each of the inflation pockets independently, thereby permitting different pressures to be selectively applied against said first and second heart portions.
9. The device as recited in claim 8 , wherein said fluid injection port comprises two septums disposed just beneath the skin of said patient, each of which is fluidly connected through a separate fluid passage to a corresponding one of said inflation pockets.
10. The device as recited in claim 8 , wherein said fluid injection port comprises a pressurized fluid reservoir and a one-way valve, so that fluid may be automatically injected into each of the first and second inflation pockets independently, responsive to pressure in each pocket.
11. The device as recited in claim 2 , wherein the containment structure is comprised substantially entirely of a flexible, biocompatible open mesh material, having a plurality of access openings disposed therein which are distributed about an outer surface of said containment structure.
12. The device as recited in claim 3 , wherein said first inflation pocket comprises a plurality of relatively small, spaced inflation pockets.
13. A device for treating a heart disorder, comprising:
a first structure for placement over a patient's heart;
a second structure disposed within said first structure for supporting a portion of said heart during at least a period of time when the heart is in a diastolic state;
a third structure disposed outside of said first structure which is adapted to operate in conjunction with the second structure to support the heart.
14. The device as recited in claim 13 , wherein said first structure comprises a containment structure for enclosing a substantial portion of said heart.
15. The device as recited in claim 13 , wherein said second structure comprises an inflation pocket comprised of a substantially non-elastic biocompatible material.
16. The device as recited in claim 14 , wherein said third structure comprises a recoil balloon.
17. The device as recited in claim 16 , and further comprising a fluid passage disposed between said inflation pocket and said recoil balloon to permit fluid to be exchanged therebetween.
18. The device as recited in claim 17 , and further comprising a fluid injection port for injecting fluid into said inflation pocket, wherein the amount of fluid being injected into said inflation pocket may be increased responsive to the size of the heart, in order to ensure that pressure is applied by said inflation pocket against said heart at least when said heart is in a diastolic state.
19. The device as recited in claim 14 , wherein said third structure is spaced from said first structure.
20. The device as recited in claim 14 , and further comprising a drug delivery line for selectively delivering drugs to said heart through said first structure.
21. A device for treating a heart disorder, comprising:
a containment structure adapted for placement over a patient's heart;
a first inflation pocket for applying pressure against the left heart ventricle during at least a period of time when the heart is in a diastolic state;
a second inflation pocket for applying pressure against the right heart ventricle during at least a period of time when the heart is in a diastolic state; and
a fluid injection port comprising a fluid line for independently delivering pressurized fluid to each of said first and second inflation pockets, so that different pressures may be selectively applied against each of said left and right heart ventricles.
22. A device for treating a heart disorder, comprising:
a containment structure adapted for placement over a patient's heart;
an inflation pocket disposed within said containment structure for supporting a portion of the heart during at least a period of time when the heart is in a diastolic state; and
a recoil balloon disposed outwardly of said containment structure which is adapted to operate in conjunction with said inflation pocket to support the heart.
23. A method for treating a heart disorder, comprising the steps of:
applying a first level of pressure against a first portion of a patient's heart; and
applying a second level of pressure against a second portion of said heart.
24. The method as recited in claim 23 , and further comprising the step of placing a containment structure over said heart.
25. The method as recited in claim 23 , wherein the step of applying a first level of pressure is accomplished by inflating a first inflation pocket which is disposed to lie adjacent to said first heart portion within said containment structure to said first level of pressure.
26. The method as recited in claim 25 , wherein the step of applying a second level of pressure is accomplished by inflating a second inflation pocket which is disposed to lie adjacent to said second heart portion within said containment structure to said second level of pressure.
27. A method for treating a heart disorder, comprising the steps of:
applying a first level of pressure against a first portion of a patient's heart;
monitoring the size of said heart over time; and
increasing said first level of pressure to a second higher level of pressure when a reduction in size of said heart is detected.
28. A device for treating a heart disorder, comprising:
a containment structure for placement over a patient's heart; and
a plurality of inflation pockets for applying pressure against a portion of said heart during at least a portion of the pumping cycle of said heart.
29. The device as recited in claim 28 , wherein said containment structure has an outer surface and comprises an open mesh material having a plurality of openings distributed about said outer surface, said plurality of openings providing access for visualizing coronary arteries and performing bypass procedures on said heart without removing said device.
30. The device as recited in claim 28 , wherein said plurality of inflation pockets comprise a plurality of inflation pockets which are each substantially smaller than a ventricle of said heart, and which are spaced with respect to one another, said plurality of inflation pockets together having sufficient size and being capable of applying sufficient force to restrain a heart ventricle.
31. The device as recited in claim 30 , and further comprising a fluid injection port and a fluid passage connected between said fluid injection port and each of said plurality of inflation pockets, for injecting fluid into each of said plurality of inflation pockets.
32. The device as recited in claim 31 , and further comprising a recoil balloon which is fluidly connected to each of said plurality of inflation pockets, said recoil balloon receiving fluid from said inflation pockets during a portion of the heart pumping cycle and delivering fluid to said inflation pockets during another portion of the heart pumping cycle.
33. The device as recited in claim 32 , wherein said recoil balloon is disposed at a location remote from said containment structure.
34. The device as recited in claim 33 , wherein said recoil balloon is disposed in said fluid passage, said fluid passage comprising a fluid line, said recoil balloon being connected to said fluid line using detachable fittings so that it is readily replaceable.
