CN219355089U

CN219355089U - Interventional type heart and kidney joint auxiliary system

Info

Publication number: CN219355089U
Application number: CN202221995738.2U
Authority: CN
Inventors: 解启莲; 刘欢; 冯启涛
Original assignee: Anhui Tongling Bionic Technology Co Ltd
Current assignee: Anhui Tongling Bionic Technology Co Ltd
Priority date: 2022-07-19
Filing date: 2022-07-28
Publication date: 2023-07-18
Anticipated expiration: 2032-07-28
Also published as: CN219355090U; CN219148993U; CN115120867A; DE202022105810U1; CN115154889A

Abstract

The utility model belongs to the technical field of medical appliances, and particularly relates to an interventional type heart and kidney combined auxiliary system. The utility model comprises a first mechanical circulatory support device located in the ventricle of a patient and a second mechanical circulatory support device located in the descending aorta of the patient, both of which are connected to the outside of the human body by a catheter. The utility model ensures the pumping initial speed of blood by the first mechanical circulation supporting device, and realizes the acceleration of secondary blood flow by the second mechanical circulation supporting device positioned in the descending aorta, thereby effectively unloading the ventricular pressure and ensuring the blood perfusion of the terminal organ.

Description

Interventional type heart and kidney joint auxiliary system

The application claims the priority of an interventional heart and kidney combined auxiliary system with the application number of 202210844673.X in the 19 th year of 2022, and the original acceptance organization is China.

Technical Field

The utility model belongs to the technical field of medical appliances, and particularly relates to an interventional type heart and kidney combined auxiliary system.

Background

The blood flow of the whole body of the human body is completed by heart pumping. The occurrence of cardiovascular diseases can lead to heart failure, which is manifested by dysfunction of the systolic function and/or the diastolic function of the heart, and the venous return blood volume can not be fully discharged out of the heart, so that ventricular blood stasis is caused, and the arterial intervention type heart and kidney combined auxiliary system has insufficient blood perfusion, so that the heart blood circulation is impaired, and life hazards such as organ failure, shock and the like are caused. Currently, mechanical circulatory support devices, or blood pumps, are available that assist or replace cardiac pumping to provide life support based on hemodynamic forces for cardiogenic shock and acute heart failure. In operation of the blood pump, blood flows from the left ventricle through the aorta to the systemic organs. However, due to the special shape of the aortic arch, the blood needs to overcome the pressure difference between the left ventricle and the aortic arch to complete the blood flow discharging movement, if the pumping power of the blood pump is insufficient to support the blood to pass through the aortic arch, the phenomenon of blood reflux can occur, the ventricular pressure cannot be effectively unloaded, and the blood perfusion of the terminal organ is insufficient.

Disclosure of Invention

The utility model aims to overcome the defects of the prior art, and provides an interventional type heart and kidney combined auxiliary system which ensures the pumping initial speed of blood by means of a first mechanical circulation supporting device and realizes the acceleration of secondary blood flow by means of a second mechanical circulation supporting device positioned in a descending aorta, so that the ventricular pressure is effectively unloaded, and the blood perfusion of a terminal organ is ensured.

In order to achieve the above purpose, the present utility model adopts the following technical scheme:

an interventional heart and kidney joint auxiliary system, which is characterized in that: comprising a first mechanical circulatory support device located in a ventricle of the patient and a second mechanical circulatory support device located in a descending aorta of the patient, the first and second mechanical circulatory support devices being connected to the outside of the human body via a first and second conduit, respectively.

Preferably, the second mechanical circulatory support device is a second blood pump having a second conduit, a second impeller, a second blood flow outlet, a second cannula and a second blood flow inlet, the second impeller acting in the lumen of the second cannula between the second blood flow inlet and the second blood flow outlet.

Preferably, the second mechanical circulation supporting device is provided with a supporting body so as to position and support the second mechanical circulation supporting device at the vessel wall of the descending aorta; the support body is made of a deformable memory alloy material and has an expansion structure in an expanded state and a contraction structure in a stressed state.

