WO2018177344A1

WO2018177344A1 - Centrifugal right ventricle assistance device

Info

Publication number: WO2018177344A1
Application number: PCT/CN2018/080996
Authority: WO
Inventors: 袁海云; 庄建; 陈寄梅; 黄焕雷; 周成斌; 刘晓冰
Original assignee: 广东省心血管病研究所
Priority date: 2017-03-31
Filing date: 2018-03-29
Publication date: 2018-10-04
Also published as: CN108653841B; ZA201903474B; CN108653841A

Abstract

Disclosed is a centrifugal right ventricle assistance device, comprising a centrifugal pump and a power transmission component. The centrifugal pump has a driving end, and the power transmission component is connected to the driving end and is used for driving the driving end to rotate along with the movement of respiratory muscles so as to drive the centrifugal pump to realize the pumping in and out of blood. The assistance device can assist patients with right ventricular dysplasia or right cardiac insufficiency, etc., implement the actions of repeatedly pumping blood in and out, and provide the power required for pulmonary circulation, such that the blood in the human body approaches a normal flow. Moreover, by using the power of the patient during respiration to assist the right ventricle, complicated power and control systems can be omitted, and as compared with external power driving, it is easier to ensure the balance of systemic circulation and pulmonary circulation, thereby better assisting the right ventricle and achieving a longer period of time for assistance; and the assistance device is conducive to clinical application and promotion.

Description

Centrifugal right ventricular assist device The present application is based on the Chinese application number of 201710204458.2, the filing date is March 31, 2017, and the priority is claimed. The disclosure of the Chinese application is hereby incorporated herein by reference. . Technical field

The present disclosure relates to the field of medical device technology, and in particular, to a centrifugal right ventricular assist device. Background technique

Many complex congenital heart diseases (complete ventricular septal atresia, severe pulmonary stenosis, and single ventricle, etc.) have impaired right heart system or right ventricular dysfunction, resulting in inability to undergo radical surgery, high operative mortality, or postoperative complications More symptoms, greatly affecting the quality of life and survival of patients. Right ventricular assist can greatly improve the cure rate and mortality of such patients. However, the existing ventricular assist devices are not specifically designed to assist the right ventricle, and often require external power, and the control system is also very complicated, which is not conducive to the clinical application and promotion of such devices.

Since the right ventricle and left ventricle are completely different in structure and function, the pulmonary circulation and systemic circulation pressure are also completely different, so the structure of the right ventricular assist pump should not be the same as that of the left ventricular assist pump. In addition, due to the lack of fineness of the existing control system, the external power is often not well matched with the left ventricular contractile force, which easily leads to imbalance of the body lung circulation. In summary, because the existing devices do not assist the right ventricle well, and the safety assistance time is shorter. Therefore, in order to meet future needs, it is necessary to design an auxiliary pump that specifically assists the right ventricle. Summary of the invention

The present disclosure proposes a centrifugal right ventricular assist device that can assist the right ventricle with self-power in the patient.

According to an aspect of the present disclosure, a centrifugal right ventricular assist device is provided, comprising: a centrifugal pump having a drive end; and

The power transmission component is connected to the driving end for driving the driving end to rotate with the movement of the respiratory muscle to drive the centrifugal pump to realize pumping and pumping of blood.

Further, wherein the power transmission component comprises at least two force applying members respectively located on opposite sides of the driving end, and the first ends of the two side force applying members are respectively connected with the driving end, and the respective second ends are respectively connected with the chest walls of the human body sides Rib joint In addition, the driving end can be driven to rotate when the respiratory muscles drive the ribs.

Further, the two side force applying members perform synchronous reverse linear motion when the respiratory muscles drive the ribs of the chest wall.

Further, wherein the centrifugal pump is provided with an inlet and an outlet, the inlet is disposed on a side opposite to the driving end, the inlet is for communicating with the right atrial appendage or the vena cava, and the outlet is for communicating with the pulmonary artery.