35. A device for treating a heart disorder, comprising:
a containment structure for placement over a patient's heart;
a drug injection port;
a drug delivery line fluidly connected to said drug injection port, said drug delivery line including a distal portion which is disposed about a circumferential portion of said containment structure; and
a plurality of drug flow holes spaced along said drug delivery line distal portion, for selectively supplying drugs to said heart.
36. A dual function device for treating a heart disorder, comprising:
a containment structure for placement over a patient's heart;
at least one inflation pocket for applying pressure against a portion of said heart during at least a portion of the pumping cycle of said heart;
a fluid injection port; and
a fluid passage connected between said fluid injection port and said at least one inflation pocket;
said device being operable to inject fluid into said at least one inflation pocket during any portion of the pumping cycle of the heart, so that it may operate either passively to restrain the size of the heart during the diastolic portion of the pumping cycle, or actively to provide a rapid pressure pulse to assist the heart during the systolic portion of the pumping cycle.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US10/058,475 US20020065449A1 (en) | 1998-12-21 | 2002-01-28 | Cardiac reinforcement device |
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US11323298P | 1998-12-21 | 1998-12-21 | |
US09/346,643 US6432039B1 (en) | 1998-12-21 | 1999-07-01 | Methods and apparatus for reinforcement of the heart ventricles |
US10/058,475 US20020065449A1 (en) | 1998-12-21 | 2002-01-28 | Cardiac reinforcement device |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/346,643 Continuation US6432039B1 (en) | 1998-12-21 | 1999-07-01 | Methods and apparatus for reinforcement of the heart ventricles |
Publications (1)
Publication Number | Publication Date |
---|---|
US20020065449A1 true US20020065449A1 (en) | 2002-05-30 |
Family
ID=26810828
Family Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/346,643 Expired - Fee Related US6432039B1 (en) | 1998-12-21 | 1999-07-01 | Methods and apparatus for reinforcement of the heart ventricles |
US10/058,475 Abandoned US20020065449A1 (en) | 1998-12-21 | 2002-01-28 | Cardiac reinforcement device |
Family Applications Before (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/346,643 Expired - Fee Related US6432039B1 (en) | 1998-12-21 | 1999-07-01 | Methods and apparatus for reinforcement of the heart ventricles |
Country Status (6)
Country | Link |
---|---|
US (2) | US6432039B1 (en) |
EP (1) | EP1140248A2 (en) |
JP (1) | JP2002532189A (en) |
AU (1) | AU2193800A (en) |
CA (1) | CA2356649A1 (en) |
WO (1) | WO2000036995A2 (en) |
Cited By (36)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20030045771A1 (en) * | 1997-01-02 | 2003-03-06 | Schweich Cyril J. | Heart wall tension reduction devices and methods |
US20030050529A1 (en) * | 2000-03-21 | 2003-03-13 | Myocor, Inc. | Splint assembly for improving cardiac function in hearts, and method for implanting the splint assembly |
US6723038B1 (en) | 2000-10-06 | 2004-04-20 | Myocor, Inc. | Methods and devices for improving mitral valve function |
US6764510B2 (en) | 2002-01-09 | 2004-07-20 | Myocor, Inc. | Devices and methods for heart valve treatment |
WO2004112867A1 (en) * | 2003-06-18 | 2004-12-29 | The Texas A & M University System | Device for proactive modulation of cardiac strain patterns |
US20050065396A1 (en) * | 1998-09-21 | 2005-03-24 | Myocor, Inc. | External stress reduction device and method |
US20060149348A1 (en) * | 2003-11-27 | 2006-07-06 | Bernd Vogel | Compression sleeve |
US20060264983A1 (en) * | 2005-05-20 | 2006-11-23 | Henry Holsten | Gastric restrictor assembly and method of use |
US20060264981A1 (en) * | 2005-05-20 | 2006-11-23 | Viola Frank J | Gastric restrictor assembly and method of use |
US20060264982A1 (en) * | 2005-05-20 | 2006-11-23 | Viola Frank J | Gastric restrictor assembly and method of use |
US20070129598A1 (en) * | 2001-09-07 | 2007-06-07 | Raman Jaishanker | Method and apparatus for external stabilization of the heart |
US20070260108A1 (en) * | 2005-04-06 | 2007-11-08 | The Texas A&M University System | Device for proactive modulation of cardiac strain patterns |
US20080021260A1 (en) * | 2005-04-06 | 2008-01-24 | The Texas A&M University System | Device for the Modulation of Cardiac End Diastolic Volume |
US20080319470A1 (en) * | 2007-06-20 | 2008-12-25 | Viola Frank J | Gastric restrictor assembly and method of use |
