Axial-flow type ventricular auxiliary pump with extracorporeal power supply

Abstract

The invention relates to an axial-flow type ventricular auxiliary pump for external power supply, which is characterized in that a front guide vane and a rear guide vane are coaxially fixed at the front part of an inner cavity of a pump shell, and a gap for mounting an impeller is reserved between the front guide vane and the rear guide vane; a first wire penetrating hole is coaxially formed in a hub of the front guide vane in a penetrating mode, and the first wire penetrating hole is right opposite to the first center hole. A hub of the rear guide vane is of a circular driven shaft-shaped structure with a closed front end and an open rear end; a driven shaft coaxially and rotatably penetrates through the front end of a hub of the rear guide vane; a second wire penetrating hole is coaxially formed in the driven shaft in a penetrating mode, and the second wire penetrating hole is right opposite to the first wire penetrating hole. An impeller is fixedly assembled on the side face of the driven shaft and located in a gap between the front guide vane and the rear guide vane. The rear end of the driven shaft is coaxially connected with a driving shaft, and the driving shaft rotationally penetrates through the supporting sleeve. The driving motor is externally arranged, so that the driving motor does not need to intervene into the blood vessel along with the pump in the treatment process.

Description

Technical Field

[0001] The present invention relates to an axial flow ventricular assist pump with external power supply, belonging to the technical field of medical devices. Background Art

[0002] A ventricular assist pump is a mechanical device that assists the heart in supplying blood to the aorta and is used for patients with heart failure or those waiting for a heart transplant. Currently, the marketed ventricular assist pumps mainly include two categories: one is a magnetic levitation centrifugal ventricular assist pump, and the other is an axial flow ventricular assist pump with an in-built drive motor. Due to their own structural limitations, these two types of ventricular assist pumps have the following problems:

[0003] Firstly, the problems of the magnetic levitation centrifugal ventricular assist pump are as follows: 1. Due to the adoption of a centrifugal impeller structure, the overall size of this pump is relatively large, so it needs to be implanted through surgery for treatment, resulting in high surgical costs, great surgical difficulty, and large surgical trauma. 2. Limited by magnetic levitation technology, on the one hand, this pump is easily interfered by external movement and electromagnetism, and on the other hand, the manufacturing cost is relatively high. Therefore, on the one hand, its working stability is poor, and on the other hand, it causes a relatively large economic burden on patients.

[0004] Secondly, during the treatment process of the axial flow ventricular assist pump with an in-built drive motor, the drive motor needs to intervene in the blood vessel together with the pump, which brings the following problems: 1. The surgical cost is relatively high. 2. The volume and power of the drive motor are limited, resulting in a relatively small blood supply. 3. The heat generated by the drive motor during operation is likely to cause thermal damage to patients. 4. When the drive motor needs to be replaced due to a malfunction during operation, the replacement is not convenient.

[0005] Based on this, it is necessary to invent an axial flow ventricular assist pump with external power supply to solve the problems of high surgical costs, great surgical difficulty, large surgical trauma, poor working stability, large economic burden on patients, small blood supply, easy thermal damage to patients, and inconvenient replacement when a malfunction occurs in the existing ventricular assist pumps. Summary of the Invention

[0006] The purpose of the present invention is to provide an axial flow ventricular assist pump with external power supply to solve the problems of high surgical costs, great surgical difficulty, large surgical trauma, poor working stability, large economic burden on patients, small blood supply, easy thermal damage to patients, and inconvenient replacement when a malfunction occurs in the existing ventricular assist pumps.

