WO2017134218A1

WO2017134218A1 - Artificial heart

Info

Publication number: WO2017134218A1
Application number: PCT/EP2017/052371
Authority: WO
Inventors: Stavros KARGAKIS
Original assignee: Kargakis Stavros
Priority date: 2016-02-03
Filing date: 2017-02-03
Publication date: 2017-08-10
Also published as: DE102016101868A1

Abstract

The invention relates to an artificial heart (1), in particular for simulating a human heart, comprising the following: - two pump chambers (2, 3) with a respective inlet opening (4) and an outlet opening (5), - a drive device (6) for changing the volumes of the pump chambers (2, 3), and - at least one transmission element (7) per pump chamber (2, 3) for transmitting forces between the drive device (6) and the respective pump chamber (2, 3). Each pump chamber (2, 3) has at least one flexible wall (8) and at least one rigid wall (9), and the inner volume of each pump chamber (2, 3) can be changed by moving the corresponding flexible wall (8) relative to the corresponding rigid wall (9). The force transmission between the drive device (6) and the respective flexible wall (8) of a pump chamber (2, 3) is carried out by means of at least one transmission element (7) which has a proximal end (10) and a distal end (11). The proximal end (10) of each transmission element (7) interacts with the drive device (6) in an articulated manner, and the distal end (11) of each transmission element (6) interacts with a flexible wall (8) of a pump chamber (2, 3) in an articulated manner. The aim of the invention is to provide an artificial heart which has smaller external dimensions than the prior art. According to the invention, this is achieved by transmission elements (7) with proximal ends (10) which can be moved on respective drive planes (12) that are oriented perpendicularly to a pump plane (13) of the distal ends (11) of the transmission elements (7), wherein at least one movement component of the proximal ends (10) is oriented perpendicularly to the pump plane (13).

Description

Artificial heart

Description Introduction

[01] The present invention relates to an artificial heart, in particular for simulating a human heart

two delivery chambers, each with an inlet opening and a

Outlet opening,

a drive device for changing the volumes of the delivery chambers, and at least one transfer element for transferring forces between the drive device and the respective delivery chamber, each delivery chamber having at least one flexible wall and at least one rigid wall and an inner volume of a respective delivery chamber

Movement of the associated flexible wall is variable relative to the associated rigid wall, wherein a force transmission between the drive means and a respective flexible wall of a delivery chamber by means of at least one

Transmission element having a proximal end and a distal end, wherein the proximal end of each transmission element hinged to the

Drive means and the distal end of each transmission element pivotally interact with a flexible wall of a delivery chamber.

[02] The "delivery chambers" effectively correspond to the heart chambers of a natural heart, thus providing the pumping volume by which blood is pumped through the respective body into which the artificial heart is inserted It is expedient for the walls of a respective delivery chamber to have a curved shape in order to be able to generate a directed blood flow.

In the context of the present application, the walls which can be flexible or rigid do not necessarily have to be separate, mutually detached walls. Instead, it is also conceivable that the flexible wall and the rigid wall are each formed only by wall parts or wall sections which are part of a one-piece body. In particular, it is conceivable that a delivery chamber of a one-piece, flexible membrane is spatially limited, wherein a portion of the membrane is disposed on a rigid housing or a rigid housing wall and by means of the connection with the housing loses its flexibility. Thus, such a portion of the membrane forms a "rigid wall" as described above Another portion of the membrane is not supported in the same way and thus, as it were, free to move in space, this portion then forming the "flexible wall" in the sense of the preceding Description.

[04] The terms "rigid" and "flexible" do not necessarily refer to the particular wall as such. This means that such a wall can also be understood as a "flexible wall" within the meaning of the present application, which is inherently rigid, but nevertheless movable in such a way that it can be moved relative to the associated rigid wall For example, a wall in the form of a rigid plate which is movably disposed within the artificial heart is also conceivable as a flexible wall in the sense of the present application In spite of this theoretical possibility of configuring the walls of a respective delivery chamber, a wall which is actually flexible in design is advantageous for use as a "flexible wall". [05] The movement of the flexible wall relative to the rigid wall goes in each one

Case associated with a change in the volume of the respective delivery chamber. In particular, the volume of the respective delivery chamber by means of the movement of the flexible wall is cyclically variable between a minimum and a maximum. Ideally, the volume is approximately zero when the minimum is present. In this state, all blood is displaced from the delivery chamber. In the presence of the maximum, however, the volume of the delivery chamber is maximum. Typically, in this state, the delivery chamber is at least substantially completely filled with blood.

The increase in the volume of a respective delivery chamber is associated with a suction effect, which leads to the blood is sucked, which then in the

Feed chamber flows. The position of the delivery chamber, in which the volume thereof is maximum, can consequently also be referred to as "suction position." Starting from this suction position, the blood is expelled from the same during the reduction of the volume of the delivery chamber until the volume of the delivery chamber is minimal. The position of the delivery chamber, in which this is the case, can therefore also be referred to as a "printing position". [07] The heart described above has at least two

Transmission elements, wherein at least one transmission element cooperates with a respective delivery chamber. Since the transmission elements are hinged at both ends, they are unable to transmit bending moments and / or shear forces. In other words, the transmission elements serve

excluding the transmission of compressive and compressive forces. In the static sense, the transmission elements can therefore be referred to as pendulum rods. The

Transmission elements thus cause a power transmission between the

Drive device and the respective associated delivery chamber by means of the transmission of compressive or tensile forces.

[08] The "interaction" of the transmission elements with the drive device, which is preferably arranged between the delivery chambers, and the flexible wall of a respective delivery chamber comprises both an immediate connection of the respective transfer element to one or both parts and an indirect connection conceivable that the distal end of a

Transmission element is connected with the interposition of a connecting part to the flexible wall of an associated delivery chamber.