US20080319256A1 (en) * | 1998-07-29 | 2008-12-25 | Myocor, Inc. | Transventricular implant tools and devices |
US7666224B2 (en) | 2002-11-12 | 2010-02-23 | Edwards Lifesciences Llc | Devices and methods for heart valve treatment |
US7695425B2 (en) | 1997-01-02 | 2010-04-13 | Edwards Lifesciences Llc | Heart wall tension reduction apparatus and method |
US20100105978A1 (en) * | 2007-03-05 | 2010-04-29 | Jms Co., Ltd. | Heart assist device |
US20110021864A1 (en) * | 2009-07-22 | 2011-01-27 | The Texas A&M University System | Biphasic and Dynamic Adjustable Support Devices and Methods with Assist and Recoil Capabilities for Treatment of Cardiac Pathologies |
US7883539B2 (en) | 1997-01-02 | 2011-02-08 | Edwards Lifesciences Llc | Heart wall tension reduction apparatus and method |
US8226711B2 (en) | 1997-12-17 | 2012-07-24 | Edwards Lifesciences, Llc | Valve to myocardium tension members device and method |
US8944987B2 (en) | 2009-09-30 | 2015-02-03 | Adjucor Ug | Cardiac assistance device and method for the control thereof |
US9220824B2 (en) | 2013-01-08 | 2015-12-29 | AdjuCor GmbH | Implanting cardiac devices |
US9510746B2 (en) | 2004-06-17 | 2016-12-06 | The Texas A&M University System | Deployment methods and mechanisms for minimally invasive implantation of heart contacting cardiac devices |
US9642957B2 (en) | 2009-07-22 | 2017-05-09 | The Texas A&M University System | Diastolic recoil method and device for treatment of cardiac pathologies |
US9833551B2 (en) | 2015-04-29 | 2017-12-05 | The Texas A&M University System | Fully implantable direct cardiac and aortic compression device |
US9833318B2 (en) | 2015-07-15 | 2017-12-05 | The Texas A&M University System | Self-expanding heart assist device |
US10130456B2 (en) | 2013-01-08 | 2018-11-20 | AdjuCor GmbH | Supporting a heart |
US10391216B2 (en) | 2013-01-08 | 2019-08-27 | AdjuCor GmbH | Supporting a heart |
US10507271B2 (en) | 2016-06-23 | 2019-12-17 | Corinnova Incorporated | Fully implantable direct myocardium assist device |
WO2020152273A1 (en) * | 2019-01-24 | 2020-07-30 | Artract Medical UG | Medical chamber system, introduction system and kit |
WO2020176670A1 (en) * | 2019-02-26 | 2020-09-03 | Percassist, Inc. | Apparatus, systems, and methods for percutaneous pneumatic cardiac assistance |
CN112996456A (en) * | 2018-11-06 | 2021-06-18 | 胶囊护理有限责任公司 | Capsule device for enclosing a body organ or mass and use thereof |
CN113230533A (en) * | 2021-06-07 | 2021-08-10 | 卫洪超 | Power pump type artificial intelligence heart |
US20210338998A1 (en) * | 2018-08-30 | 2021-11-04 | Cyberdyne Inc. | Cardiac output support apparatus |
US11511102B2 (en) | 2004-06-17 | 2022-11-29 | The Texas A&M University System | Cardiac compression device having passive and active chambers |
Families Citing this family (68)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6045497A (en) | 1997-01-02 | 2000-04-04 | Myocor, Inc. | Heart wall tension reduction apparatus and method |
AUPQ090499A0 (en) | 1999-06-10 | 1999-07-01 | Peters, William S | Heart assist device and system |
AUPQ100699A0 (en) * | 1999-06-17 | 1999-07-08 | Northern Sydney Area Health Service | An assist device for the failing heart |
US6702732B1 (en) * | 1999-12-22 | 2004-03-09 | Paracor Surgical, Inc. | Expandable cardiac harness for treating congestive heart failure |
CA2402504A1 (en) * | 2000-03-10 | 2001-09-20 | Paracor Surgical, Inc. | Expandable cardiac harness for treating congestive heart failure |
US6425856B1 (en) * | 2000-05-10 | 2002-07-30 | Acorn Cardiovascular, Inc. | Cardiac disease treatment and device |
US6730016B1 (en) * | 2000-06-12 | 2004-05-04 | Acorn Cardiovascular, Inc. | Cardiac disease treatment and device |
US6902522B1 (en) * | 2000-06-12 | 2005-06-07 | Acorn Cardiovascular, Inc. | Cardiac disease treatment and device |
US6951534B2 (en) | 2000-06-13 | 2005-10-04 | Acorn Cardiovascular, Inc. | Cardiac support device |
US6482146B1 (en) * | 2000-06-13 | 2002-11-19 | Acorn Cardiovascular, Inc. | Cardiac disease treatment and device |
US6572533B1 (en) * | 2000-08-17 | 2003-06-03 | Acorn Cardiovascular, Inc. | Cardiac disease treatment and device |
AUPR031200A0 (en) * | 2000-09-22 | 2000-10-12 | Sunshine Heart Company Pty Ltd | Heart assist devices, systems and methods II |
US6564094B2 (en) * | 2000-12-22 | 2003-05-13 | Acorn Cardiovascular, Inc. | Cardiac disease treatment and device |
AU2002241902A1 (en) * | 2001-01-18 | 2002-07-30 | The Brigham And Women's Hospital, Inc. | Prosthetic device for respiratory patients |
