DE2513489A1 - PORTABLE ARTIFICIAL KIDNEY - Google Patents

Description

DR. MÜLLER-BORE DIPL.-ING. GROENING DIPL.-CHEM. DR. DEUFEL DIPL.-CHEV. DR. SCHÖN "! PL. THYS. HERTEL

Hünchen, den * "'■' · S / Hl / We-th - S / S 89-29

Sandoz Patent GmbH
Loerrach

Portable artificial kidney

The invention relates to and relates to artificial animals particularly to a compact, portable, lightweight artificial kidney.

Artificial kidneys have been used for some time and have been found useful to diseased human kidneys partially to replace. When using such systems, blood is drawn from a patient and a dialysis facility supplied through which a dialysate solution or washing liquid circulates. Through the process of dialysis they become chemical Foreign matter or pollutants, electrolytes and water in the blood transferred into the dialysate solution or the washing liquid (and in some cases vice versa), through the thin walls a membrane, for example through hollow fibers, in which the blood flows. The dialysate solution that removes the foreign matter and contains water, is led out of the dialysis machine and removed, and the blood is returned to the patient fed. This process of removing foreign matter

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and water from the blood is called hemodialysis.

Although the systems of an artificial kidney or the hemodialysis facilities, which are currently in use are generally useful, however, they show the drawbacks that the blood Damage is inflicted that they are large, that they are expensive, that they are complex and that they are in general are unsuitable for transport. In part, these disadvantages are due to the fact that in such systems The pumps used are large and heavy and complex piping is required to carry the blood and the dialysate solution to promote. The use of baths with dialysate solution of large volume also contributes to the fact that known systems are not transportable.

The object of the invention is to create a compact and portable system of an artificial kidney.

To solve this problem, the invention provides that a Dialysis element is provided through which a patient's blood and a dialysate solution can circulate to a transfer of harmful substances and water from the blood into the solution to enable a blood transport system to continue to exist is to return blood from the patient that there is still a first pump, which is in the blood transport system is built in that the first pump has a flexible housing, which when it is alternately compressed and released, causes blood to be in the blood transport system flows that a dialysate source and a dialysate sink are still present, that a dialysate transport system continues is provided to transfer dialysate solution from the dialysate source to the dialysis element and from the dialysis element to promote the dialysate sink that a second pump is still present, which in the dialysate transport system

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is built in that the second pump has a flexible housing, which when it is alternately compressed and is released, causing dialysate solution to be in the dialysis transport system flows, and that a pump actuator ε device is present, which is used to the housing squeeze and release the first and second pumps, thus in the blood transport system and in the dialysate transport system a pumping effect is caused.

In the system of the artificial kidney according to the invention, the pump pressure and the suction for conveying "blood" can be used Dialysate solution are specified and controlled, and the dialysate source and the dialysate sink can be combined in a single filter and chemical treatment element to provide a to form closed dialysate circulation system.

A particularly preferred embodiment according to the invention. provides that a dialysis element is present through which A patient's blood, and dialysate solution circulate to prevent the passage of unwanted chemicals and water from it to allow the blood into the solution that a blood transport system continues to be in place to carry blood from the patient to convey the dialysis element and further from the dialysis element back to the patient that continues to have a dialysate transport system is present in order to supply dialysate solution to the dialysis element and to remove it from this again, and that a first and a second pump are provided, which in the blood transport system and are inserted into the dialysate transport system, respectively, to the blood and the dialysate solution - each in the blood transport system and to flow the dialysate transport system. The system also includes a device for actuating the first and second pump, so that a pulsating pumping action ' for the blood and the dialysate solution.

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According to a preferred embodiment of the invention are Pumps provided with a flexible housing, which then when it is alternately compressed and released again is, respectively, the pressure and the suction, which are required to the blood and the dialysate solution in the to let the respective transport system flow.

The dialysate source and sink can have a container, which is arranged in the dialysate transport system and through which dialysate solution flows, and it can also have a filter device be arranged in the container to remove pollutants or foreign substances from the dialysate solution when the Solution flows through the container.