Further, wherein the driving end of the centrifugal pump is provided with a connecting shaft, the power transmitting member further includes a motion converting member for converting the linear motion of the two side force applying members into the rotational motion of the connecting shaft.

Further, the centrifugal right ventricle auxiliary device further includes a one-way mechanism disposed between the motion converting member and the connecting shaft, and the motion converting member can drive the connecting shaft to rotate when the two force applying members are away from each other with respect to the driving end In order to achieve pumping and pumping of blood, and stop working when the force applying members on both sides are close to each other with respect to the driving end.

Further, wherein the centrifugal pump comprises a housing and an impeller disposed in the housing, the housing is provided with an outlet, and the outlet is disposed at a single tangential position of the impeller.

Further, wherein the motion converting member can rotate the connecting shaft in opposite directions when the two side applying members are away from or close to each other with respect to the driving end, so that the centrifugal pump can realize the pumping and pumping of the blood in both states. Out.

Further, wherein the centrifugal pump comprises a housing and an impeller disposed in the housing, the housing is provided with an outlet, and the outlet is disposed at a tangentially merged position of the impeller.

Further, wherein the motion converting member comprises a gear and a rack, the gear is disposed at an outer end of the connecting shaft, and the rack is disposed on the at least a portion of the length of the biasing member adjacent to the gear, and the two racks respectively mesh at the relative positions of the gears .

Further, the two side force applying members are kept relatively parallel during the movement.

Further, the centrifugal right ventricle auxiliary device further includes a wrapping structure for protecting the force applying members on both sides. Further, wherein the centrifugal pump comprises an impeller, and the impeller is a viscous impeller.

Further, wherein the centrifugal pump is used for connection and relatively fixed on the heart structure of the human body.

The centrifugal right ventricle auxiliary device provided by the present disclosure can drive the centrifugal pump to drive the centrifugal pump to drive the centrifugal pump to drive the centrifugal pump to drive the centrifugal pump to drive the centrifugal pump to drive the centrifugal pump. Pumping in and pumping of blood. Such an auxiliary device can assist patients with right ventricular dysplasia or right heart dysfunction, achieve repeated blood pumping and pumping action, provide the required power for the pulmonary circulation, and bring the blood close to normal flow in the human body. DRAWINGS The drawings described herein are provided to provide a further understanding of the present disclosure, and are intended to be a part of the present disclosure. In the drawing:

1 is a schematic front view of one embodiment of a centrifugal right ventricular assist device of the present disclosure; FIG. 2 is a front internal structural view of one embodiment of the centrifugal right ventricular assist device of the present disclosure; a top view of one embodiment of a ventricular assist device;

4 is a schematic view showing a state in which two force applying members are separated from each other to pump blood counterclockwise counterclockwise according to an embodiment of the centrifugal right ventricle auxiliary device of the present disclosure;

Figure 5 is a schematic view showing a state in which the two force applying members are close to each other to stop the auxiliary device from working in an embodiment of the centrifugal right ventricle auxiliary device of the present disclosure;

6 is a schematic structural view of a motion converting member and a one-way mechanism in one embodiment of the centrifugal right ventricular assist device of the present disclosure;

Figure 7 is a schematic view showing the pumping of blood flow in the forward and reverse directions in another embodiment of the centrifugal right ventricle assisting device of the present disclosure;

Figure 8 is a schematic view showing another embodiment of the centrifugal right ventricle assisting device of the present invention in a state in which the two force applying members are separated from each other to pump the blood liquid counterclockwise;

Fig. 9 is a schematic view showing another embodiment of the centrifugal right ventricular assist device of the present invention in a state in which the two force applying members are close to each other to pump the blood clockwise. Description of the reference signs:

1. Housing; 2. Import; 3. Outlet; 4. Impeller; 5. Connecting shaft; 6. Gear; 6, ratchet; 7. Applying force; 8. Pawl. detailed description

The present disclosure is described in detail below. In the following paragraphs, different aspects of the embodiments are defined in more detail. Aspects as defined herein may be combined with any other aspect or aspects unless explicitly indicated that they are not combinable. In particular, any feature that is considered to be preferred or advantageous may be combined with other one or more features that are considered preferred or advantageous.