US7468029B1 (en) * | 2001-06-04 | 2008-12-23 | Robertson Jr Abel L | Progressive biventricular diastolic support device |
AUPR669001A0 (en) * | 2001-07-30 | 2001-08-23 | Sunshine Heart Company Pty Ltd | A fluid pressure generating means |
JP2005501652A (en) * | 2001-09-10 | 2005-01-20 | パラコー メディカル インコーポレイテッド | Heart failure treatment device |
US7022063B2 (en) | 2002-01-07 | 2006-04-04 | Paracor Medical, Inc. | Cardiac harness |
AU2003248750A1 (en) * | 2002-06-27 | 2004-01-19 | J. Luis Guerrero | Ventricular remodeling for artioventricular valve regurgitation |
AU2003265354A1 (en) * | 2002-08-01 | 2004-02-23 | The General Hospital Corporation | Cardiac devices and methods for minimally invasive repair of ischemic mitral regurgitation |
JP4929428B2 (en) * | 2002-08-13 | 2012-05-09 | ロバート・エー・レヴィン | Cardiac device and method for percutaneous repair of atrioventricular valve |
AU2002952691A0 (en) * | 2002-11-15 | 2002-11-28 | Sunshine Heart Company Pty Ltd | Heart assist device utilising aortic deformation |
US7736299B2 (en) | 2002-11-15 | 2010-06-15 | Paracor Medical, Inc. | Introducer for a cardiac harness delivery |
US20060167334A1 (en) * | 2003-06-26 | 2006-07-27 | Anstadt Mark P | Method and apparatus for direct mechanical ventricular actuation with favorable conditioning and minimal heart stress |
US7494459B2 (en) * | 2003-06-26 | 2009-02-24 | Biophan Technologies, Inc. | Sensor-equipped and algorithm-controlled direct mechanical ventricular assist device |
CA2530429A1 (en) | 2003-07-10 | 2005-01-27 | Paracor Medical, Inc. | Self-anchoring cardiac harness |
AU2003904283A0 (en) * | 2003-08-12 | 2003-08-28 | Northern Sydney Area Health Service | An implantable direct cardiac compression device and system |
WO2005041783A1 (en) * | 2003-10-30 | 2005-05-12 | Sunshine Heart Company Pty Ltd | A wrap |
US7887478B2 (en) * | 2003-10-31 | 2011-02-15 | Sunshine Heart Company Pty Ltd | Percutaneous gas-line |
JP5196786B2 (en) | 2003-10-31 | 2013-05-15 | サンシャイン・ハート・カンパニー・ピーティーワイ・リミテッド | Synchronous control system |
US7955248B2 (en) * | 2003-11-11 | 2011-06-07 | Sunshine Heart Company Pty Ltd | Actuator for a heart assist device |
US20050197527A1 (en) * | 2004-03-04 | 2005-09-08 | Bolling Steven F. | Adjustable heart constraining apparatus and method therefore |
JP4656909B2 (en) * | 2004-10-15 | 2011-03-23 | オリンパス株式会社 | Intra-subject introduction apparatus and method for manufacturing the same |
US20070073218A1 (en) * | 2005-09-26 | 2007-03-29 | Lilip Lau | Inflatable cardiac device for treating and preventing ventricular remodeling |
EP1957160A2 (en) * | 2005-11-28 | 2008-08-20 | Myotech LLC | Method and apparatus for minimally invasive direct mechanical ventricular actuation |
US20070185369A1 (en) * | 2006-02-03 | 2007-08-09 | Mahmood Mirhoseini | Cardiac assist device and method |
US20070208217A1 (en) | 2006-03-03 | 2007-09-06 | Acorn Cardiovascular, Inc. | Self-adjusting attachment structure for a cardiac support device |
US20070232849A1 (en) * | 2006-04-04 | 2007-10-04 | Michael Gertner | Pericardial inserts |
US9259318B2 (en) | 2006-04-19 | 2016-02-16 | Beth Israel Deaconess Medical Center | Pericardial reinforcement device |
US20070270654A1 (en) | 2006-05-19 | 2007-11-22 | Acorn Cardiovascular, Inc. | Pericardium management tool for intra-pericardial surgical procedures |
US7841977B2 (en) * | 2006-06-22 | 2010-11-30 | Matthias Vaska | Devices and methods for absorbing, transferring and delivering heart energy |
US20080097146A1 (en) | 2006-06-29 | 2008-04-24 | Acorn Cardiovascular, Inc. | Cardiac support device with low friction delivery structures |
JP2009542338A (en) * | 2006-06-30 | 2009-12-03 | シーヴィ デヴァイシズ,エルエルシー | Percutaneous endovascular access to heart tissue |
US7651462B2 (en) | 2006-07-17 | 2010-01-26 | Acorn Cardiovascular, Inc. | Cardiac support device delivery tool with release mechanism |
EP2054103B1 (en) | 2006-08-21 | 2019-05-29 | Sunshine Heart Company Pty Ltd | An improved wrap for a heart assist device |
JP5174891B2 (en) | 2007-04-27 | 2013-04-03 | シーヴィ デヴァイシズ,エルエルシー | Devices, systems, and methods for accessing the epicardial surface of the heart |
US8192351B2 (en) | 2007-08-13 | 2012-06-05 | Paracor Medical, Inc. | Medical device delivery system having integrated introducer |
US8092363B2 (en) | 2007-09-05 | 2012-01-10 | Mardil, Inc. | Heart band with fillable chambers to modify heart valve function |
EP2229213A4 (en) * | 2008-01-08 | 2012-10-17 | Univ Nat Cheng Kung | Cardiac compression system |
BRPI0920349B8 (en) * | 2008-10-10 | 2021-06-22 | Medicaltree Patent Ltd | device and system to assist the heart |