The dialysate transport system can have an accumulator that has a jacket and a device that serves to the To install jacket in the dialysate transport system so that a passage of dialysate solution from the dialysate transport system into the jacket and from the jacket back into the dialysate transport system. The jacket can be designed to be flexible be. Furthermore, the dialysate transport system can have a collector, which in turn has a compressible cover can, which is inserted into the dialysate transport system in order to take up excess dialysate solution.

According to the invention are also a pulsation pump and a Vo11zykluspumpe provided for use in the invention Hemodialysis facility or artificial kidney are suitable.

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The invention is described below, for example, with reference to FIG Drawing "; in this show:

1 shows a schematic overall representation of an embodiment according to the invention,

FIG. 2 shows a section through a pump of the type shown in FIG Kind,

FIG. J shows a section through the vacuum regulator according to FIG. 1,

4A to 4C each show a plan view of the blood and Dialysate solution pump including the pump actuation device and holding plate,

5A to 5C each show an end view of the blood and dialysate solution pump including the pump actuator and the holding plate,

6A and 6B each show an end view of an alternative embodiment of the blood and dialysate solution pump as well as the pump actuation device,

FIG. 7 shows a plan view of the embodiment according to FIG. 6A and 6B, with the pump housings compressed, and

8 shows a full cycle pump made in accordance with the invention is.

A schematic representation of the artificial kidney system or hemodialysis device according to the invention is shown in FIG of Fig. 1 reproduced. The system generally includes a blood transport system 2 through which a patient's blood

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circulates, and a dialysate transport system. 6, by which Dialysate solution circulates. Both the blood and the dialysate solution are passed through a dialysis element 38, in which by diffusion chemical waste and water from removed from the blood. The blood is drawn through the dialysis element 38 through a bundle of hollow fiber strands (or passed through another suitable membrane arrangement), which are shown in Fig. 1 as a single tube 42 that is immersed in the dialysis solution contained in the dialysis element is included. As the blood passes through the dialysis element 38, chemical waste and water become transferred into the solution through the thin walls of the fiber strands. This hemodialysis process is known in principle and has been performed in artificial kidneys for a number of years. The structure of the dialysis elements is also known. ■

The blood transport system 2 has a pipe 4, a pump 14 and a single needle cannula 18 of known type on. Of course, the blood transport system 2 could also be in Connection with conventional double-needle EL needles is just as good can be used with the single needle cannula. With the single needle cannula the blood is alternatively withdrawn from the patient by the pump 14 or supplied to the patient.

The pump 14 is connected to the pipeline 4, respectively to apply the required pressure and the required suction so that the blood in the blood transport system 2 can circulate. According to FIG. 2, the pump 14 has a flexible cylindrical housing 202 which is open at both ends is, further has an inlet valve 210, which is connected to one side of the housing, and an outlet valve 206, which is attached to the other side of the housing. Each valve has a valve seat 214 and 222 and one

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Valve flaps 218 and 226 open to allow blood flow into and out of the pump housing 202 to control. The pump 14 according to FIG. 2 is built into the blood circulation system 2 in such a way that blood is drawn from the cannula 18 flows through the pump to the dialysis element 58. Be it it should be noted that the housing 202 could have other shapes that differ from the cylinder shape shown, as long as the pumping action described below is carried out properly.

The pump 14 is actuated by compressing the pump housing by means of a compression element 16 and then is released again. A motor 84 is mechanically coupled to the compression element 16 in such a way that the pump housing is alternately compressed and released again. While the pump housing is compressed, As is shown schematically in FIG. 1, the shut-off valve 30 is closed by the blood in the pump, while the shut-off valve 34 is opened so that blood is drawn from the pump can flow to the dialysis element 38. When the pump housing is released again, it takes on its normal shape again due to its own elasticity, creating a vacuum is generated, which closes the shut-off valve 34- and that The shut-off valve 30 opens, so that blood is sucked from the patient through the cannula 18 into the pump.