Preferably, the support body comprises a strut fixed on the outer wall of the second sleeve, the strut extends from the proximal end to the distal end, the radial distance between the strut and the outer wall of the second sleeve gradually increases along the extending direction, and more than three groups of struts are sequentially arranged around the axis of the second sleeve, so that claw-shaped support claws are formed; or the supporting body is a net-shaped pipe body or net-shaped cover body which is fixed on the outer wall of the second sleeve and coaxially extends from the proximal end to the distal end, and the distal end pipe diameter of the net-shaped pipe body or net-shaped cover body is large, and the proximal end pipe diameter is small, so that the horn-shaped or mushroom-shaped supporting claw is formed; or the supporting body is a cage-shaped structure fixed on the outer wall of the second sleeve, and one end part of the cage-shaped structure facing to the proximal end is in a spherical shape which is convenient for sheathing the sheath tube; or the supporting body is composed of more than two curve columns, and each curve column is intersected with each other orderly or unordered, so that the eggbeater-shaped or steel wire spherical supporting body is formed.

Preferably, when the supporting claw is claw-shaped, the extending end of the supporting pillar is provided with a contact pad for improving the anchoring effect relative to the vascular wall, and the middle section of the supporting pillar is provided with a bent bow-shaped outwards bent knee; when the support body is horn-shaped or mushroom-shaped, the mesh tube body or the mesh cover body can be formed by a braiding mode.

Preferably, the support body is arranged with two or more groups along the axial direction of the second mechanical circulation support device.

Preferably, the first mechanical circulation support device is also a first blood pump having a first conduit, a first motor, a first impeller, a first blood flow outlet, a first cannula, and a first blood flow inlet; the proximal ends of the first mechanical circulation supporting device and the second mechanical circulation supporting device are connected to a double-cavity connecting pipe, and two independent cavities are formed in the double-cavity connecting pipe and are used for accommodating a first catheter and a second catheter respectively.

Preferably, a reserved groove or a reserved hole for the second conduit to pass through is formed in the first mechanical circulation supporting device; the preformed groove and the preformed hole are arranged in a penetrating manner along the length direction of the first mechanical circulation supporting device.

Preferably, the first mechanical circulation supporting device and the second mechanical circulation supporting device are respectively provided with a pressure sensor; the pressure sensor is an optical fiber pressure sensor; the first mechanical cycle support device is in communication with a first controller configured to operate the first mechanical cycle support device at a first rate; the second mechanical loop support device is in communication with a second controller configured to operate the second mechanical loop support device at a second rate.

Preferably, the second rate is 30% to 80%, preferably 40% to 60%, more preferably 50% of the first rate.

The utility model has the beneficial effects that:

1) The two groups of mechanical circulation supporting devices form a series pump group, and under the axial flow pumping action, the blood flow can easily overcome the pressure difference between the left ventricle and the aorta, thereby completing the blood flow discharging movement. Specifically, the utility model uses the combination of the double pumps, can weaken the requirement of the first mechanical circulation support device on the blood pumping capacity, reduce the rotation speed of the device in the ventricle, is beneficial to reducing hemolysis, relieving the heating of a motor and the non-physiological blood stress injury, and improves the blood compatibility of the device. Meanwhile, the pumping initial speed of blood is guaranteed by the first mechanical circulation supporting device, and the secondary blood flow acceleration is realized by the second mechanical circulation supporting device positioned in the descending aorta, so that the ventricular load is reduced, the blood circulation of the descending aorta is improved, the ventricular pressure is effectively unloaded, the blood perfusion quantity of terminal organs such as kidneys and the like is increased, and the heart and kidney functions are improved.

2) Furthermore, on the basis of the structure of the serial blood pump, the utility model also adds a support body. The support body has an anchoring function capable of positioning and supporting the second mechanical circulation supporting device in the descending aorta. The shape of the support body can be horn-shaped, mushroom-shaped, cage-shaped, egg beater-shaped, claw-shaped or the like, and the purpose is to ensure the anchoring function and simultaneously ensure that the blood circulation and the device insertion and extraction are convenient.

3) When in design, the supporting bodies can be arranged in a plurality of groups along the axial direction of the corresponding pump so as to increase the stability during anchoring.

4) In the case of the claw-shaped supporting body with the supporting column, the supporting column is not only provided with a contact pad at the top end, so that the anchoring effect is improved, and the climbing stability is improved; meanwhile, the support column is also provided with an arched zigzag structure, namely a knee, so that when the support column is stored, a gap between the support body and the sheath tube can be ensured, and friction is reduced. Of course, the knee's zigzag structure may also be applied in other supports accordingly, achieving its same purpose.