US8523756B2 (en) * | 2008-12-31 | 2013-09-03 | National Cheng Kung University | Cardiac compression system |
US20110196189A1 (en) * | 2010-02-09 | 2011-08-11 | Myocardiocare, Inc. | Extra-cardiac differential ventricular actuation by inertial and baric partitioning |
CN102939117B (en) | 2010-04-02 | 2015-12-02 | 阳光心脏有限公司 | Combination heart assist system, method and apparatus |
US8795149B2 (en) * | 2010-11-23 | 2014-08-05 | Theodore J. Lillehei | Pneumatic or hydraulic cardiac assist devices |
JP6084775B2 (en) * | 2012-03-09 | 2017-02-22 | 学校法人金沢医科大学 | Heart correction net |
WO2013177460A1 (en) * | 2012-05-23 | 2013-11-28 | Lillehei Theodore J | Pneumatic or hydraulic cardiac assist devices |
EP2906151B1 (en) | 2012-10-12 | 2023-06-21 | Mardil, Inc. | Cardiac treatment system |
USD717954S1 (en) | 2013-10-14 | 2014-11-18 | Mardil, Inc. | Heart treatment device |
DE102015212699A1 (en) * | 2015-07-07 | 2017-01-12 | AdjuCor GmbH | Implantable device for localized delivery and application of substances in the pericardium or on the heart surface |
US11375824B2 (en) * | 2018-03-22 | 2022-07-05 | Bussert Medical, Inc. | Therapeutic seat cushion equipped for pressure monitoring and inflation system for same |
US11376417B2 (en) | 2018-06-06 | 2022-07-05 | The Regents Of The University Of California | Whole heart assist device |
US11219754B2 (en) | 2020-05-20 | 2022-01-11 | Rainbow Medical Ltd. | Passive pump |
US11395910B2 (en) | 2020-05-20 | 2022-07-26 | Rainbow Medical Ltd. | Passive pump |
US11896812B1 (en) | 2023-01-27 | 2024-02-13 | Lifebridge Technologies Llc | Versatile modular heart pump for non-blood contacting ventricular function augmentation |
US11383076B2 (en) | 2020-10-01 | 2022-07-12 | Lifebridge Technologies, Llc | Pump regulation based on heart size and function |
WO2022125651A1 (en) * | 2020-12-09 | 2022-06-16 | Neocardial Technologies, Llc | Mechanical cardiac resynchronization therapy device |
US11484700B1 (en) | 2021-10-25 | 2022-11-01 | Yossi Gross | Mechanical treatment of heart failure |
US11357629B1 (en) | 2021-10-25 | 2022-06-14 | Rainbow Medical Ltd. | Diastolic heart failure treatment |
Family Cites Families (34)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2826193A (en) | 1956-08-01 | 1958-03-11 | Vineberg Heart Foundation | Cardiac resuscitation device |
FR92798E (en) | 1966-09-05 | 1968-12-27 | Rhone Poulenc Sa | New cardiac assistance prosthesis and its manufacture. |
FR1512372A (en) | 1966-12-19 | 1968-02-09 | Deformable membrane by internal action | |
US3587567A (en) | 1968-12-20 | 1971-06-28 | Peter Paul Schiff | Mechanical ventricular assistance assembly |
US3613672A (en) | 1969-07-09 | 1971-10-19 | Peter Schiff | Mechanical ventricular assistance cup |
GB2115287B (en) | 1981-06-29 | 1985-10-30 | Devendra Nath Sharma | Devices for replacing or assisting the heart |
SU1009457A1 (en) | 1981-07-15 | 1983-04-07 | Проблемная Лаборатория "Вспомогательного Кровообращения" Благовещенского Медицинского Института | Artificial pericardium |
IT1155105B (en) | 1982-03-03 | 1987-01-21 | Roberto Parravicini | PLANT DEVICE TO SUPPORT THE MYOCARDIUM ACTIVITY |
US4628937A (en) | 1984-08-02 | 1986-12-16 | Cordis Corporation | Mapping electrode assembly |
US4690134A (en) | 1985-07-01 | 1987-09-01 | Snyders Robert V | Ventricular assist device |
SE454942B (en) | 1986-05-22 | 1988-06-13 | Astra Tech Ab | HEART HELP DEVICE FOR INOPERATION IN BROSTHALAN |
SU1604377A1 (en) | 1987-02-23 | 1990-11-07 | Благовещенский государственный медицинский институт | Artificial pericardium |
US5098369A (en) | 1987-02-27 | 1992-03-24 | Vascor, Inc. | Biocompatible ventricular assist and arrhythmia control device including cardiac compression pad and compression assembly |
US4827932A (en) | 1987-02-27 | 1989-05-09 | Intermedics Inc. | Implantable defibrillation electrodes |
US4976730A (en) | 1988-10-11 | 1990-12-11 | Kwan Gett Clifford S | Artificial pericardium |
FR2639221A1 (en) | 1988-11-21 | 1990-05-25 | Perrotin Daniel | APPARATUS FOR DIRECTIONAL AND PERIODIC MASSAGE OF A PART OF THE HUMAN BODY |
JPH02271829A (en) | 1989-04-13 | 1990-11-06 | Tanaka Kikinzoku Kogyo Kk | Electrode for deciding myocardial infarction |
FR2645739A1 (en) | 1989-04-14 | 1990-10-19 | Vm Tech Sa | Cardiac assistance device and its use |
SU1734767A1 (en) | 1990-01-31 | 1992-05-23 | Томский Медицинский Институт | Heart action assistance device |
US5131905A (en) | 1990-07-16 | 1992-07-21 | Grooters Ronald K | External cardiac assist device |
US5119804A (en) | 1990-11-19 | 1992-06-09 | Anstadt George L | Heart massage apparatus |