State of the art

[09] An artificial heart of the type described above is already known in the art. For this purpose, reference is made to German Offenlegungsschrift DE 31 36 969 A1. This discloses an artificial heart with two delivery chambers, each of the delivery chambers each having a rigid and a flexible wall. A contraction of the delivery chambers is effected by means of a drive device which by means of

Transfer elements compressive and tensile forces respectively on the flexible walls and in this way causes a continuous change in the volumes of the delivery chambers.

[10] A disadvantage of the known construction can be seen that the drive device occupies comparatively much space between the delivery chambers. A compact, that is space-saving, construction is not given. [1 1] On the other hand, reference is made to international patent application WO 2013/060701 A1. This is similar to the artificial heart of the beginning

described type and to that of the aforementioned document, a drive means disposed between the delivery chambers. According to the document, the drive device can be executed in various ways, in each case transmission elements which are between the drive means and the flexible walls of the respective delivery chambers act to move in a plane of the drawing shown in the figures of the document.

Also in this construction, comparable to the said German Offenlegungsschrift the disadvantage that the drive means occupies a considerable space between the delivery chambers, whereby the artificial heart occupies a comparatively large volume in total.

task

The present application is therefore based on the object to provide an artificial heart, which has smaller outer dimensions compared to the prior art.

solution

The underlying object is achieved, starting from the artificial heart of the type described above according to the invention that the proximal ends of the transmission elements are movable in drive planes, said drive planes are oriented perpendicular to a pumping plane of the distal ends of the transmission elements. It is important that the proximal ends each have at least one

Have movement component which is oriented perpendicular to the pump plane. In other words, the movements of the proximal ends and the distal ends of the transmission elements do not take place in a common plane but in planes which are linearly independent of one another. These are referred to here as the "drive level" described and the "pump level".

[15] The "pumping plane" designates that plane of the artificial heart in which, so to speak, the flexible wall of a respective delivery chamber is "driven". It is understood that for contraction of a respective delivery chamber, the flexible wall must be moved to the associated rigid wall. This movement of the flexible wall takes place in a certain direction, which corresponds to a direction of movement of the distal ends of the transmission elements or of the transmission element. The

Pumping plane thus effectively coincides with a cross-sectional plane of the artificial heart, which includes both delivery chambers and this cuts longitudinally. The position of the pumping level results in particular from the below

Embodiments. The distal ends of the transmission elements are preferably guided so that they move during the operation of the artificial heart exclusively within the pumping plane. [16] The "drive planes" are oriented at least substantially perpendicular to the pumping plane and denote those planes in which the proximal ends of the

Transmission elements are moved. It is understood that depending on the position of a respective proximal end of a transmission element different drive levels may be present, which are oriented parallel to each other. Thus, in a sense, each transmission element has its "own drive plane", which are arranged at small distances from each other.Of course, it is conceivable that several proximal ends of transmission elements are located and move in identical planes, unlike the prior art distal ends and proximal ends of the transmission elements not in a common or in

moves in parallel planes, but in mutually linearly independent planes, wherein the drive planes are preferably perpendicular to the pump plane.

[7] The heart of the invention has many advantages. In particular, the movement of the proximal ends of the transmission elements in the plane perpendicular to the pump plane oriented drive plane is particularly useful to keep a dimension of the drive device in a direction parallel to the pump plane considered as low as possible. As a result, movement of the proximal ends is not required completely within the pumping plane. This ensures that the transmission elements are only temporarily with their entire length in the pumping level and only in this

Moment a maximum space between the delivery chambers occupy. Incidentally, the transmission elements are oriented so that they are not parallel to the pump plane. Consequently, during the operation of the artificial heart, the transmission elements continually change their orientation in space. In positions where the transfer elements are not completely in the pumping plane, a length of the transfer elements projected onto the pumping plane is less than their axial length. By the inventive "evasion" of the proximal ends of the transmission elements in their respective

Drive levels is therefore given the advantage that the distance between the

Delivery chambers and consequently the volume of the artificial heart as a whole

can be kept comparatively low. In an advantageous embodiment of the heart according to the invention are the

Transmission elements each drivable with the drive device such that they cyclically each occupy a maximum position and a minimum position, wherein the distal end of each transmission element in its maximum position at a maximum distance and in its minimum position at a minimum distance from the rigid wall of the respective associated delivery chamber located. By means of such Design, it is particularly easy to transfer a respective delivery chamber between its suction position and its printing position. It is particularly conceivable that all transmission elements of a delivery chamber are simultaneously in their maximum position or their minimum position. In the presence of the

Transmission elements in their maximum positions is the associated

Delivery chamber thus in its suction position (volume of the delivery chamber maximum).

Conversely, when the transmission elements are present, the delivery chamber is in its minimum position of its pressure position (volume of the delivery chamber minimal).

For a uniform distribution or initiation of forces in the flexible walls of the respective delivery chambers, it is particularly advantageous if each

Delivery chamber each having a plurality of transmission elements, in particular with at least two transmission elements, preferably with at least three

Transmission elements, more preferably with at least four transmission elements cooperate. When using a plurality of transmission elements per delivery chamber, it is also advantageous if the distal ends of the respective transmission elements are connected at different locations of each associated flexible wall. In this way, a distribution of the introduction of force by means of the transmission elements on the associated flexible wall is particularly easy. The single ones

Depending on their positioning, transmission elements can be of different lengths relative to a respective delivery chamber.

Alternatively or in addition to the use of several transmission elements per delivery chamber, it may also be of particular advantage if the heart according to the invention has at least one connection element by means of which at least one distal end of a transmission element is connected to a respective associated flexible wall of the associated delivery chamber , Such a connection element may in particular be designed flat, so that one of the flexible wall facing surface of the connection element cooperates with the flexible wall surface. Such a connection element is suitable, by means of the or the distal ends of the transmission elements in a sense "punctually" transmitted forces on a

To distribute effective surface of the flexible wall and to ensure in this way the widest possible introduction of the forces of the transmission elements on the flexible wall.