The valve 26 and pump 14 cooperate to move the blood in one direction through the blood transport system flows. When the pump housing is squeezed, nxBimt the pressure of the blood in the pipeline 4 and thus in the valve 26, to a value which is greater than that atmospheric pressure, whereby the valve 26 is opened and Blood flow from the pipeline into the dialysis element 38

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can, through the valve 26 and the needle 22 back to the patient. When the pump housing is released, it creates a negative pressure in the cannula 18, which is less than the atmospheric pressure so that the valve 26 is closed and thereby blood from the patient through the cannula 18 in the pump 14 is brought, but not from the Kohrleitung in the dialysis element 38 through the valve 26 to the pump. The pump 14 and the valve 26 thus work together in such a way that alternating blood from the patient into the pump 14 and then blood is brought from the pump 14 into the dialysis element 38, and back through from the dialysis element 38 the valve 26 to the patient.

The pump 14 thus delivers a non-occlusive pumping action, so that the blood is treated gently by the put-up process. In the case of a rotary pump, blood that is located between such parts of the pump could mechanically move towards one another act, may be impaired. Only a very short pipeline is required for the pump 14, so that the foreign body area with which the blood in contact during the dialysis process is kept to a minimum must come.

The housing of the pump 14 can be made of latex rubber, silicone rubber or another suitable elastic material. Has a wall thickness of essentially 3 nim (1/8 of an inch) proved to be particularly suitable for the housing when either latex rubber or silicone rubber is used, to develop the suction required to aspirate the blood from the patient.

The dialysate transport system 6 according to FIG. 1 ensures that dialysate solution is fed from a dialysate source to the dialysis element

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is supplied and that dialysate solution is supplied from the dialysis element 38 to a dialysate sink. According to FIG. 1 acts a chemical cleaning container 46 as both a dialysate source and a dialysate sink. The cleaning container contains 4-6 a bed of activated carbon particles or charcoal particles and another chemical agent to make the dialysate solution to be treated as it passes through the cleaning container. The cleaning container 46 is divided by a divider 48, which, as shown, may have an inverted T-shape, into a one-way bin 50 into which the dialysate solution from the dialysis element 38 is pumped in, and divided into an outlet chamber 5 ^, from which dialysate solution is taken for further transport to the dialysis element 38. By dividing the cleaning container 46 in this way the dialysis solution is made to contain the activated charcoal particles or the charcoal particles and other chemical means to flow through, so that in this way a treatment of the dialysate solution with maximum effect is achieved. The dialysate solution is pumped into the dialysis element 38 in order to flow through the hollow blood-carrying fibers, represented by tube 42 to facilitate the dialysis process described above.

Although the dialysate source and the dialysate sink in the cleaning container 46 are combined, it should be noted that the system of FIG. 1 can also be used in conjunction with a conventional Way, sink separate from the source could be used.

The dialysate transport system 6 has a pump 52 which is constructed similarly to the pump 14 of the blood transport system 2 in order to circulate the dialysate solution through the dialysis element 38 allow. The pump 52 is in the part of the dialysate transport system built in, which solution from the dialysis element 38 to Cleaning tank 46 leads. The one driven by a motor

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Compression element 16, which actuates pump 14, actuates also the pump 52.

The dialysate transport system 6 also has an accumulator 66, the puncture of which is explained below, furthermore has a collector 70, the function of which is also explained below, and comprises a vacuum regulator 7 ^ ₅ by means of which the vacuum of the dialysate solution within the dialysis element 38 can be controlled. The accumulator 66 is built into the dialysate transport system 6 to dissolve dialysate solution when the pump 42 is compressed and to supply the solution to the system again when the pump 42 is released. The accumulator 66 serves to compensate for the volume change in the dialysate transport system, which results from the operation of the pump 42. (This is necessary because the dialysate transport system 6 according to FIG which the dialysate source and the dialysate sink are lowered from each other. In such a case no accumulator would be needed increases, the solution from the accumulator 66 is fed back into the system. The accumulator 66 is a container with a variable volume and could advantageously consist of a flexible dumbbell, the walls of which expand and contract again when dialysis solution is brought into the accumulator and then discharged again from it.