US5169381A (en) | 1991-03-29 | 1992-12-08 | Snyders Robert V | Ventricular assist device |
US5112303A (en) | 1991-05-02 | 1992-05-12 | Pudenz-Schulte Medical Research Corporation | Tumor access device and method for delivering medication into a body cavity |
US5197982A (en) | 1991-10-15 | 1993-03-30 | Goldsmith Iii Manning M | Adjustable prosthetic device for vocal cord and method |
US5383840A (en) | 1992-07-28 | 1995-01-24 | Vascor, Inc. | Biocompatible ventricular assist and arrhythmia control device including cardiac compression band-stay-pad assembly |
US5256132A (en) * | 1992-08-17 | 1993-10-26 | Snyders Robert V | Cardiac assist envelope for endoscopic application |
US5336254A (en) | 1992-09-23 | 1994-08-09 | Medtronic, Inc. | Defibrillation lead employing electrodes fabricated from woven carbon fibers |
US5749839A (en) | 1994-08-18 | 1998-05-12 | Duke University | Direct mechanical bi-ventricular cardiac assist device |
US5534024A (en) | 1994-11-04 | 1996-07-09 | Aeroquip Corporation | Intraluminal stenting graft |
US5603337A (en) | 1994-12-05 | 1997-02-18 | Jarvik; Robert | Two-stage cardiomyoplasty |
US5800528A (en) * | 1995-06-13 | 1998-09-01 | Abiomed R & D, Inc. | Passive girdle for heart ventricle for therapeutic aid to patients having ventricular dilatation |
US5713954A (en) | 1995-06-13 | 1998-02-03 | Abiomed R&D, Inc. | Extra cardiac ventricular assist device |
US5702343A (en) * | 1996-10-02 | 1997-12-30 | Acorn Medical, Inc. | Cardiac reinforcement device |
AUPO723197A0 (en) | 1997-06-06 | 1997-07-03 | Seare, William J Jr | Cardiac assist device |
-
1999
- 1999-07-01 US US09/346,643 patent/US6432039B1/en not_active Expired - Fee Related
- 1999-12-17 WO PCT/US1999/030138 patent/WO2000036995A2/en not_active Application Discontinuation
- 1999-12-17 CA CA002356649A patent/CA2356649A1/en not_active Abandoned
- 1999-12-17 EP EP99966389A patent/EP1140248A2/en not_active Withdrawn
- 1999-12-17 AU AU21938/00A patent/AU2193800A/en not_active Abandoned
- 1999-12-17 JP JP2000589109A patent/JP2002532189A/en active Pending
-
2002
- 2002-01-28 US US10/058,475 patent/US20020065449A1/en not_active Abandoned
Cited By (71)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20030045771A1 (en) * | 1997-01-02 | 2003-03-06 | Schweich Cyril J. | Heart wall tension reduction devices and methods |
US8267852B2 (en) | 1997-01-02 | 2012-09-18 | Edwards Lifesciences, Llc | Heart wall tension reduction apparatus and method |
US7883539B2 (en) | 1997-01-02 | 2011-02-08 | Edwards Lifesciences Llc | Heart wall tension reduction apparatus and method |
US8460173B2 (en) | 1997-01-02 | 2013-06-11 | Edwards Lifesciences, Llc | Heart wall tension reduction apparatus and method |
US7695425B2 (en) | 1997-01-02 | 2010-04-13 | Edwards Lifesciences Llc | Heart wall tension reduction apparatus and method |
US8226711B2 (en) | 1997-12-17 | 2012-07-24 | Edwards Lifesciences, Llc | Valve to myocardium tension members device and method |
US7722523B2 (en) | 1998-07-29 | 2010-05-25 | Edwards Lifesciences Llc | Transventricular implant tools and devices |
US7981020B2 (en) | 1998-07-29 | 2011-07-19 | Edwards Lifesciences Llc | Transventricular implant tools and devices |
US20080319256A1 (en) * | 1998-07-29 | 2008-12-25 | Myocor, Inc. | Transventricular implant tools and devices |
US20050065396A1 (en) * | 1998-09-21 | 2005-03-24 | Myocor, Inc. | External stress reduction device and method |
US8579798B2 (en) | 1998-09-21 | 2013-11-12 | Edwards Lifesciences, Llc | External cardiac stress reduction method |
US20030050529A1 (en) * | 2000-03-21 | 2003-03-13 | Myocor, Inc. | Splint assembly for improving cardiac function in hearts, and method for implanting the splint assembly |
US7766812B2 (en) | 2000-10-06 | 2010-08-03 | Edwards Lifesciences Llc | Methods and devices for improving mitral valve function |
US9198757B2 (en) | 2000-10-06 | 2015-12-01 | Edwards Lifesciences, Llc | Methods and devices for improving mitral valve function |
US6723038B1 (en) | 2000-10-06 | 2004-04-20 | Myocor, Inc. | Methods and devices for improving mitral valve function |
US8715160B2 (en) | 2001-09-07 | 2014-05-06 | Mardil, Inc. | Method and apparatus for external stabilization of the heart |
US8092367B2 (en) | 2001-09-07 | 2012-01-10 | Mardil, Inc. | Method for external stabilization of the base of the heart |
US20080215074A1 (en) * | 2001-09-07 | 2008-09-04 | Raman Jaishankar | Method and apparatus for external stabilization of the heart |
US8128553B2 (en) | 2001-09-07 | 2012-03-06 | Mardil, Inc. | Method and apparatus for external stabilization of the heart |