[0007] The present invention adopts the following technical solutions:

[0008] An axially-flowing ventricular assist pump with an external power supply, comprising a pump housing 1. The pump housing 1 is of a cylindrical structure. An inlet 1.1 is provided at the front part of the side wall of the pump housing 1, and an outlet 1.2 is provided at the rear part of the side wall. A first central hole 1.3 is coaxially provided at the front end of the pump housing 1, and a second central hole 1.4 is coaxially provided at the rear end. The second central hole 1.4 is hermetically connected to a support sleeve 3. A front guide vane 4 and a rear guide vane 5 are coaxially fixed in the front part of the inner cavity of the pump housing 1, and a gap for installing an impeller 7 is left between the front guide vane 4 and the rear guide vane 5. A first wire-passing hole 4.1 is coaxially and penetratingly provided on the hub of the front guide vane 4, and the first wire-passing hole 4.1 is aligned with the first central hole 1.3. The hub of the rear guide vane 5 is a circular structure with a closed front end and an open rear end; a driven shaft 6 coaxially and rotatably penetrates through the front end of the hub of the rear guide vane 5. A second wire-passing hole 6.1 is coaxially and penetratingly provided on the driven shaft 6, and the second wire-passing hole 6.1 is aligned with the first wire-passing hole 4.1. An impeller 7 is fixedly assembled on the outer side of the driven shaft 6, and the impeller 7 is located in the gap between the front guide vane 4 and the rear guide vane 5. A bearing 8 is assembled between the outer side surface of the driven shaft 6 and the inner side surface of the hub of the rear guide vane 5. The rear end of the driven shaft 6 is coaxially connected to a driving shaft 9, and the driving shaft 9 rotatably penetrates through the support sleeve 3. A bifurcated pipe 11 for introducing a coolant or a lubricating fluid is hermetically communicated with the rear part of the side wall of the support sleeve 3.

[0009] Preferably, a bearing cover 10 is fixedly assembled on the outer side surface of the driving shaft 9, and the bearing cover 10 is buckled on the open rear end of the hub of the rear guide vane 5; a driving motor 12 is provided at the rear side of the driving shaft 9, and the output shaft of the driving motor 12 is coaxially connected to the rear end of the driving shaft 9.

[0010] Preferably, a pigtail tube 2 for guiding a wire to pass through is hermetically connected to the front end of the first central hole 1.3.

[0011] Preferably, the front part of the pump housing 1 is in the shape of a frustum of a cone with a smaller front end and a larger rear end; the number of the inlets 1.1 is four, and the four inlets 1.1 are arranged equidistantly in the circumferential direction; the number of the outlets 1.2 is three, and the three outlets 1.2 are arranged equidistantly in the circumferential direction.

[0012] Preferably, the front end face of the hub of the front guide vane 4 is a hemispherical surface; the aperture of the rear end of the first wire-passing hole 4.1 is larger than that of the front end; the front end wall of the driven shaft 6 is in the shape of a cone with a smaller front end and a larger rear end, and the tip of the cone of the driven shaft 6 extends into the first wire-passing hole 4.1.

[0013] Preferably, the blades of the front guide vane 4 are straight blades; the blades of the rear guide vane 5 are curved blades; the blades of the impeller 7 are spiral blades.

[0014] Preferably, the number of the bearings 8 is two, and a distance is left between the two bearings 8; a shaft sleeve 13 is also fixedly assembled on the outer side surface of the driving shaft 9, and the shaft sleeve 13 is located between the two bearings 8.

[0015] Preferably, the bearing cover 10 is a cylindrical structure with an open front end and a closed rear end.

[0016] Preferably, the outside of the drive motor 12 is covered with a housing 14; a rubber sleeve 15 is fixedly penetrated through the side wall of the housing 14; a coupling 16 is provided in the inner cavity of the housing 14; the driving shaft 9 rotates through the rubber sleeve 15; the output shaft of the drive motor 12 is coaxially connected to the rear end of the driving shaft 9 through the coupling 16.

[0017] Preferably, both the driving shaft 9 and the driven shaft 6 are flexible shafts. The flexibility of the flexible shaft is not the flexibility of the material, but because the structure is in the shape of a spring.

[0018] During operation, the operating physician first inserts the guide wire into the femoral artery of the patient, so that the guide wire enters the left ventricle through the aortic valve, and then inserts the external part of the guide wire into the pigtail catheter, so that the external part of the guide wire passes through the first wire-passing hole, the second wire-passing hole, the driving shaft, and the bifurcated tube in sequence, and then inserts the present invention into the patient's body along the guide wire. On the one hand, the blood inlet is inserted into the left ventricle of the patient, and on the other hand, the blood outlet is inserted into the aorta of the patient.