The collector 70 is used to take up excess solution, which results from the fact that chemicals and water from the blood in dialysis element J8 pass into the dialysate solution. the Chemicals and the water that migrate from the blood into the dialysate solution naturally increase the volume of the solution,

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thus creating the need for this extra volume to be recorded in some form. The collector 70 is built into the dialysate transport system to remove excess Absorb and store fluid. The collector 70 is a Container with a variable volume and is advantageously designed as a compressible and disposable cover, similar to a conventional balloon, which is able to expand when the volume of the solution in the Dialysate transport system increases. This container is built into the system by means of a shut-off valve 72, which then, when the pressure in the system exceeds a certain threshold, there is a possibility of fluid in that container can occur, but while this fluid is prevented from flowing back into the transport system. The shut-off valve 72 Could be constructed in the same way as the inlet valve 210 according to FIG Fig. 2, or a spring loaded valve could be used which is constructed similarly to that which is described below with reference to FIG. 5.

The collector 70 is near the volume sensing switch 76 arranged so that when the container of the collector fills with excess solution and relies on a certain Volume expands, the container wall a feeler arm. 80 touches, which actuates the switch 76, which then triggers a signal is to either give an alarm or switch off the motor 84-. This way the volume of the solution in the dialysate transport system 6 monitored in such a way that when the volume exceeds a predetermined value, the Volume sensing switch 76 is operated to trigger an alarm or to turn off the pump motor 84. The collector 70 could then be withdrawn to make up the excess solution emptied, and it could then be reinserted into the dialysate transport system to continue using the

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artificial kidney to be operated. As a volume sensing switch 76 could serve any conventional electrical switch having a pair of contacts which are closed when the Eühlerarm 80 has been moved a certain distance, so that thereby a suitable signal is triggered.

One embodiment of a suitable vacuum regulator 74- according to FIG Fig. 1 is in the i'ig. 3 shown. The controller has a Container 302 through which the dialysate solution from the Cleaning container 46 is fed to the dialysis element 38 (Fig. 1). An element 310, which has a threaded hole, in arranged at one end of the container 302 and is used for Receiving a screw 306 provided with a complementary thread. At the end of the screw is a helical spring 314 attached, which has a plug or ball 318 on its has free end. As from the 3? Ig. 3 can be seen when the screw 306 is screwed into the element 310 moves the ball 318 closer to the opening 322 which dialysate solution is consumed. When the screw is unscrewed from element 310, ball 318 becomes moved further away from opening 322. The ball 318 is used for partially shutting off the flow of the JE'luids through the opening 322, thereby reducing the flow rate and the pressure of such a flow to control If the flow is to be reduced, of course, the ball 318 is brought closer to the opening 322, and if the flow is to be increased, the ball is moved further away from the opening 322. There could be numerous other arrangements for controlling the flow of dialysate solution can be used.

As already stated above, the pumps 14 and 14 are driven by a motor-driven Konipressionselement 16 actuated. The pumps can be arranged such that the compression element 16 alternately compresses a pump housing

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and releases it again and then compresses the other pump housing and releases it again to produce a pulsating push-pull Effect in the blood transport system 2 and in the dialysate transport system 6 evoke. The spatial arrangement of the rags 14 and 52 as well as the compression element 16 for such Configuration, is best from FIG. 4 and FIG. 5 can be seen, which are explained below.