The terms "first", "second" and the like appearing in the present disclosure are merely for convenience of description, to distinguish different components having the same name, and do not indicate sequential or primary and secondary relationships. In the description of the present disclosure, it is to be understood that the orientations or positional relationships of the terms "inner", "outer", "upper", "lower", "left", and "right" are based on the drawings. Orientation or positional relationship is merely for the convenience of the description of the disclosure, and is not intended to indicate or imply that the device referred to has a particular orientation, is constructed and operated in a particular orientation, and thus is not to be construed as limiting the scope of the disclosure.

With the development of science and technology, there is no technical barrier to convert self-kinetic energy into other energy sources that the human body can continue to use, and the kinetic energy required to drive the right ventricle auxiliary pump is relatively small, and the self-powered right ventricular assist pump will gradually become possible. By referring to related researches on ventricular assisted pumps at home and abroad, the present disclosure utilizes autologous power to drive a right ventricular assist device with the goal of assisting the right ventricle for a long period of time, restoring normal biventricular fluid flow, improving heart disease prevention and control, and lowering prices. And expand the clinical application of right ventricular assist pump.

As shown in Figures 1 to 9, the present disclosure provides a centrifugal right ventricular assist device, hereinafter referred to as "auxiliary device", which, in an exemplary embodiment, includes a centrifugal pump and a power transmitting component, centrifuged The pump is used to connect and relatively fix the heart of the human body, for example, in the right thymus position, and the front is close to the chest wall. Wherein, the centrifugal pump has a driving end, and one end of the power transmitting component is connected with the driving end, and can drive the driving end of the centrifugal pump to rotate with the movement of the respiratory muscle when the human body breathes, so as to drive the centrifugal pump to realize the pumping and pumping of the blood, thereby Provides the required power for the patient's pulmonary circulation, causing the blood in the human body to approach normal flow.

The auxiliary device of this embodiment of the present disclosure can assist patients with right heart dysplasia or right heart dysfunction, can save external force drive, and use the power of the patient to drive the centrifugal pump to work. Its function is similar to the normal right ventricular function of the human body. It repeatedly pumps in and pumps out blood when the human body breathes, providing the required power for the pulmonary circulation, and bringing the blood in the human body to normal flow. Moreover, compared with the auxiliary device using external power in the prior art, the auxiliary device of the present disclosure utilizes the power of the patient to assist the right ventricle when breathing, can eliminate complicated power and control system, and easily realize the contraction force with the left ventricle. Matching, it is easy to ensure the balance of the body lung circulation, which can better assist the right ventricle and achieve a longer auxiliary time, which is conducive to clinical application and promotion.

The centrifugal pump includes a housing 1, and the internal structure is shown in Fig. 2. The housing 1 is provided with an impeller 4, and one end of the impeller 4 along the rotation axis serves as a driving end, and the driving end can drive the impeller 4 to rotate when subjected to an external force. In some embodiments, the impeller 4 is a viscous impeller that is less damaging to blood components during rotation and also increases the adhesion of the blade surface to the blood to provide greater centrifugal force to the blood as the impeller 4 rotates, Increase the power provided by the centrifugal pump.

Referring to Figures 1, 3 and 7, the housing 1 of the centrifugal pump is provided with an inlet 2 and an outlet 3, the inlet 2 being arranged on the housing 1 along the axis of rotation of the impeller 4, and being disposed remotely from the impeller 4 On one side of the end, the inlet 2 is intended to communicate with the vena cava or right atrial appendage of the human body. The outlet 3 is located on the housing 1 in the tangential direction of the impeller 4 for use with the human body The pulmonary artery is connected.