[0019] The specific working process is as follows: Start the drive motor. The output shaft of the drive motor drives the driving shaft to rotate. The driving shaft drives the driven shaft to rotate. The driven shaft drives the impeller to rotate. Under the suction action of the impeller, the blood in the left ventricle first flows through the blood inlet to the inner cavity of the pump housing, and then flows through the blood outlet to the aorta, thereby pumping the blood from the left ventricle to the aorta. In the above process, the pigtail catheter can prevent the blood inlet from directly contacting the left ventricular wall, thereby avoiding damage. The front guide vane and the rear guide vane can ensure the stable flow of blood, thereby reducing the hemolysis rate.

[0020] Based on the above process, compared with the existing ventricular assist pump, the axial flow ventricular assist pump with external power supply described in the present invention has a new structure and has the following advantages:

[0021] First, compared with the magnetic levitation centrifugal ventricular assist pump, the advantages of the present invention are: 1. The present invention no longer adopts a centrifugal impeller structure, but an axial flow impeller structure, thereby effectively reducing the overall size. Therefore, it does not need to be treated through an implantation operation, but only through an interventional operation, thereby effectively reducing the surgical cost, effectively reducing the surgical difficulty, and effectively reducing the surgical injury. 2. The present invention is not limited by the magnetic levitation technology. On the one hand, it will not be interfered by external movement and electromagnetism, and on the other hand, it effectively reduces the manufacturing cost. Therefore, on the one hand, it effectively improves the working stability, and on the other hand, it effectively reduces the economic burden of the patient.

[0022] Second, compared with the drive motor built-in axial flow ventricular assist pump, the drive motor of the present invention is external. Therefore, during the treatment process, the drive motor does not need to intervene in the blood vessel together with the pump. The advantages brought about are as follows: 1. The surgical cost is effectively reduced. 2. The volume and power of the drive motor are no longer limited, thereby effectively increasing the blood supply. 3. The heat generated by the drive motor during operation will not cause thermal damage to the patient. 4. When the drive motor needs to be replaced due to a malfunction during operation, the replacement is very convenient.

[0023] Therefore, the present invention effectively solves the problems of the existing ventricular assist pump, such as high surgical cost, great surgical difficulty, large surgical injury, poor working stability, large economic burden on patients, small blood supply, easy to cause thermal damage to patients, and inconvenient replacement when a malfunction occurs, and is applicable to patients with heart failure or waiting for heart transplantation. BRIEF DESCRIPTION OF THE DRAWINGS

[0024] Figure 1 It is a schematic diagram of the overall external structure of the axial flow ventricular assist pump with an external power supply of the present invention.

[0025] Figure 2 It is Figure 1 partial structure schematic Figure 1 .

[0026] Figure 3 It is Figure 2 partial structure schematic Figure 1 .

[0027] Figure 4 It is Figure 2 the local enlarged view at A in

[0028] Figure 5 It is Figure 2 the local enlarged view at B in

[0029] Figure 6 It is Figure 2 partial structure schematic Figure 2 .

[0030] Figure 7 It is Figure 6 the local enlarged view at C in

[0031] Figure 8 It is Figure 2 partial structure schematic Figure 3 .

[0032] Figure 9 It is Figure 8 partial structure schematic diagram.

[0033] Figure 10 It is Figure 9 partial structure schematic diagram.

[0034] Figure 11 is Figure 10 a partial structural schematic diagram of

[0035] Figure 12 is Figure 11 a partial structural schematic diagram of

[0036] Figure 13 is Figure 12 a partial structural schematic diagram of

[0037] Figure 14 is Figure 8 a schematic diagram of the structure from another angle of

[0038] Figure 15 is Figure 14 a partial structural schematic diagram of

[0039] Figure 16 is Figure 15 a partial structural schematic diagram of

[0040] Figure 17 is Figure 16 a partial structural schematic diagram of

[0041] Figure 18 is Figure 17 a partial structural schematic diagram of

[0042] Figure 19 is Figure 18 a partial structural schematic diagram of

[0043] Figure 20 is Figure 1 a partial structural schematic Figure 2 .