According to FIG. 4, the two pumps 14 and 52 are arranged next to one another, the compression element 16 between the pumps lies. A retainer plate 410 having an interior surface that conforms to the exterior surface of the housing of the pump 14, is arranged on one side so that it is in contact with the pump 14. A similar retainer plate 414 is on arranged on one side of the pump 52. By the touch area the holding plate is each designed so that it is adapted to the corresponding pump housings, prevent the holding plates a deformation of the housing surface which is in contact with the plates when the housing is through the compression element 16 are compressed. By forming the retainer plate surface to coincide with the housing wall surface match, they also help to increase the pumping and suction pressures associated with the pumps are achievable (compared to, for example, a simple compression of the pump housing between two flat plates). Since the pump pressure generated by the pumps as well as the corresponding suction effect with the shape of the used If the retaining plates change, the pump pressure and the suction effect can in part by an appropriate selection of the shape of the Retaining plates are controlled. Such a control can also be achieved through a corresponding selection of the housing wall thickness and the Material elasticity take place, with a greater thickness and a increased resilience generally lead to increased suction and increased pump pressure while using a smaller thickness and elasticity, a lower pump pressure and a lower suction effect can be achieved. the

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Combination of the retaining plate shape and the housing wall thickness and the housing elasticity thus form a simple and yet effective method of controlling the pump pressure and suction produced by the artificial kidney system to be developed.

From Figs. 4-B and 4C it can be seen how the pump 52 by the compression element 16 is compressed or compressed and the pump 14- through the compression element 16 in is compressed or compressed in a corresponding manner. The compression element 16 is represented by the in FIG. 5 th motor 84 actuated. Caused via a conventional connection this motor that the compression element 16 alternately first compresses a pump housing and then the other, namely in a pendulum-like operation. When the pump housing is arranged as shown, a single compression element used to operate both pumps. This results in a simple, effective and compact pump configuration.

An alternative pump configuration is shown in FIGS. In this configuration, the housings of pumps 14 and 52 are simultaneously compressed and then released again by compression element 17 at the same time. As can be seen from FIGS. 6 and 7, the two pumps 14 and 52 are again arranged together, with the compression element 17 extending upward between the pumps. The compression member 17 has a stem 17b and a horizontal head 17a, which together form the T-shaped. Via a conventional connection, the motor 84 causes the compression element 17 to move between a compression position in which the housings of the pumps 14 and 52 are both compressed by the compression element 17 (FIG. 6B) and a release position in which the housings of the pumps

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are released (Fig. 6A), "moved. Fig. 7 shows a Top view of the pumps, with the pump housing through the Compression element 17 are compressed.

Although the two pump configurations have been illustrated for use in an artificial kidney system shown in FIG. 1, It should be obvious that the pumps also come in a variety could be used by other applications in which fluids are to be pumped.

Fig. 8 shows a full cycle pump, either in a or could be used in both systems, namely either in the blood transport system 2 and in the dialysate transport system 6 or in one of the two systems (whereby the pump is equipped with a double needle cannula). This pump has two housings 802 and 804, which are arranged on either side of the compression element 806. Each case is similar constructed as in the case of the pump according to FIG. 2, each housing namely having an inlet and an outlet as well as an inlet valve and an exhaust valve. The two housings are inserted in parallel into a fluid conduit 808, with the inlets each housing is connected to a line section 808a and the outlets are connected to a line section 808b. That Compression element 806 operates by first compressing and releasing one of the housings and then the other housing is pressed together and released. While one housing is squeezed and the other is released, fluid is from the one housing into the line section 808b is pressed in, and the other housing sucks in fluid from the line section 808a. Thus, at fluid supplied to the conduit section 808b with each stroke or with each half cycle of the compression element 806, so that a Kind of full cycle pumping action is achieved. There is a so-called Half-cycle pumping action, which then arise

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would if only one housing were inserted into line 808. Then it would only take place every second stroke or every second
Half-cycle movement of the compression element 806 directs fluid from the housing into the conduit.

