CIRCULATORY ASSISTANCE DEVICE

Abstract

Circulatory assistance device for a heart of a living being, including a cuff for periodically applying pressure to the heart by at least one dielectric elastomer membrane which is controllable by a control device in synchronization with a cardiac beat in order to convey blood in pulses, wherein the cuff is designed to be pulled over the outside of the heart and for this purpose has an inner shape that is adapted to the outer contour of the heart at least in the region outside the ventricles, wherein the cuff is composed of an outer contraction layer including the dielectric elastomer membrane and an inner padding layer, and the padding layer is filled with an incompressible liquid and has at least one outlet valve, which is closed in a normal state and opened in an emergency state.

Claims

1. A circulatory assistance device for a heart of a living being, the circulatory assistance device comprising a cuff to periodically apply pressure to the heart by at least one dielectric elastomer membrane, the at least one dielectric elastomer membrane controllable by a control device in synchronization with a heart beat in order to convey blood in pulses, wherein the cuff is designed to be pulled over an outside of the heart and for this purpose the cuff has an inner shape that is adapted to an outer contour of the heart at least in a region outside ventricles of the heart, wherein the cuff is composed of an outer contraction layer comprising the dielectric elastomer membrane and an inner padding layer, and the inner padding layer is filled with an incompressible liquid and has at least one outlet valve, the at least one outlet valve being closed in a normal state and open in an emergency state.

2. The circulatory assistance device according to claim 1, wherein the padding layer has a thickness that corresponds at least to one contraction stroke of the contraction layer.

3. The circulatory assistance device according to claim 1, wherein the contraction layer includes a number of annular sections which are separately electrically controllable in a time-staggered sequence.

4. The circulatory assistance device according to claim 3, wherein from 3 annular sections to 250 annular sections of the contraction layer are provided.

5. The circulatory assistance device according to claim 3, wherein the padding layer includes the same number of liquid-filled annular spaces, in each case located below the annular sections of the contraction layer, wherein each annular space has its own outlet valve.

6. The circulatory support device according to claim 1, wherein the padding layer communicates over the outlet valve with a collecting bag or an outlet line for passage out of the body of the living being.

7. The circulatory assistance device according to claim 1, wherein the incompressible liquid of the padding layer is physiologically tolerable and is releasable over the outlet valve into the body of the living being.

8. The circulatory assistance device according to claim 7, wherein the incompressible liquid of the padding layer comprises at least one substance with positive inotropic activity.

9. The circulatory assistance device according to claim 1, wherein the control device has an emergency state detection unit to detect an emergency state if a power supply for the contraction layer falls below a minimum value for a specified time period.

10. The circulatory assistance system comprising a circulatory assistance device according to claim 1, a control device, a power supply device, and at least one sensor device to detect a cardiac cycle of the heart.

11. A method of introducing a circulatory assistance system according to claim 1 into the body of the living being, wherein the method comprises: pulling the circulatory assistance device over the heart of the living being fixing in position the circulatory assistance device pulled over the heart; and attaching a sensor device to the heart, the sensor capable of detecting a cardiac cycle of the heart.

12. A method of assisting circulation of the blood in a living being using a circulatory assistance system according to claim 10, wherein the method comprises: detecting a cardiac cycle of the heart; and supplying power to the contraction layer synchronously with the cardiac cycle of the heart as detected.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

[0035] In the drawings:

[0036] FIG. 1 is a schematic representation of a heart with a circulatory assistance system in the normal operating state;

[0037] FIG. 2 is a schematic representation of a heart with the circulatory assistance system in an emergency state;

[0038] FIG. 3 is a schematic representation of a heart with a second design of a circulatory assistance system in the normal operating state;

[0039] FIG. 4 is a schematic representation of a heart with a third design of a circulatory assistance system; and

[0040] FIG. 5 is several views of the mode of action of the third embodiment.

DETAILED DESCRIPTION

[0041] In FIGS. 1 and 2 a heart of a living being with a circulatory assistance system according to the present invention is shown in two states, namely in the normal operating state in FIG. 1 and in an emergency state in FIG. 2. The heart 10 consists essentially of a right ventricle 12, a left ventricle 14, an intraventricular septum 16, and a ventricular wall 18. Additional vessels of the circulatory system 20 are not shown in further detail or provided with reference symbols.

[0042] A cuff 22 of a circulatory assistance device in a first embodiment fits closely around the heart 10 during the diastolic phase of the cardiac cycle. The cuff includes an outer contraction layer 24 and an inner padding layer 26. In the interior of the contraction layer 24 is at least one elastic elastomer membrane, which preferably has a closed annular shape, or as shown in FIGS. 1 and 2, a tulip shape. In the cuff 22 several dielectric elastomer membranes may be arranged adjacent to or one on top of the other. The elastomer membranes are preferably closed, but within the scope of the invention it is also possible to arrange several separately controlled annular elastomer membranes alongside one another.

[0043] Materials that may be considered for the contraction layer 24 include, for example, PDMS, polyurethane, and acrylates (e.g., VHB from 3M). Particularly suitable is a silicone with polydimethyl siloxane as the polymer component and acrylic polymers and natural rubber.

[0044] The padding layer 26 is functionally connected to an outlet valve 28 in such a way that in the opened state of the outlet valve 28, incompressible liquid located in the padding layer 26 can emerge into the environment or into reservoirs provided for this, not shown. In FIG. 1 the circulatory assistance device is in the normal operating state, so that the outlet valve 28 is closed.