[0044] Figure 21 is Figure 20 a partial structural schematic diagram of

[0045] In the figure: 1 - pump housing, 1.1 - blood inlet, 1.2 - blood outlet, 1.3 - first central hole, 1.4 - second central hole, 2 - pigtail tube, 3 - support sleeve, 4 - front guide vane, 4.1 - first wire threading hole, 5 - rear guide vane, 6 - driven shaft, 6.1 - second wire threading hole, 7 - impeller, 8 - bearing, 9 - driving shaft, 10 - bearing cover, 11 - bifurcated pipe, 12 - driving motor, 13 - bushing, 14 - housing, 15 - rubber sleeve, 16 - coupling. Specific embodiments

[0046] The present invention will be further described below in conjunction with the accompanying drawings and specific embodiments.

[0047] See Figure 1-2, an axially - flow ventricular assist pump with an external power supply, comprising a pump housing 1;

[0048] Combined Figure 1-3 , the pump housing 1 is a cylindrical structure with both ends closed; a blood inlet 1.1 is formed through the front part of the side wall of the pump housing 1; a blood outlet 1.2 is formed through the rear part of the side wall of the pump housing 1; a first central hole 1.3 (for threading a guide wire) is formed through the front end wall of the pump housing 1 coaxially, and a pigtail tube 2 is hermetically docked with the first central hole 1.3; a second central hole 1.4 (for threading the driving shaft 9 and then threading a guide wire through the middle of the driving shaft) is formed through the rear end wall of the pump housing 1 coaxially, and a support sleeve 3 is hermetically docked with the second central hole 1.4.

[0049] See Figure 2 , a front guide vane 4 and a rear guide vane 5 (for support, supported on the inner wall of the support sleeve 3) are coaxially fixed to the front part of the inner cavity of the pump housing 1, and there is a distance between the front guide vane 4 and the rear guide vane 5; a first wire - threading hole 4.1 is formed through the hub of the front guide vane 4 coaxially, and the first wire - threading hole 4.1 is aligned with the first central hole 1.3; the hub of the rear guide vane 5 is a cup - shaped structure with a closed front end and an open rear end; a driven shaft 6 rotates through the front end wall of the hub of the rear guide vane 5 coaxially.

[0050] A second wire - threading hole 6.1 is formed through the driven shaft 6 coaxially, and the second wire - threading hole 6.1 is aligned with the first wire - threading hole 4.1; an impeller 7 is fixedly assembled on the side surface of the driven shaft 6, and the impeller 7 is located between the front guide vane 4 and the rear guide vane 5; a bearing 8 is assembled between the side surface of the driven shaft 6 and the inner side surface of the hub of the rear guide vane 5.

[0051] The rear end of the driven shaft 6 is coaxially connected to a driving shaft 9, and the driving shaft 9 rotates through the support sleeve 3; the driving shaft 9 is a flexible pipe structure of a round tube with both ends open (preferably, it can be a spring structure made of metal material); a bearing cover 10 is fixedly assembled on the outer side surface of the driving shaft 9, and the bearing cover 10 is buckled on the open rear end of the hub of the rear guide vane 5; a bifurcated pipe 11 (for introducing cooling or lubricating liquid) is hermetically communicated with the rear part of the side wall of the support sleeve 3 outside the driving shaft 9; a driving motor 12 is arranged at the rear side of the driving shaft 9, and the output shaft of the driving motor 12 is coaxially connected to the rear end of the driving shaft 9.

[0052] See Figure 3 , the front part of the pump housing 1 is in the shape of a frustum of a cone with a thinner front and a thicker rear; the number of the blood inlets 1.1 is four, and the four blood inlets 1.1 are arranged equidistantly in the circumferential direction; the number of the blood outlets 1.2 is three, and the three blood outlets 1.2 are arranged equidistantly in the circumferential direction.