- patent claims -

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Claims (1)

Claims f LyHämodialysseeinrichtung, thereby geke η η ζ eichnet ^ that a dialysis element (38) is provided through which a patient's blood and a dialysate solution can circulate in order to transfer harmful substances and water from the blood into the solution To enable a blood transport system (2) to continue to be present, to supply ura blood from your patient to the dialysis element (38) and to return it from the dialysis element (38) to the patient Blood transport system (2) is built in that the first pump (14) has a flexible housing (202) which, when it is alternately compressed and released, causes blood to flow in the blood transport system (2), that a dialysate source and a dialysate sink are also present, that a dialysate transport system (6) is also provided in order to transfer dialysate solution from the dialysate source to the dialysis element (38) and from the dialyz To promote seelecient (38) to the dialysate sink that a second pump (52) is also present, which is built into the dialysate transport system (6), that the second pump (52) has a flexible housing, which when it is alternately compressed and is released, causes dialysate solution to flow in the dialysis transport system (6) and that there is a pump actuator which serves to compress and release the housings (such as 202) of the first and second pumps (14, 52), so that a pumping action is produced in the blood transport system (2) and in the dialysate transport system (6). 2. Hemodialysis device according to claim. 1, characterized in that that the dialysate source and the dialysate sink a container (46) have, which is inserted into the dialysate transport system (6) 509840/0816 and through which the dialysate solution flows, and that a filter device (48) is provided which is arranged in the container (46) and serves to collect waste materials remove from the dialysate solution if the solution flows through the container (46). 3. hemodialysis device according to claim 1 or 2, characterized characterized in that the dialysate transport system (6) has an accumulator (66) which has a dumbbell and a device has to carry the dumbbell with the dialysate transport system (6) to couple a passage of dialysate solution from the dialysate transport system (6) into the jacket and from the To enable dumbbell to the dialysate transport system (6). 4. Hemodialysis device according to claim 3, characterized in that that the dumbbell is flexible. 5- Hemodialysis device according to one of the preceding claims, characterized in that the dialysate transport system (6) has a collector (70) which enters the dialysate transport system (6) is inserted to absorb excess dialysate solution. 6. Hemodialysis device according to claim 5 »characterized in that that the collector (70) has a compressible shell. 7. Hemodialysis device according to claim 6, characterized in that that the collector (70) has a shut-off valve which serves to block the flow of solution from the dialysate transport system (6) to enable the sheath and the flow of solution from the sheath into the dialysate transport system (6) prevent. 509 8 40/0816 8. hemodialysis device according to claim 6 or 7, characterized characterized in that the collector (70) has a sensor arm (80) which is arranged to come into engagement with the sheath when the sheath is on a predetermined one Volume fills, and that a switch device is provided to generate a signal when the envelope comes into engagement with the sensor arm (80). 9. Hemodialysis device according to one of claims ^ to; 8th, characterized in that der.'Akkumulstor (66) and eggs Collector (70) in that section of the dialysate transport systems (6) are inserted, rather the dialysate solution from the container (46) leads to the dialysis element (38), and that the second pump (52) in that section of the dialysis? ttransportsystems (6) is inserted which solution of yours Dialysis element (38) leads to the container (46). 10. Hemodialysis device according to one of the preceding claims, characterized in that a "vacuum regulator (74) is coupled to the dialysate transport system (6) that the vacuum regulator (74) has a container (302) which has a Has opening (322) through which dialysate solution flows, and that the vacuum regulator (74) has a closing device (318) which can be arranged in front of the opening (322) at adjustable distances therefrom in such a way that the The flow of the solution through the opening (322) can be controlled. 11. Hemodialysis device according to claim 10, characterized in that the vacuum regulator (74) is arranged in that section of the dialysate transport system (6) which leads solution from the dialysate source to the dialysis element (38). S09840 / 0816 12. Hemodialysis device according to one of the preceding Claims, characterized in that the flexible. Housing (202) of each pump (14, 52) has an inlet and an outlet has, via which the housing is connected to the corresponding transport system (2, 6) in each case, that there is also an inlet valve (210) through which fluid can flow into the housing, and that a Exhaust valve (206) is present through which fluid can flow out of the housing (202). 