5) The protection sheath for femoral artery and the guiding sheath for forming corresponding catheter can be formed by means of the double-cavity connecting pipe, so that the utility model can be rapidly intervened in a shorter time, the blood circulation of patients suffering from acute heart failure such as sudden myocardial infarction can be rapidly established, valuable life-saving time is won, and the safety of operation and corresponding blood pump working is synchronously improved. The utility model can rapidly promote the blood flow rate of the whole aorta by utilizing the unique serial blood double acceleration design once started, can always maintain high-efficiency blood circulation, can effectively ensure the sufficiency of blood perfusion to human organs, and has reliable and stable work.

6) In the utility model, on the basis of the structure, a corresponding pressure sensor and a controller are additionally arranged. The pressure sensor can respectively detect the pressure of the blood flow of the ventricle and the aortic blood, so that the monitoring effectiveness of the physiological information is improved; in use, an optical fiber pressure sensor is preferably used. Each controller plays a role in automatically controlling the rotation speed of the corresponding pump body, and can even combine with a pressure sensor if necessary to realize the automatic and continuous operation functions of flow and intellectualization so as to further improve the real-time performance, accuracy and reliability of the device.

Drawings

FIG. 1 is a schematic view of an assembled state of the present utility model;

FIGS. 2 and 3 are block diagrams of two embodiments of the second mechanical circulatory support device in an operating mode;

fig. 4, 5, 6, 7, 8, 9 and 10 are schematic structural views of seven embodiments of the support body.

The actual correspondence between each label and the component name of the utility model is as follows:

10-first mechanical circulation support device 11-first catheter 12-first blood outflow opening

13-first sleeve 14-first blood inflow opening 15-pigtail

20-second mechanical circulation support device 21-second catheter 22-second blood outflow opening

23-second cannula 24-second blood flow inlet

25-support 25 a-contact pad 25 b-knee 25 c-curved strut

30-double-cavity connecting pipe

Detailed Description

For ease of understanding, the specific structure and operation of the present utility model will be further described herein with reference to FIGS. 1-10:

for ease of understanding, the "proximal" is defined herein first as the end of the interventional medical device closer to the operator, and the "distal" is defined as the end of the interventional medical device farther from the operator.

The utility model aims to reduce left ventricular pump blood pressure, reduce hemolysis damage and increase kidney perfusion. In view of this, as shown in fig. 1, on the basis of the conventional left ventricle auxiliary blood pump, the present utility model adds a set of mechanical circulation support devices at the descending aorta adjacent to the ventricle, so that the pump set formed by connecting the two pump bodies in series is utilized to realize the dual acceleration function of blood, so as to ensure that the blood can overcome the pressure difference between the left ventricle and the descending aorta to complete the blood flow discharging movement, and form a higher arterial pressure to increase the blood flow flowing to the kidney, thereby enhancing the kidney function and increasing the urine discharging amount.

Referring to fig. 1, an interventional type heart and kidney joint auxiliary system includes a first mechanical circulation support device 10 located in a ventricle of a patient and a second mechanical circulation support device 20 located in a descending aorta of the patient, the first mechanical circulation support device 10 and the second mechanical circulation support device 20 being connected to the outside of the human body through a first catheter 11 and a second catheter 21, respectively. The first mechanical circulatory support device 10 and the second mechanical circulatory support device 20 are operated and the cardiac output of the patient is maintained or enhanced.

The interference of the two pipes of the first mechanical circulation supporting device 10 and the second mechanical circulation supporting device 20 is considered when the first mechanical circulation supporting device 10 and the second mechanical circulation supporting device 20 are connected in series. Therefore, the present utility model is further provided with the dual-lumen connecting tube 30, thereby ensuring the motion avoidance characteristics of the first and second catheters 11 and 21 with respect to each other by using two sets of lumen passages in the dual-lumen connecting tube 30 independent of each other, as shown with reference to fig. 1.