This is particularly advantageous insofar as for the generation of a directed blood flow by means of the heart according to the invention the contraction of a respective delivery chamber should be as even as possible, so that in the course of the transfer of Delivery chamber starting from its suction position in its printing position at least in

Essentially, all of the blood contained in the delivery chamber is forced out through the exit opening of the respective delivery chamber. However, the formation of a local cavity in which blood could possibly remain is especially detrimental to the operation of the artificial heart. Therefore, there is an interest in smoothly moving all locations of the flexible wall and avoiding local sacks or cavities.

[22] When using a connection element for connecting the distal end or ends of a transmission element to an associated flexible wall, it may be particularly advantageous to use a plurality of connection elements. This allows in particular an independent force introduction into the flexible wall. Advantageously, the various connection elements are connected to one another, in particular in such a way that they are movable relative to each other, in particular relative to each other rotatable. For example, it is conceivable the individual

Coupling connection elements with formation of hinges to each other. This design makes it possible for the various connection elements to have relative orientations that change relative to one another and in this way to be able to simulate a given geometry of the respectively associated flexible wall of the respective delivery chamber. This is particularly apparent from the below-described

Embodiments. [23] In a particularly advantageous embodiment of the heart according to the invention, the transmission elements are arranged in a specific manner on the drive device, in such a way that at least two transmission elements, preferably at least two transmission elements per delivery chamber, their respective maximum position and / or their respective minimum position at different times during the operation of the heart. In this embodiment, therefore, the individual transmission elements are not at the same time during the operation of the heart in their

Maximum positions or minimum positions. Such a design is based on the consideration that it can be advantageous for the pumping action of a respective delivery chamber if it to some extent executes a "directed contraction." This includes

understood that the flexible wall of the respective delivery chamber is moved in the form of a directed movement to the rigid wall.

This movement takes place in particular in such a form that the flexible wall in the course of the transfer of the respective delivery chamber of their suction position in their

Printing position is moved in a temporal sequence on the rigid wall to.

For example, it is conceivable that the outlet opening of the respective delivery chamber one end of the delivery chamber is connected. In this case, it is particularly advantageous if, for the displacement of the blood from the delivery chamber, the flexible wall is initially moved to one of the output opening facing away from the pumping chamber on the rigid wall and such movement takes place only as the last directly in the region of the outlet opening itself , A point in time at which the flexible wall comes into contact with the rigid wall at this point, which faces away from the exit opening, and thus locally the volume of the delivery chamber is reduced to zero, lies in this embodiment before a time at which one of the outlet opening further faces Site of the delivery chamber is locally contracted. The point at which the outlet opening of the delivery chamber is arranged, in accordance with this procedure, is preferably reached only at the end of the process of transfer of the delivery chamber into its printing position.

By this type of movement of the flexible wall, the blood from the

In a sense, the delivery chamber is "squeezed out" from one end of the delivery chamber to the other end that has the exit orifice

Contraction "of a delivery chamber is particularly advantageous for the generation of a directed blood flow and for the complete displacement of all possible blood from the delivery chamber.

An arrangement of the transmission elements on the drive device, which allows such a directed contraction of the delivery chamber, for example, be designed so that the transmission elements in different spatial orientations on the

Drive means are arranged, in such a way that they occupy their respective minimum position in the course of their movement by means of the drive means in different positions of the drive means (and thus at different times during operation of the heart), in which the distance between the distal end of the respective transmission element and the rigid wall of the associated delivery chamber is minimal. It is understood that the transmission elements preferably on the

Drive means are arranged such that, starting with the transmission element furthest from the outlet opening and ending with the transmission element arranged closest to the outlet opening one after another during a

Contraction of the delivery chamber take their minimum positions.

For producing a described "directed contraction", it is particularly advantageous if a respective flexible wall cooperates with at least three, preferably with at least four, transmission elements cooperate, which allow a force distribution in the flexible wall, wherein preferably a plurality of connecting elements is provided, which are hinged together.

When using at least two transmission elements per delivery chamber, it is advantageous if the proximal ends of these transmission elements at different

Positions are arranged on the drive device. This arrangement of the proximal ends makes it possible to adjust the above-described "directed contraction" of a delivery chamber, In particular, it is possible to control the spatial orientation of the individual

To make transmission elements different from each other and in this way to achieve that occupy their respective minimum position on the transmission elements at different times. Typically, the transfer elements in such an arrangement also take their maximum position too different

Time points. However, this does not necessarily have to be the case.

[29] The heart further embodying the invention, the drive device comprises at least one drive element in the drive plane or in one of the

Support plane parallel plane is mounted, wherein the drive element is preferably arranged between the delivery chambers. In such an embodiment, the proximal ends of the transmission elements can be particularly easily connected to the drive element, so that by means of movement of the drive element in the Antnebsebene or parallel to the drive plane level equally the proximal ends of the transmission elements are movable in corresponding drive levels.

[30] It is particularly advantageous if the drive device comprises at least two drive elements, which are each mounted rotatably about a bearing axis. The bearing axes are advantageously in the pumping plane of the artificial heart and are therefore aligned perpendicular to the drive plane. The use of two drive elements allows in particular a differentiated design of the

Movements of the individual transmission elements. In other words, it is not necessary to make the movement of a single driving member such that it is suitable for driving all the transmitting elements comprising the heart as a whole. The division into several drive elements facilitates the design of the motion sequences of the individual transmission elements up to such a degree to which certain movements using only a single drive element are not feasible. [31] When using multiple drive elements, it is particularly advantageous if these are coupled together in force transmitting manner. In particular, it is conceivable, the transmission elements by means of a positive connection, in particular by means of

Interlocking gears to connect with each other. This embodiment has the advantage that even in the presence of multiple drive elements only a single

Drive member is required to move the drive elements together. This follows the consideration that the drive of one of the coupled drive elements is transmitted due to the coupling directly to the other or the other drive elements and thus equally has their movement result. The coupling of the individual drive elements is accordingly for the embodiment of

Overall drive device of advantage, in particular, an energy-saving drive of the artificial heart can be realized. A further advantage is that by means of the coupling, the individual drive elements in each case run synchronously and there is no risk of adjusting over time asymmetry of the individual drive elements.