13 · Hemodialysis device according to claim 12, characterized in that ", that the housing (202) are made of rubber and have a wall thickness of about 3 now (1/8 of an inch) exhibit. 14. Hemodialysis device according to claim 12 or 13, characterized characterized in that each housing (202) is elongated with the inlet valve (210) on one End of the housing (202) and the outlet valve (206) are arranged at the other end of the housing. . 15. Hemodialysis device according to one of claims 12 to 14, characterized in that the housings (202) are arranged next to one another and that the pump actuation device has a compression element (16) which is arranged between the housings and alternately in a first position in which the housing of the first pump (14) is compressed, and is movable into a specific position in which the housing of the second pump (5> 2) is compressed, whereby the first and second pumps (14, 52) are operated alternately will. S09840 / 0816 mm, -Φ £ \ - 16. Hemodialysis facility after. Claim 15, characterized in that that a first holding plate (410) is provided, one surface of which is shaped so that it is one side of the housing of the first pump (14-) is adapted that the first holding plate (4-10) is arranged such that the one surface is in contact with one side of the housing in order to avoid deformation of one side, when the housing is compressed, and that a second retaining plate (4-14) is present, one side of which is such is shaped so that it is adapted to the one.side of the housing of the second pump (52) that the second holding plate (4-14) is arranged so that one side thereof is in contact with one side of the housing of the second pump (52) stands to prevent deformation when the case the second pump (52) is compressed. 17 · hemodialysis device according to one of claims 12 to 16, characterized in that the housings are arranged side by side and that the rag actuating device is a Compression element (17), which between a first position in which both housings by the compression element (17) are compressed, and a second position is movable in which the housing by the Compression element (17) are released. 18. System of an artificial heather, characterized in that that a dialysis element (JS) is provided through which a patient's blood and a dialysate solution circulate, about the passage of waste matter and water from the blood to enable in the solution that a blood transport system (2) is still present to carry blood from the patient to the Dialysis element (38) and from the dialysis element (38) to the patient that continues to have a first pump (14 ·) is provided, which is built into the blood transport system (2), in order to transport the blood from the patient to the dialysis element (38) and from the dialysis element (38) to the patient 509840/0816 pump back that continues to be a source of dialysate and -senke are present that a dialysate transport system (6) is also provided to deliver dialysate solution from the dialysate source to the dialysis element (38) and from the dialysis element (38) to the dialysate sink to transport that Furthermore, a wide pump (52) is built into that section of the dialysate transport system (6), the Pump dialysate solution from the aera dialysis element (38) to the Dialysate sink promotes to bring the solution to that of the dialysis element (33) to the dialysate sink and flows from the dialysate source to the dialysis element (38) so that the second pump (52) has a flexible housing, which in the compressed state presses the solution out of the housing in the direction of the dialysate sink and which in the released state, the solution from the dialysis element (38) is sucked into the housing so that a pump actuation continues means are provided to compress and release the housings of the first and second pumps (14-, 52), thus in the blood transport system (2) and in the dialysate transport system (6) a pumping effect is produced, that still an accumulator (6 &) in the dialysate transport system (6) is built in to receive dialysate solution when the second pump (52) is squeezed, and around Deliver dialysate solution when the second pump (52) is released is, and that a collector (70) in the dialysate transport system (6) is installed to absorb excess dialysate solution from the dialysate transport system (6). S09840 / 081G · Device according to claim 18, characterized in that a shut-off valve is present in the collector (70) to to allow the flow of the solution from the dialysate transport system (6) to the collector (70) and to allow the flow of the To prevent dissolution from the collector (70) to the dialysate transport system (6). 