In some embodiments, the power transmission component mentioned above includes at least two force applying members 7 respectively located on opposite sides of the driving end with respect to the rotation axis, and the first ends of the two side force applying members 7 are respectively connected to the driving end. The respective second ends are respectively connected to the ribs of the chest wall on both sides of the human body to drive the centrifugal pump to realize pumping and pumping of blood. The auxiliary device of the structure has three fixed points, including: a fixed point of connection between the centrifugal pump housing 1 and the human heart, and a fixing point of the side force applying members 7 on the chest wall ribs on both sides of the human body, which can make the auxiliary device The connection and fixing are more stable, thereby improving the reliability and life of the auxiliary device working in the human body.

The advantage of attaching the force applying member 7 to the rib is that the connection is convenient, the fixing is reliable, and since the rib does not cause significant deformation in a short period of time, serious complications are not easily caused. Of course, if it is desired to use the auxiliary device of the present disclosure to power the heart in a short period of time, the force applying member 7 can also be attached to other body parts that can move with the respiratory muscles, such as the sternum and diaphragm.

In some embodiments, the auxiliary device further includes a wrap structure for protecting the force applying members 7 on both sides to improve the reliability and life of the auxiliary device. The wrapping structure may be a flat tubular shape having a smooth inner wall, wrapping a force applying member on one side, and the shape is adapted to the force applying member.

Referring to Figures 4 and 5, a force applying member 7 is respectively disposed on both sides of the driving end with respect to the axis of rotation. The urging member 7 may be a long strip-like plate or strip-like structure, and the extending path may include a straight line or a curved line, as long as the structure for transmitting force from the rib of the chest wall to the driving end is within the protection scope of the present disclosure. In terms of material use, the urging member 7 may be a structural member made of metal or plastic.

In some embodiments, the two force applying members 7 are capable of synchronous reverse linear motion as the respiratory muscles move the ribs of the chest wall. Typically, the inlet 2 of the housing 1 of the centrifugal pump is sewn to the vena cava or to the right atrial appendage, and the outlet 3 is sewn to the pulmonary artery. Since the heart is not a completely fixed point, the synchronous force movement of the force applying members 7 on both sides of the driving end can realize the relative pulling or pushing of the driving end, so that the two sides of the centrifugal pump are simultaneously subjected to the relative force, and the centrifugal pump is maintained. The mounting position is stable and helps to protect the connection between the pump and the heart.

In some embodiments, the two force applying members 7 are kept relatively parallel during the movement, so that the two force applying members 7 can be more evenly stressed during the movement, so as not to cause too much involvement on the centrifugal pump. Helps protect the connection between the pump and the human heart.

As shown in Figs. 3 and 7, a connecting shaft 5 is provided at the driving end of the centrifugal pump, and one end of the connecting shaft 5 is connected to the impeller 4, and the other end is connected to the power transmission member. Further, the power transmitting member further includes a motion converting member for converting linear motion of the force applying members 7 on both sides of the driving end into rotational motion of the connecting shaft 5 to drive the impeller 4 to rotate. Depending on the direction of rotation that the impeller 4 can achieve, two types of embodiments are given below. In one embodiment, as shown in FIGS. 1 to 6, the auxiliary device of the present disclosure further includes a one-way mechanism provided between the motion converting member and the connecting shaft 5, and the motion converting member can be applied on both sides The force member 7 drives the connecting shaft 5 to rotate relative to the driving end, so that the centrifugal pump realizes pumping and pumping of blood, and stops working when the force applying members 7 on both sides are close to each other with respect to the driving end.

The working principle of the auxiliary device of this embodiment is given below:

When the human body inhales, referring to FIG. 1, FIG. 2 and FIG. 4, the intercostal muscle contraction drives the ribs on both sides of the chest wall to move upward and outward, and the ribs on both sides of the chest wall respectively drive the force applying members 7 on both sides with respect to the driving end. Along with the force transmission of the motion converting member and the one-way mechanism, the driving end drives the impeller 4 to rotate counterclockwise (in the direction of the arrow E), and the blood flows into the casing 1 of the centrifugal pump through the inlet 2 to realize the pumping of blood. At the same time, the blood in the centrifugal pump casing 1 is deflected toward the outer edge of the impeller 4 by the rotation of the impeller 4 to move counterclockwise along the arrow C, and then flows out along the arrow B through the outlet 3 to realize counterclockwise pumping of the blood. .