[0053] See Figure 8-14 , the front end face of the hub of the front guide vane 4 is a hemispherical surface; the rear aperture of the first wire - threading hole 4.1 is larger than the front aperture; the front end wall of the driven shaft 6 is in the shape of a cone with a thinner front and a thicker rear, and the tip of the cone of the driven shaft 6 extends into the first wire - threading hole 4.1.

[0054] See Figure 8 , the blades of the leading guide vane 4 are straight blades; the blades of the trailing guide vane 5 are curved blades; the blades of the impeller 7 are helical blades.

[0055] See Figure 15 , the number of bearings 8 is two, and there is a distance between the two bearings 8; a bushing 13 is fixedly assembled on the outer side of the driving shaft 9, and the bushing 13 is located between the two bearings 8.

[0056] See Figure 14 , the bearing cover 10 is a cup-shaped structure with an open front end and a closed rear end.

[0057] See Figure 20-21 , the outer side of the driving motor 12 is covered with a casing 14; a rubber sleeve 15 is fixedly penetrated through the side wall of the casing 14; a coupling 16 is provided in the inner cavity of the casing 14; the driving shaft 9 rotates through the rubber sleeve 15; the output shaft of the driving motor 12 is coaxially connected to the rear end of the driving shaft 9 through the coupling 16.

[0058] During operation, the operating physician first inserts the guide wire through the femoral artery of the patient, so that the guide wire enters the left ventricle through the aortic valve, and then inserts the external part of the guide wire through the pigtail catheter, so that the external part of the guide wire passes through the first wire-passing hole, the second wire-passing hole, the driving shaft, and the bifurcated pipe in sequence and then exits, and then inserts the present invention into the patient along the guide wire. On the one hand, the blood inlet is inserted into the left ventricle of the patient, and on the other hand, the blood outlet is inserted into the aorta of the patient.

[0059] The specific working process is as follows: Start the driving motor, the output shaft of the driving motor drives the driving shaft to rotate, the driving shaft drives the driven shaft to rotate, and the driven shaft drives the impeller to rotate. Under the suction action of the impeller, the blood in the left ventricle first flows through the blood inlet into the inner cavity of the pump housing, and then flows through the blood outlet into the aorta, thereby pumping the blood from the left ventricle to the aorta. During the above process, the pigtail catheter can prevent the blood inlet from directly contacting the left ventricular wall, thereby avoiding damage. The leading guide vane and the trailing guide vane can ensure the stable flow of blood, thereby reducing the hemolysis rate.

[0060] Compared with the driving motor built-in axial-flow ventricular assist pump, the driving motor of the present invention is external. Therefore, during the treatment process, the driving motor does not need to be inserted into the blood vessel together with the pump. The advantages brought about are: 1. The surgical cost is effectively reduced. 2. The volume and power of the driving motor are no longer limited, thereby effectively increasing the blood supply. 3. The heat generated by the driving motor during operation will not cause thermal damage to the patient. 4. When the driving motor needs to be replaced due to a failure during operation, the replacement is very convenient.

[0061] Although the specific embodiments of the present invention have been described above, those skilled in the art should understand that these are only examples, and the protection scope of the present invention is defined by the appended claims. Without departing from the principle and essence of the present invention, those skilled in the art can make various changes or modifications to these embodiments, but these changes and modifications all fall within the protection scope of the present invention.