[32] In one possible embodiment of the heart according to the invention, individual drive elements can be formed, for example, by triangular discs which are arranged to a certain extent opposite one another, wherein mutually facing sides of the triangular discs are preferably provided with mutually corresponding toothings. By means of these teeth are the triangular

Disks in transferring manner connected to each other, so that the movement of one of the discs transmits directly to the other disc. The

triangular discs are each rotatably mounted about a separate bearing axis, said bearing axes are preferably arranged on the one hand parallel to each other and further preferably to the other in the pumping plane of the artificial heart. The

Triangular shape of the triangular discs is designed so that expand the individual discs, starting from their bearing axes in each case to the other disc towards. During operation of a drive device equipped with such drive elements, the two drive elements are each rotated about their bearing axes and thus describe a circular arc-shaped movement. The facing each other

Thus, sides of the triangular discs are not straight but have a circular arc along which they are described

Gears extend.

[33] Regardless of the presence of single or multiple drive elements, the heart according to the invention can then be particularly advantageous if it has at least one Drive member has, that is mounted rotatably about a drive axis perpendicular to the drive axis. Such a rotation of the drive member is particularly advantageous with regard to the energy efficiency of the heart according to the invention. In particular, it is conceivable to achieve the movements of the transmission elements and consequently the contractions of the delivery chambers solely on the basis of a rotational movement of the at least one drive member. A rotational movement has the advantage that during operation of the corresponding drive member at no time to a reversal of motion of the oscillating masses and thus energy consumption due to permanent

Accelerating and decelerating oscillating masses fails. In this way a very energy-efficient drive of the heart is made possible.

[34] With regard to the design of the drive member, it is also advantageous if this has a self-contained, preferably elliptical, outer edge. The geometry of such a drive member is particularly suitable for a movement of the transmission elements, for example with the interposition of a possible

Driving elements to make variable, in particular a

Movement speed of the individual transmission elements can be made variable over time.

[35] In this context, it may be particularly advantageous if the drive member has a circumferential groove, which preferably extends in the direction of the pump plane of the heart according to the invention. Such a groove is suitable for intermeshing positively with a corresponding journal of a drive element of the drive device, so that movement of the drive member causes the drive element to be dragged along by "dragging along." A corresponding embodiment can be removed from the exemplary embodiment described below If the form-fitting connection between the pin and the described groove is designed to be as frictionless as possible, it is understood that a reverse embodiment is also conceivable in which the drive member comprises a pin and the respective drive element a groove.

[36] The underlying object is further achieved by an artificial heart drive device comprising the drive device:

at least one drive axle as well

at least one drive member rotatably arranged about the drive axis, wherein the drive member by means of a drive, in particular an electric motor, is rotatably driven about the drive axis, so that the drive member during operation of Drive device performs a, preferably unidirectional, rotation about the drive axis, characterized in that the drive member is formed in the form of a cam, which preferably has a deviating from a circular shape elliptical shape. [37] The "drive link" describes in this context a part of

Drive device which is suitable for the transmission of forces starting from the actual drive. For example, it is conceivable that directly by means of

Drive member delivery chambers of an artificial heart are driven.

However, the drive member preferably only serves to drive at least one drive element.

[38] For the purposes of the present application, a "cam disk" is understood to mean a component which has a disk-shaped design and has a certain curved contour, the disk shape being due to the fact that one thickness of the cam plate clearly undercuts its other dimensions, in particular one exceeds along a major axis measured length of the cam whose thickness by at least a factor of 5, preferably at least by a factor of 7, more preferably at least by a factor of 10. The curve or the curved contour manifests itself in that a peripheral edge of the cam is curved Consequently, the circular shape can be considered as the simplest conceivable curved contour, In particular, the cam disc according to the invention can have a regular elliptical shape Alternatively, all other curve shapes are conceivable, in particular irregular curved shapes.

[39] The cam is preferably drivable so that it continuously performs a uniform rotation about the drive axis in the course of its operation. In particular, the cam can be connected to a drive shaft, wherein the latter can be driven by means of the drive. Alternatively, it is conceivable to drive the cam alternately, effectively performing a "back and forth" movement, each extending over a certain partial rotation angle, but this variant has the disadvantage that the cam as a whole must constantly be accelerated and decelerated The continuous overcoming of the mass inertia of the cam requires an increased use of energy, a unidirectional rotation of the

Cam around a drive axle is therefore particularly advantageous from the point of view of energy consumption of the drive device. Since the power consumption of an artificial heart driving device is of particular importance To be able to operate artificial heart as low maintenance over a long period of time, the drive device according to the invention is particularly advantageous.

[40] The drive device according to the invention has many advantages. In particular, it is suitable for driving an artificial heart. For example, it is conceivable to couple such a cam with a drive element, so that the drive element performs a movement in the course of rotation of the cam. For this purpose, it is conceivable to store the cam outwardly, so that it makes an "eggier" movement in the course of its rotation about the drive axle

Cam in an elliptical shape inevitably the case. The irregularity of the movement, which is at a different distance from the outer edge of the

Cam during rotation of the same expresses in a certain viewing angle relative to the drive axle, is adapted to move a drive element. This is possible in a particularly simple way by the drive element and the

Drive member positively engage with each other, in particular by means of a tongue and groove system. A corresponding embodiment is explained in more detail below.