US9289298B2 (en) | 2001-09-07 | 2016-03-22 | Mardil, Inc. | Method and apparatus for external stabilization of the heart |
US20070129598A1 (en) * | 2001-09-07 | 2007-06-07 | Raman Jaishanker | Method and apparatus for external stabilization of the heart |
US8506624B2 (en) | 2002-01-09 | 2013-08-13 | Edwards Lifesciences, Llc | Devices and methods for heart valve treatment |
US7678145B2 (en) | 2002-01-09 | 2010-03-16 | Edwards Lifesciences Llc | Devices and methods for heart valve treatment |
US8070805B2 (en) | 2002-01-09 | 2011-12-06 | Edwards Lifesciences Llc | Devices and methods for heart valve treatment |
US6764510B2 (en) | 2002-01-09 | 2004-07-20 | Myocor, Inc. | Devices and methods for heart valve treatment |
US7666224B2 (en) | 2002-11-12 | 2010-02-23 | Edwards Lifesciences Llc | Devices and methods for heart valve treatment |
US7445593B2 (en) | 2003-06-18 | 2008-11-04 | The Texas A&M University System | Device for proactive modulation of cardiac strain patterns |
US20050004420A1 (en) * | 2003-06-18 | 2005-01-06 | The Texas A&M University System | Device for proactive modulation of cardiac strain patterns |
WO2004112867A1 (en) * | 2003-06-18 | 2004-12-29 | The Texas A & M University System | Device for proactive modulation of cardiac strain patterns |
US20060149348A1 (en) * | 2003-11-27 | 2006-07-06 | Bernd Vogel | Compression sleeve |
US8388616B2 (en) * | 2003-11-27 | 2013-03-05 | Endosmart Gesellschaft Für Medizintechnik MbH | Compression sleeve |
US9510746B2 (en) | 2004-06-17 | 2016-12-06 | The Texas A&M University System | Deployment methods and mechanisms for minimally invasive implantation of heart contacting cardiac devices |
US11511102B2 (en) | 2004-06-17 | 2022-11-29 | The Texas A&M University System | Cardiac compression device having passive and active chambers |
US7935045B2 (en) | 2005-04-06 | 2011-05-03 | The Texas A&M University System | Device for proactive modulation of cardiac strain patterns |
US7871366B2 (en) * | 2005-04-06 | 2011-01-18 | The Texas A&M University System | Device for the modulation of cardiac end diastolic volume |
US20080021260A1 (en) * | 2005-04-06 | 2008-01-24 | The Texas A&M University System | Device for the Modulation of Cardiac End Diastolic Volume |
US20070260108A1 (en) * | 2005-04-06 | 2007-11-08 | The Texas A&M University System | Device for proactive modulation of cardiac strain patterns |
US7666180B2 (en) | 2005-05-20 | 2010-02-23 | Tyco Healthcare Group Lp | Gastric restrictor assembly and method of use |
US7691053B2 (en) | 2005-05-20 | 2010-04-06 | Tyco Healthcare Group Lp | Gastric restrictor assembly and method of use |
US20060264983A1 (en) * | 2005-05-20 | 2006-11-23 | Henry Holsten | Gastric restrictor assembly and method of use |
US20060264981A1 (en) * | 2005-05-20 | 2006-11-23 | Viola Frank J | Gastric restrictor assembly and method of use |
US20060264982A1 (en) * | 2005-05-20 | 2006-11-23 | Viola Frank J | Gastric restrictor assembly and method of use |
US8114010B2 (en) | 2005-05-20 | 2012-02-14 | Tyco Healthcare Group Lp | Gastric restrictor assembly and method of use |
US20100145472A1 (en) * | 2005-05-20 | 2010-06-10 | Tyco Healthcare Group Lp | Gastric Restrictor Assembly And Method Of Use |
US20100105978A1 (en) * | 2007-03-05 | 2010-04-29 | Jms Co., Ltd. | Heart assist device |
US8790290B2 (en) | 2007-06-20 | 2014-07-29 | Covidien Lp | Gastric restrictor assembly and method of use |
US20080319470A1 (en) * | 2007-06-20 | 2008-12-25 | Viola Frank J | Gastric restrictor assembly and method of use |
US8435203B2 (en) | 2007-06-20 | 2013-05-07 | Covidien Lp | Gastric restrictor assembly and method of use |
US20110021864A1 (en) * | 2009-07-22 | 2011-01-27 | The Texas A&M University System | Biphasic and Dynamic Adjustable Support Devices and Methods with Assist and Recoil Capabilities for Treatment of Cardiac Pathologies |
US8944986B2 (en) | 2009-07-22 | 2015-02-03 | The Texas A&M University System | Biphasic and dynamic adjustable support devices and methods with assist and recoil capabilities for treatment of cardiac pathologies |
WO2011011641A3 (en) * | 2009-07-22 | 2011-06-30 | The Texas A&M University System | Biphasic and dynamic adjustable support devices and methods with assist and recoil capabilities for treatment of cardiac pathologies |
US9259520B2 (en) | 2009-07-22 | 2016-02-16 | The Texas A&M University System | Biphasic and dynamic adjustable support devices and methods with assist and recoil capabilities for treatment of cardiac pathologies |