The first mechanical circulation support device 10 is a first blood pump having a first catheter 11, a first motor, a first impeller, a first blood outflow port 12, a first cannula 13, a first blood inflow port 14 and a pig tail 15, wherein the pig tail and the first blood inflow port 14 are placed in a left ventricle, the first cannula 13 spans an aortic valve, the first impeller and the first blood outflow port 12 forming the first motor are positioned in an ascending aorta, the first impeller is connected with a rotating shaft in the hollow cup motor, the hollow cup motor is operated to drive the first impeller to rotate, blood in the left ventricle is sucked, and the blood is finally discharged into the aorta through the first blood inflow port 14, the first cannula 13 and the first blood outflow port 12, so that ventricular load is unloaded, and aortic blood flow pressure is increased. The first blood pump may be inserted into the human body via, for example, the femoral artery, the first catheter 11 extending from inside the body to outside the body to be connected to the first controller, and a cable, a corresponding sensor, an irrigation line, etc. being provided in the first catheter 11, so that the first blood pump can communicate with the first controller. The first controller is configured to operate the first blood pump at a first rate at which the first blood pump may provide an operational flow rate of 1.5 to 6L/min, for example, the first blood pump is operated at a flow rate of 2.5L/min or 5L/min. When the first blood pump operates at a higher flow rate, the pressure of the ventricle can be effectively unloaded, and accordingly, the non-physiological stress damage of the instrument to blood is larger; when the first blood pump is operated at a lower flow rate, the unloading effect of the ventricular pressure is weaker and, correspondingly, the blood compatibility of the device is better. For example, a sensor protection housing may be provided on the first blood inflow opening 14 for protecting the sensor probe from the impact of the blood flow. The sensor is preferably a pressure sensor, more preferably an optical fiber pressure sensor, and is used for detecting the ventricular blood flow pressure, so that the physiological information monitoring effectiveness is improved.

The second mechanical circulation supporting device 20 is a second blood pump which is provided with a second conduit 21, a hollow cup motor forming a second motor, a second impeller, a second blood outflow opening 22, a second sleeve 23, a second blood inflow opening 24 and a supporting body 25, the second conduit 21 extends from inside to outside and is connected with a second controller, a second blood pump main body is positioned in a descending aorta, the second impeller is connected with a rotating shaft in the hollow cup motor, the hollow cup motor can drive the second impeller to rotate when working, blood discharged from a left ventricle to the aorta is sucked, and the perfusion of the blood of the aorta to organs such as kidneys is increased by utilizing the principle of secondary pressurization, so that the ventricular pressure can be further unloaded, and the kidney perfusion amount is increased. The second blood pump may be inserted into the human body via, for example, the femoral artery, with cables, corresponding sensors, and irrigation tubing, etc. provided within the second catheter 21, so that the second blood pump can communicate with the second controller. The second controller is configured to operate the second blood pump at a second rate at which the second blood pump may provide an operational flow rate of 1.5 to 6L/min, for example, the second blood pump is operated at a flow rate of 2.0L/min, 2.5L/min, 4.0L/min, or 5L/min. A sensor protection housing may be provided on the second blood inflow opening 24, for example, for protecting the sensor probe from impact damage by blood flow. The sensor is also preferably a pressure sensor, more preferably an optical fiber pressure sensor, and is used for detecting the blood flow pressure at the descending aorta, so that the physiological information monitoring effectiveness is improved.

Preferably, the second rate is 30% to 80%, preferably 40% to 60%, more preferably 50% of the first rate. In fact, the first mechanical circulatory support device 10 pumps the blood in the ventricle into the ascending aorta, wherein a portion of the blood is used to supply brain tissue and another portion of the blood is directed by the second mechanical circulatory support device 20 to each end organ, adapting to the physiological characteristics of the human body.