When the human body exhales, referring to FIG. 5, the intercostal muscle relaxation causes the ribs on both sides of the chest wall to move downward and inward, and the ribs on both sides of the chest wall respectively drive the two force applying members 7 to be close to each other with respect to the driving end, in one direction Under the action of the mechanism, the drive end cannot be rotated, and the impeller 4 remains stationary, so that the centrifugal pump stops working.

As shown in Figure 6, the motion converting member and the one-way mechanism together form a flywheel structure. Specifically, the motion converting member includes a gear 6 and a rack that mesh with each other, and the one-way mechanism includes a ratchet 6' provided on the inner circumference of the gear 6, and a pawl 8 provided on the outer circumference of the connecting shaft 5, the pawl 8 and the spine The teeth 6, cooperate with each other. For example, the two pawls 8 can respectively engage the ratchet teeth 6' at the opposite positions of the inner ring of the gear 6. For example, the two pawls 8 respectively engage with the ratchet teeth 6' of the upper and lower positions of the inner ring of the gear 6.

The gear 6 is provided at the outer end of the connecting shaft 5, that is, on the opposite side of the inlet 2. The rack is disposed on the at least a portion of the length of the biasing member 7 adjacent to the gear 6, and the rack can be fixed to the urging member 7 or integrally formed with the urging member 7. The length of the rack can be adjusted to indirectly adjust the blood flow per pump to accommodate the patient's pulmonary circulation. The two racks are respectively engaged with the opposite positions on the outer circumference of the gear 6. For example, based on the figures shown in Figs. 4 and 5, the two racks mesh with the teeth of the outer ring at the upper and lower positions of the gear 6, respectively. This embodiment can save complicated power and control system, and adjust the rotation speed of the impeller 4 indirectly by adjusting the diameter of the driving end gear 6, and adjust the pump bleeding amount to adapt to the patient's pulmonary circulation, so as to achieve the phase balance of the body lung circulation, thereby being able to Better assist the right ventricle and achieve a longer auxiliary time, which is conducive to clinical application and promotion.

The gear transmission method has a simple structure, small occupied space, and can make the rotation of the connecting shaft 5 more stable, thereby making the blood pumping process more moderate. Alternatively, in another structural form, the motion converting member is a crank slider mechanism, and the slider is coupled to the urging member 7 to linearly move along the sliding slot, and the crank is connected to the connecting shaft 5 for driving The moving shaft rotates.

As shown in Figs. 1 and 2, the centrifugal pump includes a housing 1 and an impeller 4 disposed in the housing 1, and the housing 1 is provided with an outlet 3. In one configuration, the housing 1 is provided as a volute housing, and the outlet 3 is disposed along a single tangential direction of the impeller 4 to accommodate one-way pumping of blood. For example, in Fig. 1, the outlet is disposed along the right tangential direction of the impeller 4.

For the embodiment of the motion converting member including the gear 6 and the rack, the one-way mechanism includes the ratchet 6' and the pawl 8, the working principle of such an auxiliary device is specifically described as follows:

When the human body inhales, referring to Fig. 1, Fig. 2, Fig. 4 and Fig. 6, the intercostal muscle contraction drives the ribs on both sides of the chest wall to move upward and outward, and the ribs on both sides of the chest wall respectively drive the force applying members 7 on both sides. The driving ends are away from each other along the arrow D, that is, the overlapping sections of the two urging members 7 are shortened, and the two racks are also away from each other, and the gear 6 is driven to rotate counterclockwise (in the direction of the arrow E) through the inner ring of the gear 6. The ratchet 6' dials the pawl 8, drives the connecting shaft 5 and the impeller 4 to rotate counterclockwise, and the blood flows into the housing 1 of the centrifugal pump through the inlet 2 to realize the pumping of blood. At the same time, the blood in the centrifugal pump casing 1 is deflected toward the outer edge of the impeller 4 by the rotation of the impeller 4, and moves counterclockwise along the arrow C, and then flows out along the arrow B through the outlet 3 to realize the counterclockwise pump of blood. Out.