[41] A drive element coupled to the drive member can be set into motion by the rotation of the drive member. Such a drive element can, for example, interact with transmission elements as described above and in this way operate a delivery chamber of an artificial heart. In principle, however, a drive element is not absolutely necessary, since it is also conceivable to transfer elements directly to the drive member

to join.

[42] If the drive device according to the invention comprises at least one drive element, it is particularly advantageous if the drive element and the drive element are coupled to one another in such a way that the drive element performs an at least partially rotatory movement as a result of the rotational movement of the drive element. For this purpose, it is particularly conceivable that the respective drive element is rotatably mounted about a bearing axis, wherein by means of the coupling between the drive and the drive element, for example, an "up-and-down movement" is transferable to the drive element.

Due to the rotational support of the drive element selbiges performs as a result of this movement therefore a partial rotation about the respective bearing axis. It is understood that any transmission elements that interact with such a drive element, can be easily cyclically moved between its maximum position and its minimum position. It follows that by means of such a drive device Particularly simple delivery chambers of an artificial heart can be continuously transferred alternately between their suction positions and their pressure positions.

[43] As already described above, when used, it is at least one

Drive element particularly easy to couple this to the drive member by both parts are coupled together by means of a tongue and groove system. Here, one of the two parts has a groove, with one on the other part

arranged pin cooperates positively. In a particularly advantageous embodiment, for example, the cam has a circumferential groove and the respective drive element via a corresponding pin which extends into the groove. By means of the drive of the drive member, the drive element is "dragged" along with the drive member as a result of the positive connection, and as a result, is moved, in which way a rotational movement of the drive member can be transferred to the drive element.

Furthermore, it may be of particular advantage if the inventive

Drive device has at least two drive elements that are in force

transmitting manner are coupled together, in particular by means of mutually corresponding toothings. As explained above, the

It is understood that embodiments of the drive device according to the invention are also conceivable, which have more than two Ahtriebselemente .The coupling of the individual Drive elements together with one another has the advantage that the movement of one of the drive elements is transmitted directly to the respective other drive element and consequently a separate drive is not necessary for each individual drive element In other words, the drive elements of the drive device according to the invention by means of their coupling alone by the action of a single drive member to be driven.

[45] When using two drive elements, it may also be advantageous if they are rotatably supported in each case about a bearing axis, wherein the bearing axes of the drive elements are preferably oriented parallel to each other and from each other

spaced apart. The arrangement of the drive elements on spaced bearing axes makes it possible to connect various transmission elements at different locations within the artificial heart and a suitable by means of the selection of a suitable location on one of the drive elements

Assign Movement Profile. Thus, for example, the arrangement of a proximal end of a transmission element in the immediate vicinity of a bearing axis of a drive element means that the respective transmission element in the course of a complete

Movement cycle of the drive member or the associated drive element undergoes only a minimal deflection, since the radial distance of the proximal end of the

Transmission element to the bearing axis is very low. In reverse logic can be achieved by the arrangement of a proximal end of a transmission element at a large distance from the respective associated bearing axis of the associated drive element, a particularly pronounced movement of the respective transmission element during operation of the drive means. By means of the use of a plurality of drive elements, such different movement profiles of transmission elements can be carried out particularly easily at different locations within an artificial heart and thus at different distances relative to the flexible conversions of the delivery chambers. For the design of drive elements, it may be particularly advantageous to form these each in the form of triangular discs extending from their bearing axes extending toward each other, preferably the

Drive elements engage positively on mutually facing edges with each other. This exercise can be favorable in particular for the operation of an artificial heart if the bearing axes of the triangular discs intersect the delivery chambers of the associated artificial heart in an edge region or extend near an edge region of the delivery chambers. Contact sections of the drive elements, on which the drive elements are in contact with each other, are at the same time preferably arranged so that they - viewed on the delivery chambers - correspond with central regions of the delivery chambers.

[48] This is based on the consideration that a deflection of a respective point of a drive element during operation of the drive device is greater, the further said point is located away from the associated bearing axis of the drive element. For the contraction of a delivery chamber, that is movement of the flexible wall on the rigid wall to, is in the edge region of the respective

Delivery chamber only a relatively small relative movement between the flexible wall and the rigid wall necessary; in the middle area of the

Conveying chamber, however, requires a comparatively large relative movement between the two walls. Accordingly, it is necessary for transmission elements with different locations of the flexible wall of a respective delivery chamber cooperate, a different magnitude of motion amplitude as a function of the point at which a respective distal end of a transmission element is connected to the flexible wall of an associated delivery chamber.

[49] By means of the described arrangement of the drive elements, the

Movement amplitude of transmission elements, which cooperate with a central region of a respective flexible wall, are made particularly large, while in a peripheral region of the flexible wall, only a small amplitude of movement occurs. This results in the result that the described embodiment of

Drive elements are adapted to a certain extent the kinematic needs of the flexible walls of the delivery chambers and thus allow a particularly efficient operation of the associated artificial heart.

embodiments

[50] The heart according to the invention is explained in more detail below with reference to an exemplary embodiment, which is illustrated in the figures. Show it:

1 shows a cross section through an inventive artificial heart,

Fig. 2: an isometric view of the drive means of the invention

heart

3 shows a plan view of the drive device according to FIG. 2 and FIG

FIG. 4: A side view of the drive device according to FIG. 2. [51] The present exemplary embodiment, which is illustrated in FIGS. 1 to 4, comprises an artificial heart 1, which has two delivery chambers 2, 3 lying opposite one another. Between the delivery chambers 2, 3, a drive device 6 is arranged, which is adapted to change the volumes of the delivery chambers 2, 3. In this way it is possible by means of the drive means 6, by cooperation with the

Delivery chambers 2, 3 to generate a directed blood stream. For this purpose, the

Delivery chambers 2, 3 each have an inlet opening 4 and an outlet opening 5, which are each fluidically connected to an interior of the respective associated delivery chamber 2, 3.