[0045] The padding layer 26 preferably has a thickness of 0.5 cm to 2.5 cm and is preferably filled with an absorbable aqueous solution. According to a further development, this can also contain medication.

[0046] The circulatory support device 22 is connected to a control device 30, which includes a power supply unit, not shown. The control device 30 is also connected to a sensor 32, which detects the cardiac cycle of the heart 10 at a suitable location. The control device 30 is connected to the contraction layer 24 over a power supply line 34, wherein sensor signals from sensors, not shown, indicating the state of the contraction layer 24 can also travel over separate conductors of the power supply line 34. From the power supply line 34, a power supply line 36 branches off; this supplies the outlet valve 28 with power such that it assumes the closed state shown in FIG. 1 when power is supplied. If the power supply unit of the control device 30 does not function, or in case of inadequate power supply to the contraction layer 24, the outlet valve 28 receives no power supply or only an inadequate one, and then it opens so that the incompressible liquid located in the padding layer 26 can flow over the outlet valve 28 into the environment, i.e., the surrounding tissue in the chest cavity, as is shown in FIG. 2.

[0047] In FIG. 3 a second embodiment of a circulatory assistance system in the form of an annular cuff 40 is shown. Aside from the fact that this cuff 40 does not surround the apex of the heart 10, this has structurally and functionally the same design as the cuff 22.

[0048] As can be seen in FIGS. 1 to 3, the cuff 22 or 40 preferably extends along the entire ventricular wall 18 and is fastened to it by means not shown, preferably mounted in an annular shape.

[0049] In normal operation the sensor 32 detects the cardiac cycle of the heart 10. In an initial state the heart 10 is in the diastolic phase, in which it is relaxed and occupies the largest volume, wherein the two ventricles fill with blood. In this state the contraction layer 24 is supplied with power so that this is in the state of greatest possible expansion. The padding layer 26 filled with an incompressible fluid at this time is located internally against the cardiac wall and externally against the contraction layer 24. As soon as the control device 30 detects the beginning of systole, the power supply to the contraction layer is interrupted suddenly or according to a predetermined sequence, so that the contraction layer 24 thus draws together radially inward and transfers the resulting, radially inwardly directed forces to the ventricular wall of the heart. At the latest when the systolic phase of the cardiac cycle is completed, the contraction layer 24 is again supplied with power, so that this again expands radially and with it, moves the padding layer 26 away from the expanding ventricular wall 18.

[0050] Both the power supply and the power interruption over line 34 can preferably take place according to a preset voltage-time curve.

[0051] In FIG. 4 a third embodiment is shown, which differs from the previous embodiments in that the contraction layer 24 includes a number of adjacent annular sections 41, each of which is individually controlled by the control device 30, which for the sake of clarity is only shown for the annular section marked with reference symbol 41. This is normally a film that is subdivided into rings. Alternatively, individual film rings connected together may be provided.

[0052] Correspondingly, the padding layer 26 located beneath it is subdivided into a number of adjacent annular regions 44 separated by expandable partitions 42. Each annular region 44 has its own outlet valve 46, controlled by the control device (for the sake of clarity, only shown here for one outlet valve 46) into the environment.

[0053] The annular sections 41 are separately supplied with power by the control device 30 in a time-staggered sequence, synchronous with the cardiac contraction spreading from the cardiac apex. Thus, energization of the individual annular sections 41 takes place in a time-staggered manner in accordance with the typical spread of the muscular contractile movement of the heart.

[0054] FIG. 5 shows three schematic representations for demonstrating the functioning of the design according to FIG. 4. In FIG. 5a the contraction layer 24 is shown in a resting position, in which all annular sections 41 are supplied with power. Correspondingly, no pressure is applied to the ventricular wall 18.

[0055] In the position according to FIG. 5b the power supply to the first annular section 41 is interrupted, but not to the additional annular sections 41 and 41. Thus, the first annular section 41 draws together and contracts. Since an incompressible medium is contained in the corresponding annular space 44, in this way a pressure is exerted on the ventricular wall 18 at location 50.

[0056] When the power supply to the first annular section 41 is restored and instead the power supply to the adjacent annular section 41 is interrupted, the first annular section 41 expands again and the pressure at location 50 of the ventricular wall 18 relaxes, while the second annular section 42 draws together and at location 50, generates pressure on the ventricular wall 18. All of this is controlled by the control device 30, specifically synchronously with the propagation of the cardiac contraction from the cardiac apex. In this way, one annular section 41 after the other is energized and thus a pressure wave is produced, which likewise propagates synchronously to the propagation of the cardiac contraction.

[0057] Although the invention was illustrated in greater detail and explained by preferred embodiments, the invention is not limited by the examples disclosed, and other variations can be derived from these by the person skilled in the art without leaving the scope of protection of the invention. From this it is clear that a number of possible variations exist. It is also clear that embodiments named by way of example only represent examples that are not in any way to be perceived as limiting, for example, the scope of protection, the possibilities of application or the configuration of the invention. Instead the above description and the explanation of the figures will place the person skilled in the art in a position to concretely implement the exemplified embodiments, in which the person skilled in the art, knowing the disclosed concept of the invention, can make many changes, for example in terms of the function or the arrangement of individual elements named in an exemplified embodiment, without leaving the scope of protection defined by the claims and their legal counterparts, for example further explanation in the description.