When the human body exhales, referring to FIG. 5 and FIG. 6, the intercostal muscle relaxation causes the ribs on both sides of the chest wall to move downward and inward, and the ribs on both sides of the chest wall respectively drive the two force applying members 7 with respect to the driving end along the arrow F. Close to each other, that is, the overlapping sections of the two urging members 7 become longer, and the two racks are also close to each other. As shown in FIG. 6, the driving gear 6 rotates clockwise (in the direction of the arrow G), but is disposed in the inner ring of the gear 6. The ratchet 6' cannot drive the pawl 8 to drive the connecting shaft 5 to rotate, and the impeller 4 remains stationary, so that the centrifugal pump stops working.

In another embodiment, as shown in FIGS. 7 to 9, the motion converting member can rotate the connecting shaft 5 in opposite directions when the side applying members 7 are apart from or close to each other with respect to the driving end (arrows E and G) Direction), so that the pump can be pumped and pumped out when the centrifugal pump rotates in different directions. This auxiliary device, which enables two-way work, provides more power to the pulmonary circulation, bringing the blood closer to normal flow.

When the human body inhales, in conjunction with FIG. 7 and FIG. 8, the intercostal muscle contraction drives the ribs on both sides of the chest wall to move upward and outward, and the ribs on both sides of the chest wall respectively drive the side force applying members 7 away from each other with respect to the driving end. The drive end rotates counterclockwise (in the direction of arrow E), and blood flows into the housing 1 of the centrifugal pump through the inlet 2 to effect pumping of blood. At the same time, the blood in the centrifugal pump casing 1 is deflected toward the outer edge of the impeller 4 by the rotation of the impeller 4 to move counterclockwise along the hollow arrow C1, and then flows out along the arrow B through the outlet 3 to realize the counterclockwise pump of blood. Out.

When the human body exhales, in conjunction with FIG. 7 and FIG. 9, the intercostal muscle relaxation causes the ribs on both sides of the chest wall to move downward and inward, and the ribs on both sides of the chest wall respectively drive the two force applying members 7 to approach each other with respect to the driving end. Make the drive clockwise (in the direction of the arrow G), the blood flows into the casing 1 of the centrifugal pump through the inlet 2, and the blood is pumped. At the same time, the blood in the centrifugal pump casing 1 is deflected toward the outer edge of the impeller 4 by the rotation of the impeller 4 to move clockwise along the solid arrow C2, and then flows out along the arrow B through the outlet 3 to realize the clockwise pump of the blood. Out.

The outer structure of the centrifugal pump is shown in Fig. 7, and the casing 1 of the centrifugal pump is provided with an outlet 3. In some embodiments, the housing 1 is a gourd-shaped housing as shown in Fig. 7, that is, the bottom has a circular arc shape, and the upper portion gradually contracts inwardly on the basis of the circular arc structure. The outlet 3 is provided at the double tangential merge position of the impeller 4, i.e., the junction of the blood outflow passages of the casing 1 which are disposed tangentially along the impeller 4 as the outlet 3. Further, the distal confluence of the outlet 3 is inflated to conform to hemodynamics and to accommodate positive or reverse pumping of blood.

Specifically, the motion converting member may include a gear 6 and a rack, and the gear 6 is provided at an outer end of the connecting shaft 5, that is, on the opposite side of the inlet 2, and the rack is disposed at at least a portion of the length of the biasing member 7 near the gear 6. Upper, the rack can be fixed on the urging member 7, or can be integrally formed with the urging member 7. The length of the rack can be adjusted to indirectly adjust the blood flow per pump to accommodate the patient's pulmonary circulation. The two racks are respectively engaged with the positions of the gears 6. Preferably, the two racks mesh with the gear 6 at the upper and lower positions of the gear 6 with reference to the drawings shown in Figs. 8 and 9. The diameter of the gear 6 can be selected according to the demand, indirectly adjusting the rotational speed of the impeller 4, and regulating the amount of pump bleeding to accommodate the pulmonary circulation of the patient.

The gear transmission method has a simple structure, small space occupation, and can make the rotation of the connecting shaft 5 more stable, thereby making the blood pumping process more moderate. The two racks are respectively engaged with the opposite positions on the gear 6, and the gear 6 can be driven to rotate by the reverse simultaneous movement of the two racks. Referring to Fig. 8, when the side force applying members 7 are apart from each other with respect to the driving end, the gear 6 is driven to rotate counterclockwise by the arrow E by the rack. Referring to Fig. 9, when the side force applying members 7 are close to each other with respect to the driving end, the gear 6 is rotated clockwise by the arrow G, and both of the states can be pumped and pumped out.

For the structure of the motion conversion component including the gear 6 and the rack, the working principle of such an auxiliary device is specifically described as follows:

When the human body inhales, combined with FIG. 7 and FIG. 8, the intercostal muscle contraction drives the ribs on both sides of the chest wall to move upward and outward, and the ribs on both sides of the chest wall respectively drive the two force applying members 7 along the connecting shaft 5 along the arrow D. Moving away from each other, that is, the overlapping sections of the two force applying members 7 are shortened, and the two racks are also away from each other, so that the gear 6, the connecting shaft 5 and the impeller 4 are rotated counterclockwise (in the direction of the arrow E), and the blood flows in through the inlet 2. In the housing 1 of the centrifugal pump, blood is pumped in. The blood in the centrifugal pump casing 1 is urged toward the outer edge of the impeller 4 by the rotation of the impeller 4 to move counterclockwise along the arrow C1, and then flows out through the outlet 3 along the arrow B to effect counter-clockwise pumping of the blood.

When the human body exhales, combined with Figure 7 and Figure 9, the intercostal muscle relaxation causes the ribs on both sides of the chest wall to move downwards.

Claims

The ribs on both sides of the chest wall respectively drive the two force applying members 7 to be close to each other with respect to the connecting shaft 5 along the arrow F, that is, the overlapping ends of the two force applying members 7 become long, and the two racks are also close to each other, and the gears are driven. 6 The connecting shaft 5 is rotated by the instantaneous needle (in the direction of the arrow G), and the blood flows into the casing 1 of the centrifugal pump through the inlet 2 to realize the pumping of blood. The blood in the centrifugal pump casing 1 is urged toward the outer edge of the impeller 4 by the rotation of the impeller 4 to move clockwise along the arrow C2, and then flows out along the arrow B through the outlet 3 to realize clockwise pumping of the blood. The auxiliary device of the present disclosure is designed to solve the power of the pulmonary circulation, and is different from other pumps designed to improve left ventricular dysmotility, and can stably provide the pulmonary circulation for patients with right ventricular dysplasia or right ventricular dysfunction. Motivation, which lays the foundation for the ultimate realization of autologous right ventricular assist, can greatly improve the surgical outcome and prognosis of such patients. Moreover, the auxiliary device can be powered by the patient's own breathing, and can be driven by the movement of the respiratory muscles without the need to provide additional power components. When the auxiliary device is implanted into the human body, the function of the original ventricle can be prevented to the utmost extent. In addition, there is no mechanical valve in the auxiliary device, and a viscous impeller rotor is used, which has less damage to blood components. In terms of the manufacturing method, the auxiliary device of the present disclosure can adopt a 3D printing method to manufacture an integrated auxiliary device or make a key component, and the auxiliary device can also be produced by using a conventional mold. In terms of material use, auxiliary devices can be produced using biocompatible metals, synthetic biomaterials or other non-immunogenic materials. At present, chemical materials are readily available and stable in nature, and are preferably used for the production of centrifugal right-heart assist pumps. A centrifugal right ventricular assist device provided by the present disclosure has been described in detail above. The principles and embodiments of the present disclosure have been described with reference to the specific embodiments herein, and the description of the above embodiments is only to assist in understanding the method of the present disclosure and its core idea. It should be noted that those skilled in the art can make various modifications and changes to the present disclosure without departing from the scope of the present disclosure, and such modifications and modifications are also within the scope of the appended claims. Rights request

A centrifugal right ventricular assist device comprising:

a centrifugal pump having a drive end; and

The power transmitting component is coupled to the driving end for driving the driving end to rotate according to the movement of the respiratory muscle to drive the centrifugal pump to realize pumping and pumping of blood.

2. The centrifugal right ventricle assist device according to claim 1, wherein the power transmitting member comprises at least two force applying members (7) respectively located on both sides of the driving end, and the force applying members on both sides ( 7) The respective first ends are respectively connected to the driving end, and the respective second ends are respectively connected with the ribs of the chest wall on both sides of the human body, and can drive the driving end to rotate when the respiratory muscles drive the ribs of the chest wall.

3. The centrifugal right ventricle assist device according to claim 2, wherein the force applying members (7) on both sides perform synchronous reverse linear motion when the respiratory muscles drive the ribs.

4. The centrifugal right ventricle assist device according to claim 1, wherein the centrifugal pump is provided with an inlet (2) and an outlet (3), and the inlet (2) is disposed at a side opposite to the driving end Side, the inlet (2) is for communication with a right atrial appendage or vena cava, and the outlet (3) is for communicating with a pulmonary artery.

5. The centrifugal right ventricle assist device according to claim 2, wherein a driving end of the centrifugal pump is provided with a connecting shaft (5), and the power transmitting member further includes a motion converting member for The linear motion of the urging member (7) is converted into the rotational motion of the connecting shaft (5).

6. The centrifugal right ventricle assist device according to claim 5, further comprising a one-way mechanism provided between the motion converting member and the connecting shaft (5), the motion converting member The connecting shaft (5) can be rotated when the force applying members (7) on the two sides are away from each other with respect to the driving end, so as to realize pumping and pumping of blood, and the force applying members on both sides (7) Stop working when they are close to each other with respect to the drive end.

7. The centrifugal right ventricle assist device according to claim 6, wherein the centrifugal pump comprises a housing (1) and an impeller (4) provided in the housing (1), the housing is provided There is an outlet (3) which is provided at a single tangential position of the impeller (4).

8. The centrifugal right ventricle assist device according to claim 5, wherein the motion converting member is capable of driving the connecting shaft when the force applying members (7) on both sides are away from or close to each other with respect to the driving end (5) Rotate in the opposite direction so that the centrifugal pump can pump and pump blood in both states.

9. The centrifugal right ventricle assist device according to claim 8, wherein the centrifugal pump comprises a housing (1) and an impeller (4) provided in the housing (1), the housing is provided Have an exit (3), the exit (3) At the converging position of the impeller (4) in a double tangential direction.

10. The centrifugal right ventricle assist device according to claim 5, wherein the motion converting member comprises a gear (6) and a rack, and the gear (6) is provided at an outer end of the connecting shaft (5), The rack is disposed on the at least a portion of the length of the force applying member (7) adjacent to the gear (6), and the two racks are respectively at the gear

Engage at the relative position of (6).

11. The centrifugal right ventricular assist device according to claim 2, wherein the force applying members (7) on both sides remain relatively parallel during the movement.

12. The centrifugal right ventricular assist device according to claim 2, further comprising a wrap structure for protecting the force applying members (7) on both sides.

13. The centrifugal right ventricle assist device according to claim 1, wherein the centrifugal pump comprises an impeller (4), the impeller (4) being a viscous impeller.

14. The centrifugal right ventricular assist device according to claim 1, wherein the centrifugal pump is for connecting and relatively fixed to a heart structure of a human body.