[52] In the position of the artificial heart shown in FIG

Delivery chambers 2, 3 in the suction position. That is, the volumes of the

Delivery chambers 2, 3 are in the position shown in Figure 1 each maximum. A

Change in the volumes of the delivery chambers 2, 3 is achieved in that a flexible Wall 8 a respective delivery chamber 2, 3 is moved to the associated rigid wall 9 to. The rigid walls 9 are connected directly to a housing 26 enclosing the artificial heart 1. This housing 26 is designed so stiff that it is suitable for receiving compressive forces. By means of the connection of a partial region of a material surrounding a respective delivery chamber 2, 3, the rigid wall 9 of the respective delivery chamber 2, 3 is generated. This means that not necessarily the actual surround the respective delivery chamber 2, 3 material or component must have an inherent rigidity, which gives the rigid wall their increased rigidity; instead, as in the example shown here, the rigid wall can be created by connecting the respective material to another rigid component (in this case to the rigid housing 26).

[53] The flexible walls 8 of the delivery chambers 2, 3 are each arranged opposite their associated rigid walls 9. A change in the volumes of the delivery chambers 2, 3 takes place by means of a relative movement between a respective flexible wall 8 and the associated rigid wall 9, wherein in each case the flexible wall 8 is moved towards the rigid wall 9. It is understood that for this purpose a force on the respective flexible wall 8 is required. This force is generated in the heart 1 according to the invention by means of the drive device 6. For this purpose, the drive device 6 has a drive, not shown, which may be formed for example by an electric motor. To supply such a drive with energy, the heart 1 according to the invention can have, for example, an energy store in the form of a rechargeable battery.

[54] Of particular importance for the heart 1 according to the invention

Transmission elements 7, which are used for power transmission between the drive device 6 and a respective flexible wall 8 of a delivery chamber 2, 3. In the example shown, each of the delivery chambers 2, 3 acts with four each

Transmission elements 7 together the transmission elements 7 each have a proximal end 10 and a distal end 11, wherein the proximal ends 10 each with the drive means 6 and the distal ends 11 each with one of the flexible

Walls 8 interacts. The transmission elements 7 are both at the

Drive device 6 as also articulated to the respective associated flexible wall 8, so that by means of the transmission elements 7 only tensile forces and

Compressive forces between the drive device 6 and the respective delivery chamber 2, 3 are transferable. A transmission of bending moments and / or shear forces is not possible, at least in the static sense. It is understood that the articulated connections the transmission elements 7 by design subject to at least a minimum of friction, whereby an idealized in the static sense articulated connection can not be achieved to 100%. The friction occurring in the joints of the transmission elements 7 ultimately leads to a minimal entry of transverse forces and consequently to a minimal formation of bending moments in the transmission elements 7. However, this does not take place as planned; the order of magnitude of the shear forces thus transmitted and

Bending moments is negligible in any case.

[55] On the side of the flexible walls 8, the transmission elements 7 are connected with their distal ends 11 directly to connection elements 14. The

Connection elements 14 are in turn connected directly to the respective flexible wall 8. A geometry of the connection elements 14 results particularly well with reference to Figure 2. The transmission elements 7, which are designed here rod-shaped, transmit their axial forces at least substantially punctually, that is, an introduction of a force acting in the transmission elements 7 force in a respectively connected component acts on a spatially limited place. Such a power transmission is for one

direct drive a flexible wall 8 a delivery chamber 2, 3 is not necessarily suitable; In particular, the flexible wall 8 may be of such low rigidity that it would only locally deform at points at a respective junction of a distal end 11 of a transmission element 7. For this reason, in the present embodiment, the connection elements 14 are used, the one

Distributing the forces transmitted by the transmission elements forces on an increased area of each associated flexible wall 8 effect. In this way it is ensured that the flexible wall 8 is uniformly deformed or moved by driving means of the drive means 6 and in this way a reliable regulation of the volume of the respective associated delivery chamber 2, 3 allows.

[56] In the present example, for each of the delivery chambers 2, 3, a plurality of connection elements 14 are used, namely three. The individual connection elements 14 are connected to each other by means of joints 22, so that the connection elements 14 can rotate relative to each other about an axis of rotation. This has the advantage that the connecting elements 14 can move in different ways along the respectively associated flexible wall 8 and in this way can simulate a movement of the flexible wall 8 better.

[57] The distal ends 1 of the transmission elements 7 are moved during operation of the heart 1 according to the invention in a pumping plane 13 which corresponds to the plane of the drawing of FIG. The pumping plane 13 is further characterized by motion vectors 24 of Defined distal ends of the transmission elements 7, which result from Figures 1, 2 and 3. The motion vectors 24 of the distal ends 11 are respectively in the

Based on the representation of Figure 1, it follows that the flexible wall 8 of a respective delivery chamber 2, 3 in the direction of

Movement vectors 24 during operation of the artificial heart 1 "back and forth." This movement of the flexible wall 8 leads to an ongoing

Change in the volume of the respective associated delivery chamber 2, 3 and thus causes their pumping action.

[58] As already indicated above, in the position shown in FIG. 1, the transmission elements 7 are each in their maximum position, in which there is a distance between a respective distal end 11 of a respective transmission element 7 to the associated rigid wall 9 of the associated delivery chamber 2 , 3 is maximum. This maximum position of the transmission elements 7 corresponds to the suction position of the respective delivery chamber 2, 3. The opposite of the maximum position of the transmission elements 7 is the minimum position in which the described distance between the distal end 11 and rigid wall 9 is minimal. Ideally, the presence of the

Transmission elements 7 in their minimum positions, the flexible wall 8 and the rigid wall 9 of the respective delivery chamber 2, 3 in direct contact with each other, so that the volume of the associated delivery chamber 2, 3 is minimal. The delivery chamber 2, 3 is therefore in its printing position.