US20110060181A1 (en) * | 2009-07-22 | 2011-03-10 | The Texas A&M University System | Biphasic and Dynamic Adjustable Support Devices and Methods with Assist and Recoil Capabilities for Treatment of Cardiac Pathologies |
US9642957B2 (en) | 2009-07-22 | 2017-05-09 | The Texas A&M University System | Diastolic recoil method and device for treatment of cardiac pathologies |
US10398556B2 (en) | 2009-07-22 | 2019-09-03 | Corinnova Incorporated | Diastolic recoil method and device for treatment of cardiac pathologies |
US8944987B2 (en) | 2009-09-30 | 2015-02-03 | Adjucor Ug | Cardiac assistance device and method for the control thereof |
EP2482865B1 (en) * | 2009-09-30 | 2015-05-06 | AdjuCor GmbH | Cardiac assistance device |
US10123875B2 (en) | 2013-01-08 | 2018-11-13 | AdjuCor GmbH | Implanting cardiac devices |
US10130456B2 (en) | 2013-01-08 | 2018-11-20 | AdjuCor GmbH | Supporting a heart |
US10391216B2 (en) | 2013-01-08 | 2019-08-27 | AdjuCor GmbH | Supporting a heart |
US9220824B2 (en) | 2013-01-08 | 2015-12-29 | AdjuCor GmbH | Implanting cardiac devices |
US9833551B2 (en) | 2015-04-29 | 2017-12-05 | The Texas A&M University System | Fully implantable direct cardiac and aortic compression device |
US9833318B2 (en) | 2015-07-15 | 2017-12-05 | The Texas A&M University System | Self-expanding heart assist device |
US10507271B2 (en) | 2016-06-23 | 2019-12-17 | Corinnova Incorporated | Fully implantable direct myocardium assist device |
US20210338998A1 (en) * | 2018-08-30 | 2021-11-04 | Cyberdyne Inc. | Cardiac output support apparatus |
CN112996456A (en) * | 2018-11-06 | 2021-06-18 | 胶囊护理有限责任公司 | Capsule device for enclosing a body organ or mass and use thereof |
CN113348012A (en) * | 2019-01-24 | 2021-09-03 | 阿尔特医疗公司 | Medical chamber system, introduction system and kit |
WO2020152273A1 (en) * | 2019-01-24 | 2020-07-30 | Artract Medical UG | Medical chamber system, introduction system and kit |
WO2020176670A1 (en) * | 2019-02-26 | 2020-09-03 | Percassist, Inc. | Apparatus, systems, and methods for percutaneous pneumatic cardiac assistance |
US20210379357A1 (en) * | 2019-02-26 | 2021-12-09 | Percassist, Inc. | Apparatus, systems, and methods for percutaneous pneumatic cardiac assistance |
CN113230533A (en) * | 2021-06-07 | 2021-08-10 | 卫洪超 | Power pump type artificial intelligence heart |
Also Published As
Publication number | Publication date |
---|---|
WO2000036995A3 (en) | 2000-11-09 |
WO2000036995A2 (en) | 2000-06-29 |
JP2002532189A (en) | 2002-10-02 |
AU2193800A (en) | 2000-07-12 |
US6432039B1 (en) | 2002-08-13 |
EP1140248A2 (en) | 2001-10-10 |
CA2356649A1 (en) | 2000-06-29 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US6432039B1 (en) | Methods and apparatus for reinforcement of the heart ventricles | |
US6685627B2 (en) | Modification of properties and geometry of heart tissue to influence heart function | |
RU2703701C2 (en) | Heart supporting device | |
US6360749B1 (en) | Modification of properties and geometry of heart tissue to influence heart function | |
US7468029B1 (en) | Progressive biventricular diastolic support device | |
US5848962A (en) | Device for assisting cardiac function | |
US20070208210A1 (en) | Method and apparatus to unload a failing heart | |
US20070073218A1 (en) | Inflatable cardiac device for treating and preventing ventricular remodeling | |
US20040225177A1 (en) | Implantable cardiac assist device | |
CA2068996A1 (en) | Implantable coronary perfusion pump | |
JPH06510686A (en) | Cardiac support device that can be implanted subcutaneously | |
WO2009018358A2 (en) | Device for the modulation of cardiac end diastolic volume | |
US6149578A (en) | Piston-action intra-aortic coronary assist device | |
CA2566813C (en) | Device for epicardial support and/or the assuming of cardiac activity | |
US8715156B2 (en) | Modification of properties and geometry of heart tissue to influence function | |
US11511102B2 (en) | Cardiac compression device having passive and active chambers | |
US20120283507A1 (en) | Cardiac Assist Devices | |
Gealow et al. | Conformational adaptation of muscle: implications in cardiomyoplasty and skeletal muscle ventricles | |
EP4169483B1 (en) | Vascular graft | |
US11229785B2 (en) | Circulatory assistance device | |
WO2023093478A1 (en) | Ventricular assist device | |
US20220346956A1 (en) | Cardiac Compression Device Having Passive And Active Chambers | |
US20070129594A1 (en) | Implantable direct cardiac compression device and system | |
RU2007149449A (en) | METHOD OF RESTORING FUNCTIONS OF A PATIENT'S ORGANISM BY INFLUENCE ON HOLLOW BODIES AND A DEVICE FOR ITS IMPLEMENTATION |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION |