Parallel blood pump

Abstract

The application aims to provide a low-speed large-torque parallel blood pump, which comprises a blood flow channel and a pumping unit. One end of the blood flow channel is provided with a blood inflow port, and the other end is provided with a blood outflow port. The pumping unit comprises a foldable impeller and a motor set for driving the foldable impeller to rotate. The motor set comprises a rotating shaft connected with the foldable impeller, and a plurality of motors are circumferentially arranged outside the rotating shaft and jointly drive the rotating shaft to rotate. When the blood pump is used for vascular intervention, the plurality of motors are arranged in series on a track, and the overall diameter is small, so as to avoid damaging the blood vessel. After the intervention is in place, the plurality of motors are assembled into a parallel structure, the torque of the plurality of motors is superimposed on the rotating shaft, and the foldable impeller is jointly driven to rotate. Therefore, the foldable impeller can be larger, and blood is pumped from the blood inflow port into the blood flow channel and discharged from the blood outflow port.

Description

Technical Field

[0001] This invention relates to the field of motor manufacturing technology, and specifically to a parallel blood pump. Background Technology

[0002] Cardiovascular disease can lead to heart failure, characterized by impaired systolic and / or diastolic function of the heart. This results in insufficient pumping of venous blood back to the heart, causing ventricular congestion and inadequate blood perfusion in arterial interventional cardiorenal support systems. Consequently, circulatory disturbances can occur, leading to organ failure and even life-threatening shock. Currently, mechanical circulatory support devices, or blood pumps, exist to assist or replace the heart's pumping function, providing hemodynamic-based life support for cardiogenic shock and acute heart failure.

[0003] A blood pump can be inserted into the patient's heart through blood vessels, allowing blood to flow through the pump and into the arteries. During pumping, the blood flow rate and volume must meet the body's physiological needs. Simultaneously, to prevent damage to blood vessels and related organs, the diameter and length of the blood pump and its impeller are limited, which in turn restricts the pump's torque. Furthermore, the pump's rotational speed should not be too high, otherwise it will damage blood cell structure. With a fixed pump speed, to reduce blood flow rate and increase blood volume, a special design is used after the impeller enters the heart to expand the impeller blades within the heart, increasing the overall size of the impeller. However, the given pump torque cannot drive the enlarged impeller, leading to overheating and potential clotting. Additionally, the complex blade structure is inconvenient to operate and poses safety hazards. Summary of the Invention

[0004] The purpose of this invention is to provide a low-speed, high-torque parallel blood pump.

[0005] To achieve the above objectives, the technical solution adopted by the present invention is as follows: a parallel blood pump, including a blood flow channel and a pumping unit. One end of the blood flow channel is provided with a blood inlet and the other end is provided with a blood outlet. The pumping unit includes a foldable impeller and a motor unit for driving the foldable impeller to rotate. The motor unit includes a rotating shaft connected to the foldable impeller. Multiple motors are circumferentially arranged around the outer circumference of the rotating shaft, and the torques of the multiple motors are superimposed and jointly drive the rotating shaft to rotate.

[0006] The rotating shaft is provided with a support base on its outer periphery, and the two are in a circumferential rotation and axial limiting fit. Multiple motors are mounted on the outer wall of the support base. The motor shaft ends are connected to small transmission wheels, and a large transmission wheel is provided on the rotating shaft. The multiple small transmission wheels drive the large transmission wheel to rotate together.

[0007] The large and small transmission wheels are connected in a non-contact manner. The large transmission wheel has a permanent magnet block on its surface, and the small transmission wheel also has a permanent magnet block on its surface. The permanent magnet blocks on the adjacent surfaces of the large and small transmission wheels have the same magnetic poles.

[0008] The support base is provided with a guide rail at its near end. The guide rail includes multiple rail segments connected in series. Each rail segment is connected by an electromagnet. The motor housing is provided with a guide groove that matches the rail segment. Multiple motors move from the rail segment to the outer wall of the support base. The outer wall of the support base is also provided with a track that matches the guide groove.

[0009] The outer circumference of the pumping unit is equipped with an expandable and contractible bleeding cage. One end of the bleeding cage is fixed to the proximal end of the blood flow channel, and the other end is fixed to a positioning block set on the guide rail section. The proximal end of the positioning block is fixed to the distal end of the catheter. Before assembly, the motor is set on the guide rail section between the positioning block and the support base. The positioning block pushes the motor to move to the distal end while causing the bleeding cage to expand.