The supporting body 25 is used for positioning and supporting the second blood pump on the wall of the descending aorta blood vessel, so as to ensure the running stability of the second blood pump. The support body 25 is made of a deformable memory alloy material and has an expanded configuration in an expanded state and a contracted configuration in a stressed state. The second blood flow outlet 22 is bordered by a proximal end, which is the end of the interventional medical device closer to the operator, and a distal end, which is the end of the interventional medical device further from the operator. The support 25 may be provided at the distal and/or proximal end of the second cannula 24, the end through-hole of the distal end of the second cannula 24 constituting the second blood inflow port 24. When disposed distally, the support 25 may be disposed at an end wall of the second cannula 24 and integrally formed with the second cannula 24, or may be disposed at a wall of the second cannula 24 and integrally formed with the second cannula 24. The supporting bodies 25 may be disposed at different positions of the second sleeve 24 by one or two or more groups, may be disposed at intervals in the axial direction of the second sleeve 24, or the like. The support 25 has various modifications, including horn-shaped, mushroom-shaped, cage-shaped, egg whisk-shaped, claw-shaped structures, etc., and has a common feature that the support is fixed at the pipe wall of the second sleeve 24, for example, a guide surface structure such as a conical surface or a spherical surface with a large distal pipe diameter and a small proximal pipe diameter is formed at the end wall, so as to facilitate the insertion and extraction of the device. Referring to fig. 2-3, the supporting body 25 is three-jaw, but two-jaw or four-jaw arc shape can be adopted, provided that the positioning stability is ensured. The modified structure of fig. 4 can also be extended on the basis of the structure of fig. 2-3. In other words, taking a three-jaw support as an example, in fig. 4, three struts constituting three jaws may connect adjacent two struts with each other through an elastic member such as a curved strut 25 a. When the stent is placed into the descending aorta, since the sheath is sleeved on the outer wall of the second sleeve 24 at an early stage, each strut is radially compressed and folded, and at this time, the sheath can forcefully bend the curve compression rod 25a to be in a force storage state. When the descending aorta is sent and the sheath tube is removed, the curve compression bar 25a releases force, so that the three struts can be driven to be reset and opened to the state shown in fig. 4, and the purpose of climbing and positioning the top supporting blood vessel wall is achieved. Similarly, the curved compression bar 25a can be replaced by other elastic force storage structures, and only the force storage and release effects are needed. In fig. 4, the positions of the knee portion 25b and the contact pad 25b can be seen, and the description thereof will be omitted.

Further, referring to fig. 6, the supporting body 25 is in a shape of an eggbeater or a steel wire-like sphere, that is, is formed by a plurality of curve columns in a staggered manner, so that the purpose of climbing and positioning the vessel wall is achieved while the hollowing is ensured. Similarly, if the supporting body 25 is umbrella-shaped or mushroom-shaped, the function of blood circulation and climbing can be achieved correspondingly. Further, fig. 7 discloses one of the woven cage-like structures, in which case the entire cage-like structure may be made entirely of a memory alloy to achieve its action function; the expansibility of the memory alloy in the blood caused by heating can restore the cage-shaped structure to an initial state, and the diameter of the cage-shaped structure is increased at the moment, so that the climbing effect of the descending aorta vessel can be achieved; the woven cage may span the entire second blood pump, i.e., both ends may be connected to the proximal and distal ends simultaneously, although both ends may be located at the proximal end or mounted at the distal end. Another cage-like structure shown in fig. 8 is integrally formed of a memory alloy. Fig. 9 and 10 show two further variants of the horn-shaped support body 15; at this time, the whole supporting body 25 is still horn-shaped, and the difference is that the supporting body is provided with more woven or hollowed holes so as to ensure the unblocked effect of blood.

In actual mounting of the support body 25, the support body 25 may be disposed individually and correspondingly at the proximal end or distal end of the second cannula 24, or even individually at the second blood inflow port 24, or may be disposed in plural. Even the plurality of sets of supporting bodies 25 may take different forms, without being constrained to have to take the same form.

It will be understood by those skilled in the art that the present utility model is not limited to the details of the foregoing exemplary embodiments, but includes other specific forms of the same or similar structures that may be embodied without departing from the spirit or essential characteristics thereof. The present embodiments are, therefore, to be considered in all respects as illustrative and not restrictive, the scope of the utility model being indicated by the appended claims rather than by the foregoing description, and all changes which come within the meaning and range of equivalency of the claims are therefore intended to be embraced therein. Any reference sign in a claim should not be construed as limiting the claim concerned.

Furthermore, it should be understood that although the present disclosure describes embodiments, not every embodiment is provided with a separate embodiment, and that this description is provided for clarity only, and that the disclosure is not limited to the embodiments described in detail below, and that the embodiments described in the examples may be combined as appropriate to form other embodiments that will be apparent to those skilled in the art.

The technology, shape, and construction parts of the present utility model, which are not described in detail, are known in the art.

Claims

1. An interventional heart and kidney joint auxiliary system, which is characterized in that: comprising a first mechanical circulatory support device (10) located in the ventricle of the patient and a second mechanical circulatory support device (20) located in the descending aorta of the patient, the first mechanical circulatory support device (10) and the second mechanical circulatory support device (20) being connected to the outside of the human body by a first catheter (11) and a second catheter (21), respectively.