Claims

1. An axial-flow ventricular assist pump with extracorporeal power supply, comprising a pump housing (1), characterized in that: The pump housing (1) is a cylindrical structure, a blood inlet (1.1) is provided at the front of the side wall of the pump housing (1), and a blood outlet (1.2) is provided at the rear of the side wall; a first center hole (1.3) is coaxially provided at the front end of the pump housing (1), and a second center hole (1.4) is coaxially provided at the rear end, and the second center hole (1.4) is sealingly connected to the support sleeve (3); A front guide vane (4) and a rear guide vane (5) are coaxially fixed to the front of the inner cavity of the pump housing (1), and a gap for installing an impeller (7) is left between the front guide vane (4) and the rear guide vane (5); a first threading hole (4.1) is coaxially opened on the hub of the front guide vane (4), and the first threading hole (4.1) is directly opposite to the first center hole (1.3); the hub of the rear guide vane (5) is a circle with a closed front end and an open rear end, and the driven shaft-shaped structure; the front end of the hub of the rear guide vane (5) is coaxially rotated and penetrated by the driven shaft (6); A second threading hole (6.1) is coaxially formed on the driven shaft (6), and the second threading hole (6.1) is directly opposite to the first threading hole (4.1); an impeller (7) is fixedly mounted on the side of the driven shaft (6), and the impeller (7) is located in the gap between the front guide vane (4) and the rear guide vane (5); a bearing (8) is mounted between the outer side surface of the driven shaft (6) and the inner side surface of the hub of the rear guide vane (5); The rear end of the driven shaft (6) is coaxially connected to the driving shaft (9), and the driving shaft (9) rotates to penetrate the support sleeve (3); the rear part of the side wall of the support sleeve (3) is sealed and connected to a bifurcated pipe (11) for passing a cooling liquid or a lubricating liquid.

2. The axial-flow ventricular assist pump with extracorporeal power supply according to claim 1, characterized in that: A bearing cover (10) is fixedly mounted on the outer side of the driving shaft (9), and the bearing cover (10) is buckled onto the rear end opening of the hub of the rear guide vane (5); a driving motor (12) is arranged on the rear side of the driving shaft (9), and the output shaft of the driving motor (12) is coaxially connected to the rear end of the driving shaft (9).

3. The axial-flow ventricular assist pump with extracorporeal power supply according to claim 1, characterized in that: The front end of the first central hole (1.3) is sealedly connected to a pigtail tube (2) for the guide wire to pass through.

4. The axial-flow ventricular assist pump with extracorporeal power supply according to claim 1, characterized in that: The front part of the pump housing (1) is in the shape of a truncated cone which is thin at the front and thick at the back; there are four blood inlets (1.1) which are arranged equidistantly in the circumferential direction; there are three bleeding ports (1.2) which are arranged equidistantly in the circumferential direction.

5. The axial-flow ventricular assist pump with extracorporeal power supply according to claim 1, characterized in that: The front end face of the hub of the front guide vane (4) is a hemispherical surface; the rear end aperture of the first threading hole (4.1) is larger than the front end aperture; the front end wall of the driven shaft (6) is in a conical shape with a thin front end and a thick rear end, and the cone tip of the driven shaft (6) extends into the first threading hole (4.1).

6. The axial-flow ventricular assist pump with extracorporeal power supply according to claim 1, characterized in that: The blades of the front guide vane (4) are straight blades; the blades of the rear guide vane (5) are curved blades; and the blades of the impeller (7) are spiral blades.

7. The axial-flow ventricular assist pump with extracorporeal power supply according to claim 1, characterized in that: There are two bearings (8), and a distance is left between the two bearings (8); a shaft sleeve (13) is also fixedly mounted on the outer side surface of the driving shaft (9), and the shaft sleeve (13) is located between the two bearings (8).

8. The axial-flow ventricular assist pump with extracorporeal power supply according to claim 1, characterized in that: The bearing cover (10) is a cylindrical structure with an open front end and a closed rear end.

9. The axial-flow ventricular assist pump with extracorporeal power supply according to claim 1, characterized in that: The outer side of the driving motor (12) is covered with a housing (14); a rubber sleeve (15) is fixedly passed through the side wall of the housing (14); a coupling (16) is provided in the inner cavity of the housing (14); the driving shaft (9) rotatably passes through the rubber sleeve (15); and the output shaft of the driving motor (12) is coaxially connected to the rear end of the driving shaft (9) through the coupling (16).

10. The axial-flow ventricular assist pump with extracorporeal power supply according to claim 1, characterized in that: The driving shaft (9) and the driven shaft (6) are both flexible shafts, and the flexibility of the flexible shaft is not due to the flexibility of the material, but due to the structure being in the shape of a spring.

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