[0010] The positioning block is a frustum-shaped cone with a small diameter at the near end and a large diameter at the far end. It has a through-hole for the guide rail to pass through. The end of the hole near the support is an end that can accommodate the tilt of the guide rail. On the side of the positioning block near the guide rail and on the opposite side of the side, there are multiple permanent magnet blocks I and II. Permanent magnet blocks I and II are tilted at the same angle and in opposite directions. The far end face of the positioning block abuts against the near end face of the motor to position the motor connected in parallel.

[0011] The far end of the support is connected to the rotating mechanism, which drives the support to rotate so that the different tracks and guide rails on the outer wall of the support are aligned.

[0012] Multiple permanent magnet blocks three and four are arranged on the side of the track that contacts the motor. Multiple permanent magnet blocks three are arranged adjacent to each other, and multiple permanent magnet blocks four are arranged adjacent to each other. Permanent magnet blocks three and four are tilted at the same angle and in opposite directions. The magnetic poles of permanent magnet blocks three and four are the same as those of permanent magnet blocks one and two at their adjacent ends.

[0013] The bleeding cage comprises a grid-like support body made of shape memory alloy material and a thin film covering the inner and / or outer and / or interlayer of the support body. After being covered by the thin film, it forms a hollow tubular protective peripheral wall structure of the shell. An opening is made in the thin film at the proximal end of the support body to form a blood outflow outlet.

[0014] The foldable impeller includes a rigid hub and blades disposed on the outer periphery of the rigid hub. The shaft extends outward to the outside of the rigid hub to form a protruding section. The protruding section and the fixed ring fixed in the blood flow channel form an axial limiting and circumferential rotational engagement.

[0015] In the above scheme, when the blood pump is inserted through a blood vessel, multiple motors are connected in series on the track. The overall diameter is small to avoid damage to the blood vessel. After the insertion is in place, the multiple motors are assembled into a parallel structure. The torque of the multiple motors is superimposed on the rotating shaft, which drives the foldable impeller to rotate. Therefore, the foldable impeller can be set to be larger, pumping blood from the blood inlet into the blood channel and ejecting it from the blood outlet. Attached Figure Description

[0016] Figure 1 This is a diagram of the blood pump before assembly.

[0017] Figure 2 This is a diagram showing the assembled appearance of the blood pump.

[0018] Figure 3 A schematic diagram of the internal structure of a blood pump before assembly;

[0019] Figure 4 A schematic diagram of the internal structure of a blood pump after assembly;

[0020] Figure 5 for Figure 4 A partially enlarged schematic diagram;

[0021] Figure 6 for Figure 5 Partial structural diagram;

[0022] Figure 7 This is a schematic diagram of the assembled motor unit;

[0023] Figure 8 This is a cross-sectional view of the assembled motor unit;

[0024] Figure 9 This is an outline drawing of the motor housing;

[0025] Figure 10 This is a schematic diagram of the permanent magnet block. Detailed Implementation

[0026] To facilitate understanding, we will first define the terms "proximal" and "proximal" as used below: "proximal" refers to the side closest to the operator / doctor, while "distal" refers to the side furthest from the operator / doctor, i.e., the side closest to the heart. The following will combine these definitions... Figures 1-10 The present invention will be described in further detail below.

[0027] A parallel blood pump includes a blood flow channel 10 and a pumping unit. One end of the blood flow channel 10 has a blood inlet 11, and the other end has a blood outlet 12. The pumping unit includes a foldable impeller 20 and a motor assembly 30 for driving the foldable impeller 20 to rotate. The motor assembly 30 includes a rotating shaft 31 connected to the foldable impeller 20. Multiple motors 32 are circumferentially arranged around the rotating shaft 31, and the torques of the multiple motors 32 are superimposed to drive the rotating shaft 31 to rotate. In other words, the torques of the multiple motors 32 are superimposed on the rotating shaft 31, jointly driving the rotating shaft 31 to rotate the foldable impeller 20. Therefore, the foldable impeller 20 can be made larger, pumping blood from the blood inlet 11 into the blood flow channel 10 and ejecting it from the blood outlet 12.

[0028] As a preferred embodiment of the present invention, such as Figure 7 As shown, a support base 33 is provided on the outer periphery of the rotating shaft 31, and the two form a circumferential rotation and axial limiting fit. Multiple motors 32 are installed on the outer wall of the support base 33. The motor shaft 321 of the motor 32 is connected to a small transmission wheel 322. A large transmission wheel 311 is provided on the rotating shaft 31. Multiple small transmission wheels 322 jointly drive the large transmission wheel 311 to rotate.