2. An interventional heart and kidney joint assistance system according to claim 1, wherein: the second mechanical circulation support device (20) is a second blood pump having a second conduit (21), a second impeller, a second blood outflow opening (22), a second cannula (23) and a second blood inflow opening (24), the second impeller acting in the lumen of the second cannula (23) between the second blood inflow opening (24) and the second blood outflow opening (22).

3. An interventional heart and kidney joint assistance system according to claim 1 or 2, wherein: the second mechanical circulation supporting device (20) is provided with a supporting body (25) so as to position and support the second mechanical circulation supporting device (20) at the vascular wall of the descending aorta; the support body (25) is made of a deformable memory alloy material and has an expanded configuration in an expanded state and a contracted configuration in a stressed state.

4. An interventional heart and kidney joint assistance system according to claim 3, wherein: the supporting body (25) comprises a strut fixed on the outer wall of the second sleeve (23), the strut extends from the proximal end to the distal end, the radial distance between the strut and the outer wall of the second sleeve (23) gradually increases along the extending direction, and more than three groups of struts are sequentially arranged around the axis of the second sleeve (23), so that the claw-shaped supporting body is formed; or the supporting body (25) is a net-shaped pipe body or net-shaped cover body which is fixed on the outer wall of the second sleeve (23) and extends coaxially from the proximal end to the distal end, the pipe diameter of the distal end of the net-shaped pipe body or net-shaped cover body is large, the pipe diameter of the proximal end of the net-shaped pipe body or net-shaped cover body is small, and therefore the horn-shaped or mushroom-shaped supporting body is formed; or the supporting body (25) is a cage-shaped structure fixed on the outer wall of the second sleeve (23), and one end part of the cage-shaped structure facing to the proximal end is in a spherical shape which is convenient for sheathing the sheath tube; or the supporting body (25) is composed of more than two curve columns, and each curve column is intersected with each other orderly or unordered, so that the eggbeater-shaped or wire-ball-shaped supporting body (25) is formed.

5. An interventional heart and kidney joint assistance system according to claim 4, wherein: when the supporting body is claw-shaped, the extending end of the supporting column is provided with a contact pad (25 a) for improving the anchoring effect relative to the vessel wall, and the middle section of the supporting column is provided with a bent arc-shaped outwards bent knee (25 b); when the support body (25) is horn-shaped or mushroom-shaped, the mesh tube body or the mesh cover body may be formed by knitting.

6. An interventional heart and kidney joint assistance system according to claim 4, wherein: the support body (25) is provided with more than two groups along the axial direction of the second mechanical circulation supporting device (20).

7. An interventional heart and kidney joint assistance system according to claim 2, wherein: the first mechanical circulation support device (10) is likewise a first blood pump having a first conduit (11), a first motor, a first impeller, a first blood outflow opening (12), a first cannula (13) and a first blood inflow opening (14); the proximal ends of the first mechanical circulation supporting device (10) and the second mechanical circulation supporting device (20) are connected to a double-cavity connecting pipe (30), and two independent cavities are formed in the double-cavity connecting pipe (30) and are used for accommodating a first guide pipe (11) and a second guide pipe (21) respectively.

8. An interventional heart and kidney joint assistance system according to claim 7, wherein: a reserved groove or a reserved hole through which the second guide pipe (21) can pass is formed in the first mechanical circulation supporting device (10); the preformed groove and the preformed hole are arranged in a penetrating manner along the length direction of the first mechanical circulation supporting device (10).

9. An interventional heart and kidney joint assistance system according to claim 1 or 2, wherein: the first mechanical circulation supporting device (10) and the second mechanical circulation supporting device (20) are respectively provided with a pressure sensor; the pressure sensor is an optical fiber pressure sensor; the first mechanical cycle support device (10) is in communication with a first controller configured to operate the first mechanical cycle support device (10) at a first rate; the second mechanical cycle support device (20) is in communication with a second controller configured to operate the second mechanical cycle support device (20) at a second rate.

10. An interventional heart and kidney joint assistance system according to claim 9, wherein: the second rate is 30% -80% of the first rate.

11. An interventional heart and kidney joint assistance system according to claim 9, wherein: the second rate is 40-60% of the first rate.

12. An interventional heart and kidney joint assistance system according to claim 9, wherein: the second rate is 50% of the first rate.