20. Device according to one of claims 18 or 19? through this characterized in that the collector (70) is a compressible Enclosure comprises that further means is present to alternate between the housing of the second Squeeze pump (ü? 2) and continue to release that a feeler arm is arranged to come into engagement with the sheath when the sheath extends over a fills predetermined volume out, and that further a device (76) is provided which on the engagement the sleeve with the feeler arm (80) is responsive to the pump actuator switch off. 21. Device according to one of claims 18 to 20, characterized in that the accumulator (66) and the collector (70) in that section of the dialysate transport system (6) are used, which solution leads from the dialysate source to the dialysis element (58). 22. Device according to one of claims 18 to 21, characterized in that a vacuum regulator (76) in the dialysate ran sport system (6) between the dialysis element (38) and the accumulator (66) is arranged and that a collector (70) for regulating the flow of the solution into the Dialysis element (38) is present. £ 09840/0 8-16 23. Device according to claim 22, characterized in that the vacuum regulator (76) comprises a container (302) which has an opening (322) through which dialysate solution flows, and that a closing device (318) is also present which has a diameter which is larger than the diameter of the opening (322) and in front of this opening (322) at adjustable distances therefrom to control the flow of solution through the opening (322). 24. Device according to one of the preceding claims, characterized in that to form a pulsation pump first and second pumps (W-, 52) are present, each having a flexible housing having an inlet and has an outlet, there is also an inlet valve (210) disposed in the inlet to allow fluid through the inlet into the housing, there being further an outlet valve (206) to allow fluid to flow out of the housing through the outlet, that the housings are arranged opposite one another and that one Pump actuator is provided which a Compression element (16) which can be actuated in such a way that the housing of the first pump (14) is compressed and is released again and the housing of the second pump (52) is compressed and released again, so that this creates a pulsating pumping effect. 25 · Device according to claim 24, characterized in that the housings are made of rubber and that the Housing a wall thickness of about 3 mm (1/8 of an inch) exhibit. 509840/0816 26. Device according to claim 24 or 25? characterized, that a compression element (16) between the housings the first and the second pump (14, 52) is arranged and so "can be actuated that it alternately the housing the first pump (14-) squeezes and releases and the housing of the second pump (52) squeezes and releases, whereby a push-pull pulsating pump effect is caused. 27. Device according to claim 25 or 26, characterized in that a first holding plate (410) is provided, one surface of which is shaped such that it is adapted to one side of the housing of the first pump (14), that the holding plate (410) is arranged such that a surface with _# one side of the housing is in contact, in order to prevent defoliation one side, when the case is compressed such that further comprises a second holding plate (414) is provided, one face of which shaped such is that it mates with one side of the housing of the second pump (52), and that the second holding plate (414) is arranged such that a surface of the second holding plate (414) with one side of the housing of the second pump (52) in Contact is to avoid deformation of the same when the housing is compressed. 28. Device according to one of claims 24 to 27, characterized in that each housing is elongated and that the inlet valve (210) on one side of the housing and the outlet valve (206) on the other ' Side of the housing are arranged. 29. Device according to one of claims 24 to 28, characterized in that the compression element (17) between, a first position in which the housing of the first 509840/0816 and the second pump (14-, 52) are compressed by the compression element (17), and a second Position in which the housing is released by the compression element (17) "is movable. 30. Device according to one of the preceding claims, characterized in that to form a Vo11zykluspumpe first and second flexible housings (802, 804-) are provided each having an inlet and an inlet valve (210) arranged in the inlet to allow fluid to flow into the housing, and that an outlet and an outlet valve (206) are provided to allow fluid to continue to flow out of the housing a device is provided which connects the inlets of the housings to one side (808a) of a fluid-carrying line connects that there is also a device which connects the outlets of the housings to the other side (808b) the fluid-carrying line connects and that a device is provided which serves to alternately a Squeeze and release the housing and then the other housing, thereby creating a full cycle pumping action is caused. 31. Device according to claim 30 »characterized in that the housing (802, 804 ·) are arranged side by side that the for. Squeeze and release serving Device comprises a compression element (806) which is arranged between the housings (802, 804-) and alternately in a first position in which the first housing (802) is compressed, and in a second Position in which the second housing (804-) is compressed is movable. 5Q3840 / 0816