[0029] The large transmission wheel 311 and the small transmission wheel 322 engage in a non-contact manner. Permanent magnets are mounted on the surface of both the large and small transmission wheels 311 and 322, with the magnetic poles of the permanent magnets on adjacent surfaces of both wheels being identical. This transmission method is a non-contact magnetic transmission. The permanent magnets on the small transmission wheels 322 move with the motor 32 and interact with the permanent magnets on the large transmission wheels 311, causing the large transmission wheels 311 to rotate. All the small transmission wheels 322 together drive the large transmission wheels 311 to rotate, and the torque is superimposed on the large transmission wheels 311. A flexible polymer film can be fitted over the small transmission wheels 322 and the large transmission wheels 311 to prevent direct contact between the transmission wheels and blood, thus avoiding damage to blood cells during rotation.

[0030] Due to the limited diameter of the blood vessels, the overall diameter of the blood pump during intervention cannot be too large, which restricts the torque of the motor 32. To solve this problem, the present invention employs the following technical solution: a guide rail 40 is provided at the proximal end of the support base 33. The guide rail 40 includes multiple guide rail segments 41 connected in series, and the guide rail segments 41 are connected by electromagnets. The motor 32 housing has guide grooves 323 that are adapted to the guide rail segments 41. Multiple motors 32 move from the guide rail segments 41 to the outer wall of the support base 33. The outer wall of the support base 33 is also provided with tracks 331 that cooperate with the guide grooves 323. Initially, the motors 32 are coaxially mounted on the guide rails 40. When working, multiple motors 32 move through the guide rails 40 to the tracks 331 on the outside of the support base 33, and the motors 32 drive the small transmission wheel 322 to rotate. The cross-sectional structure of the guide rail section 41 resembles an "Ω". The length and number of the guide rail section 41 are the same as those of the motor 32. The sections are connected by magnets, which connect when energized and disconnect when not energized. This design is intended to give the system a certain degree of flexibility when passing through blood vessels, thus avoiding damage to the blood vessels.

[0031] Furthermore, the outer periphery of the pumping unit is equipped with an expandable and retractable bleeding cage 50. One end of the bleeding cage 50 is fixed to the proximal end of the blood flow channel 10, and the other end is fixed to a positioning block 42 provided on the guide rail section 41. The proximal end of the positioning block 42 is fixed to the distal end of the conduit 60. Before assembly, the motor 32 is set on the guide rail section 41 between the positioning block 42 and the support base 33. The positioning block 42 pushes the motor 32 to move distally, causing the bleeding cage 50 to expand. This structure is also the key point of the present invention, that is, during the process of the positioning block 42 pushing the motor 32 to move distally, the bleeding cage 50 also slowly expands, providing sufficient space for the assembly of the motor 32 and the support base 33. After all the motors 32 are assembled, the positioning block 42 can abut against the proximal end of the motor 32 housing, locking the position of the motor 32.

[0032] Specifically, the positioning block 42 is a frustum-shaped cone with a small diameter at the near end and a large diameter at the far end. It has a through irregular hole 421 inside, through which the guide rail 40 passes. The end of the irregular hole 421 near the support base 33 is an end that can accommodate the inclined guide rail 40. On the side of the positioning block 42 near the guide rail 40 and on the opposite side of the side, there are multiple permanent magnet blocks a and b. The permanent magnet blocks a and b are inclined at the same angle and in opposite directions. The far end face of the positioning block 42 abuts against the near end face of the motor 32 to position the motor 32 connected in parallel.

[0033] The distal end of the support base 33 is connected to the rotating mechanism, which drives the support base 33 to rotate so that different tracks 331 on the outer wall of the support base 33 align with the guide rail 40. As the support base 33 rotates, the tracks 331 correspond to the ends of the guide rail 40 and form a track with the guide rail 40. The motor 32 moves to the designated position, thereby realizing the purpose of moving multiple motors 32 to different tracks 331 respectively, and realizing the assembly of the pumping component.