[59] The proximal ends 10 of the transmission elements 7 are directly to the

Drive device 6 connected. As can be seen from the figures, the individual transmission elements 7 are at different locations on the drive device 6

arranged so that they are each oriented differently in space. In other words, the transmission elements 7 are not arranged parallel to one another.

[60] In the example shown, the drive device 6 comprises a drive element 18 and two drive elements 15. The drive element 18 is formed by a cam plate which has an elliptical shape. The shape of the drive member 18 can be seen particularly well with reference to FIG. The drive member 18 is mounted on a drive shaft 23 which is drivable by means of the drive, not shown. The drive shaft 23 - and therefore the

Drive member 18 - are rotatably mounted about a drive axis 20. The drive member 18 and the drive shaft 23 are connected to each other such that the rotation of

Drive shaft 23 is transmitted directly to the drive member 18. In particular, the drive member 18 and the drive shaft 23 may be integrally connected to each other. The drive member 18 has a circumferential groove 19, which is made equally Figure 2 shows. This groove 19 is adapted to engage with a corresponding, not shown in the figures pin and form a positive connection with this. This pin is arranged on one of the drive elements 15, which cooperates with the drive member 18. In this way, it is possible that a movement of the drive member 18 is transmitted to the associated drive element 15, wherein the power transmission takes place by means of the described positive connection between the pin of the drive element 15 and the groove 19 of the drive member 18.

[61] During operation of the artificial heart 1, the drive shaft 23 and with it the drive member 18 are driven in a rotational direction. This drive is such that the drive member 18 continuously rotates about the drive shaft 20, typically without changing its direction of rotation. The rotation of the drive member 18 causes due to the coupling with the associated drive element 15 directly one

Movement of the drive element 15. The drive elements 15 are rotatably mounted in each case about mutually parallel and spaced-apart bearing shafts 16. Further, the drive elements 15 are coupled by means of a toothing 17 in force transmitting manner with each other. As a result, a movement of one of the drive elements 15 is transmitted directly to the other drive element 15, so that independent movements of the drive elements 15 are not possible. This design contributes to the fact that it is sufficient for the drive of both drive elements 15 to drive only one of the two drive elements 15 directly.

[62] The rotation of the drive member 18 thus leads to both

Drive elements 15 move alike. The movement of the drive elements consists in a cyclical up-down movement, with an upper maximum position of the drive elements 15 being shown in FIGS. 2 and 4. This upper maximum position describes a position of the drive elements 15 in which there is no further "upward" movement Thus, in their maximum position, the drive elements 15 are to a certain extent in a reversal position, after which they reverse their direction of rotation about their respective bearing axis 16. FIG cyclic movement of the drive elements 15 is achieved by means of the elliptical shape of the drive member 18 and its positive coupling to one of the drive elements 15.

[63] It follows that the drive elements 15 move in a drive plane 12, which runs parallel to a plane of the drawing of FIG. As a result of the connection of the proximal ends 10 of the transmission elements 7 with the drive elements 15, these proximal ends 10 also respectively move in drive planes 12

Drive planes 12, are perpendicular to the pumping plane 13 described above oriented. They also arise from the movement vectors 25 of the proximal ends 10 of the transmission elements 7 shown in FIGS. 2 and 4. It is understood that the motion vectors 25 of the proximal ends 10 are perpendicular to the

Motion vectors 24 of the distal ends 11 of the transmission elements 7 are oriented. Due to the rotational movement of the drive elements 15 change the

Motion vectors 25 continuously their orientation, since the proximal ends 10 of the transmission elements 7 move in a circular path. This design is

according to the invention for the course of movement of the individual transmission elements. 7

especially beneficial. [64] This is based on the consideration that the transmission elements 7 in the course of the transfer of the delivery chambers 2, 3, starting from their printing positions in their

Suction positions must be removed in any way from the rigid walls 9 of the delivery chambers 2, 3. In contrast to the prior art, this invention proposes a movement that makes it possible not completely to move the individual transmission elements 7 within the pumping plane 13, but out of the pumping plane 13. As a result of this type of movement of the transmission elements 7, their lengths projected onto the pump plane 13 are continuously changed during operation of the drive device 6. Consequently, the transmission elements 7 only occupy a maximum space within the pumping plane 13 when they are in their respective positions

Minimum position. The "evasion" of the proximal ends 10 of the

Transmission elements 7 down and up (viewed from the pumping plane 13) makes it possible to significantly reduce a space required between the delivery chambers 2, 3 over the prior art and thus to reduce the volume of the entire heart 1 according to the invention. [65] The special type of design of the drive device 6 also makes it possible to operate the same particularly energy-saving and consequently to keep the energy consumption of the heart 1 according to the invention low. In this case, the drive device 6 allows the transmission elements 7 to be connected to the drive elements 15 in different positions. This has the advantage that by means of a clever arrangement of the individual transmission elements 7, a respective flexible wall 8 of an associated delivery chamber 2, 3 can be operated using a specific "pumping direction." This is based on the consideration that the passage of the individual

Transmission elements 7 by their minimum position during operation of the

Drive device 6, the movement between the flexible wall 8 and the associated rigid wall 9 is providable with one direction, so that the associated delivery chamber 2, 3 is in a sense "squeezed out." The articulated connection of the individual

Connecting elements 14 favors such an independent movement of the individual transmission elements 7. A directed in this manner movement of a respective flexible wall 8 has the particular advantage that the blood contained in the associated delivery chamber 2, 3 are particularly easy pressed in a particular flow direction can, whereby the desired generation of a directed blood flow by means of the heart 1 according to the invention is particularly well possible.