[0034] See Figure 10 Multiple permanent magnet blocks 3c and 4d are arranged on the side of track 331 that contacts motor 32. Permanent magnet blocks 3c and 4d are arranged adjacent to each other. Permanent magnet blocks 3c and 4d are energized in segments for stable drive of motor 32. Permanent magnet blocks 3c and 4d are tilted at the same angle but in opposite directions. The magnetic poles of permanent magnet blocks 3c and 4d are the same as those of permanent magnet blocks 1a and 2b at their adjacent ends. When motor 23 moves towards hose 1, permanent magnet blocks 1a and 3c are energized, while permanent magnet blocks 2b and 4d are not energized. When motor 32 moves towards conduit 60, permanent magnet blocks 2b and 4d are energized, while permanent magnet blocks 1a and 3c are not energized.

[0035] To achieve the expansion and contraction of the bleeding cage 50, the bleeding cage 50 includes a mesh-like support body made of shape memory alloy material and a thin film covering the inner and / or outer and / or interlayer layers of the support body. The thin film also has the characteristic of being expandable and contractable, thus ensuring that it can expand or contract synchronously with the support body while forming a blood channel. After being covered by the thin film, it forms a hollow tubular protective peripheral wall structure. An opening is formed in the thin film at the proximal end of the support body to form a blood outlet 12. The blood outlet 12 is located at the proximal end of the thin film to avoid the existence of a blood recirculation area, that is, blood flows from the blood channel to the nearest end area and then returns to flow out from the blood outlet 12, which would cause energy loss.

[0036] To further improve the stability of the pumping assembly, the foldable impeller 20 includes a rigid hub and blades disposed on the outer periphery of the rigid hub. The rotating shaft 31 protrudes to the outside of the rigid hub to form a protruding section. The protruding section and the fixing ring fixed in the blood flow channel 10 form an axial limiting and circumferential rotational engagement. In this way, the distal end of the pumping assembly is supported by the fixing ring and the proximal end is supported by the catheter 60, making the position of the entire pumping assembly more stable.

[0037] The working process of the blood pump in this invention is as follows:

[0038] Initially, multiple motors 32 are coaxially positioned on guide rail 40, which corresponds to one of the multiple tracks 331. During system movement, adjacent guide rail segments 41 may or may not contact each other. When the entire system needs to be introduced into the body, firstly, the blood pump is inserted into the blood vessel under the constraint of the sheath. Then, the guide rail segments 41 are electromagnetically connected, with their equally spaced adjacent ends contacting each other. Next, the power supply to the permanent magnet block 3c on the guide rail segment 41 is connected, and under the action of the controller, the permanent magnet block generates strong magnets in segments, which interact with the permanent magnet block 1a of the motor 32, pushing multiple motors 32 and positioning blocks 42 step by step along the guide rail 40 towards the track 331 until one end of the motor 32 is placed on the track 331 of the support base 33. Then, the permanent magnet block 3c on the track 331 is energized, causing one motor 32 to move to the predetermined position, and the permanent magnet block 3c is temporarily de-energized. At this time, the bleeding on the side of the positioning block 42 stops. One end of the cage 50 moves with the positioning block 42, causing the bleeding cage 50 to gradually transform from a long cylindrical shape into a lantern shape. Then, the rotating mechanism drives the support base 33 to rotate at a certain angle, so that another positioning track 331 on the support base 33 corresponds to the guide rail 40, so that the next motor 32 can move onto the support base 33, until all the motors 32 have moved to the side of the support base 33 and the positioning block 42 has moved to the end face of the support base 33 and limited the multiple motors 32. At this time, the bleeding cage 50 has formed a lantern shape, and the blood outlet 12 on the bleeding cage 50 becomes larger and faces the aorta. All the motors 32 of the motor group 30 are energized and the speed is controlled by the current. At the same time, the transmission wheel group is energized. At this time, each motor 32 rotates, and the torque of the motor 32 is gathered into the large transmission wheel 311 through the small transmission wheel 322. The large transmission wheel 311 drives the unfolded foldable impeller 20 to pump blood.

[0039] Of course, those skilled in the art will recognize that the present invention is not limited to the details of the exemplary embodiments described above, but also includes the same or similar structures that can be implemented in other specific forms without departing from the spirit or essential characteristics of the invention. Therefore, the embodiments should be considered illustrative and non-limiting in all respects, and the scope of the invention is defined by the appended claims rather than the foregoing description. Thus, all variations falling within the meaning and scope of equivalents of the claims are intended to be included within the present invention. No reference numerals in the claims should be construed as limiting the scope of the claims.

[0040] Furthermore, it should be understood that although this specification describes embodiments, not every embodiment contains only one independent technical solution. This narrative style is merely for clarity. Those skilled in the art should consider the specification as a whole, and the technical solutions in each embodiment can also be appropriately combined to form other embodiments that can be understood by those skilled in the art.