[66] In the example shown, the drive elements 15 are each triangular in shape, each having two side cheeks 27 which are arranged parallel to one another. Between the side walls 27 is always a free space. In one of the two drive elements 15, the drive member 18 is arranged in ebendiesem free space, wherein the drive shaft 23 extend through associated recesses 28 of the side walls 27 of the associated drive element 15. The triangular configuration of the drive elements 15 is used in particular to the mutually corresponding toothings 17 along sides of the facing

Drive elements 15 to be able to pull so far that even in the presence of the

Drive elements in their upper or lower reversing positions in each case one

Coupling of the drive elements 15 is ensured.

[67] The features described in connection with the present embodiment are basically independent of each other, if this is the

Professional makes sense. The features described here are not necessarily dependent on the combination with the other features in each case but can be implemented in principle detached from each other.

LIST OF REFERENCE NUMBERS

1 heart

2 delivery chamber

3 delivery chamber

4 entrance opening

5 outlet opening

6 drive device

7 transmission element

8 Flexible wall

9 Rigid wall

10 Proximal end

1 1 Distal end

12 drive level

13 pump levels

14 connection element

15 drive element

16 bearing axis

17 toothing

18 drive member

19 groove

20 drive axle

21 housing

22 joint

23 drive shaft

24 motion vector (distal end)

25 motion vector (proximal end)

26 housing

27 side cheek recess

Claims

claims

Artificial heart (1), in particular for the reproduction of a human heart

two delivery chambers (2, 3) each having an inlet opening (4) and an outlet opening (5),

a drive device (6) for changing the volumes of the delivery chambers (2, 3) and

at least one transmission element (7) for transmitting forces between the drive device (6) and the respective delivery chamber (2, 3) per delivery chamber (2, 3),

each delivery chamber (2, 3) having at least one flexible wall (8) and

at least one rigid wall (9) and an inner volume of a respective delivery chamber (2, 3) by means of movement of the associated flexible wall (8) is variable relative to the associated rigid wall (9), wherein a power transmission between the drive means (6) and a respective flexible wall (8) of a delivery chamber (2, 3) by means of at least one transfer element (7) having a proximal end (10) and a distal end (11), the proximal end (10) of each Transmission element (7) articulated with the drive means (6) and the distal end (1 1) of each transmission element (6) hingedly cooperate with a flexible wall (8) of a delivery chamber (2, 3), characterized in that

the proximal ends (10) of the transmission elements (7) are each movable in drive planes (12) oriented perpendicular to a pumping plane (13) of the distal ends (11) of the transmission elements (7), at least one component of movement of the proximal ends (10) is oriented perpendicular to the pump plane (13).

Artificial heart (1) according to claim 1, characterized in that the

Transmission elements (7) in each case by means of the drive means (6) are driven such that they each occupy a maximum position and a minimum position, wherein the distal end (1 1) of a respective transmission element (7) in its maximum position at a maximum distance and in its minimum position at a minimum distance from the rigid one

Wall (9) of the respective associated delivery chamber (2, 3) is located.

Artificial heart (1) according to claim 1 or 2, characterized in that each delivery chamber (2, 3) cooperates in each case with a plurality of transfer elements (7), wherein the distal ends (1 1) with a respective

Delivery chamber (2, 3) cooperating transmission elements (7) act on different locations of the associated flexible wall (8).

Artificial heart (1) according to one of claims 1 to 3, characterized by at least one connection element (14), by means of which at least one distal end (1) of a transmission element (7) to the flexible wall (8) of the respective associated delivery chamber (2, 3) is connected, wherein the connection element (14) cooperates with the flexible wall (8).

Artificial heart (1) according to one of claims 1 to 4, characterized in that the transmission elements (7) are arranged on the drive device (6) such that at least two transmission elements (7), preferably at least two transmission elements (7) per delivery chamber ( 2, 3), their respective

Achieve maximum position and / or their respective minimum position at different times during the operation of the heart (1).

Artificial heart (1) according to one of claims 1 to 5, characterized in that in the presence of the drive device (6) in at least one specific drive position, preferably in the presence of the drive means in any drive position, at least two to the same delivery chamber (2, 3) belonging transmission elements (7), preferably all to the same delivery chamber (2, 3) belonging transmission elements (7), have a different spatial orientation

Artificial heart (1) according to one of claims 1 to 6, characterized in that the drive device (6) comprises at least one drive element (15) which is arranged in the drive plane (12), wherein the drive plane (12) preferably between the Delivery chambers (2, 3) extends, wherein the

Drive element (15) is further preferably movably mounted within the drive plane (12).

Artificial heart (1) according to claim 7, characterized in that the

Drive device (6) comprises at least two drive elements (15), each about a bearing axis (16) are rotatable, wherein the bearing shafts (6) are preferably arranged parallel to each other and further preferably perpendicular to the drive planes (12).

Artificial heart (1) according to claim 8, characterized in that the

Drive elements (15) are coupled in force transmitting manner with each other, in particular by means of corresponding toothings (17) mesh with each other.

Artificial heart (1) according to one of claims 1 to 9, characterized in that the drive device (6) has at least one drive member (18) which is rotatable about a drive axis (20) perpendicular to the working planes (12).

Artificial heart (1) according to claim 10, characterized in that the drive member (18) has a self-contained, preferably elliptical, outer edge.

Artificial heart (1) according to claim 10 or 1 1, characterized in that the drive member (8) has a circumferential groove (19) which engages positively with a pin of a drive element (15) of the drive means (6), so that movement of Drive member (18) triggers a movement of the drive element (15), wherein preferably a complete revolution of the drive member (18) about its drive axis (20) a complete cycle of movement of

Drive element (15) corresponds.