Claims

1. A parallel blood pump comprising a blood flow channel (10) and a pumping unit, one end of the blood flow channel (10) being provided with a blood inflow port (11) and the other end being provided with a blood outflow port (12), characterized in that: The pump unit comprises a foldable impeller (20) and a motor set (30) for driving the foldable impeller (20) to rotate, the motor set (30) comprises a rotating shaft (31) connected with the foldable impeller (20), a plurality of motors (32) are circumferentially arranged on the outer periphery of the rotating shaft (31), and the torques of the plurality of motors (32) are superimposed on each other and jointly drive the rotating shaft (31) to rotate. The rotating shaft (31) is provided with a support seat (33) on the outer periphery and the two are in circumferential rotation and axial limiting fit, the plurality of motors (32) are mounted on the outer wall of the support seat (33), the motor shaft (321) of the motor (32) is connected with a small transmission wheel (322) at the shaft end, the rotating shaft (31) is provided with a large transmission wheel (311), the plurality of small transmission wheels (322) jointly drive the large transmission wheel (311) to rotate. The large transmission wheel (311) and the small transmission wheel (322) are in non-contact fit, the wheel surface of the large transmission wheel (311) is provided with a permanent magnet block, the wheel surface of the small transmission wheel (322) is also provided with a permanent magnet block, and the magnetic poles of the permanent magnet blocks on the wheel surfaces of the large transmission wheel (311) and the small transmission wheel (322) are the same.

2. The parallel blood pump of claim 1, wherein: The proximal end of the support seat (33) is provided with a guide rail (40), the guide rail (40) comprises a plurality of guide rail segments (41) connected in series, the guide rail segments (41) are connected by electromagnets, the motor (32) shell is provided with a guide groove (323) matched with the guide rail segment (41), the plurality of motors (32) are moved from the guide rail segment (41) to the outer wall of the support seat (33), and the outer wall of the support seat (33) is also provided with a track (331) matched with the guide groove (323).

3. The parallel blood pump of claim 2, wherein: The outer peripheral cover of the pump unit is provided with an inflatable and contractible bleeding cage (50), one end of the bleeding cage (50) is fixed to the proximal end of the blood flow channel (10), one end is fixed to the positioning block (42) provided on the guide rail segment (41), the proximal end of the positioning block (42) is fixed to the distal end of the catheter (60), before assembly, the motor (32) is arranged on the guide rail segment (41) between the positioning block (42) and the support seat (33), the positioning block (42) drives the motor (32) to move to the distal end while driving the bleeding cage (50) to expand.

4. The parallel blood pump of claim 3, wherein: The positioning block (42) is in the shape of a truncated cone with a small diameter at the proximal end and a large diameter at the distal end, and is provided with a through-shaped hole (421) in the inside, the shaped hole (421) is for the guide rail (40) to pass through, the end of the shaped hole (421) close to the support seat (33) is an inclined end part for accommodating the guide rail (40), the side of the positioning block (42) close to the guide rail (40) is arranged with a plurality of permanent magnet blocks one (a) and permanent magnet blocks two (b) on the opposite sides, the permanent magnet blocks one (a) and the permanent magnet blocks two (b) are arranged at the same angle and opposite directions, and the distal end surface of the positioning block (42) abuts against the proximal end surface of the motor (32) to position the motor (32).

5. The parallel blood pump of claim 2, wherein: The distal end of the support seat (33) is connected with a rotating mechanism, the rotating mechanism drives the support seat (33) to rotate to align the different tracks (331) on the outer wall of the support seat (33) with the guide rail (40).

6. The parallel blood pump of claim 4, wherein: The side of the track (331) in contact with the motor (32) is respectively arranged with a plurality of permanent magnet blocks three (c) and a plurality of permanent magnet blocks four (d), the plurality of permanent magnet blocks three (c) are arranged adjacent to each other, the plurality of permanent magnet blocks four (d) are arranged adjacent to each other, the permanent magnet blocks three (c) and the permanent magnet blocks four (d) are arranged at the same angle and oppositely inclined, and the magnetic poles of the permanent magnet blocks three (c) and the permanent magnet blocks four (d) are the same as those of the permanent magnet blocks one (a) and the permanent magnet blocks two (b) at adjacent ends.

7. The parallel blood pump of claim 1, wherein: The bleeding cage (50) comprises a grid-shaped stent body made of a shape memory alloy material and a film covering the inner layer and / or the outer layer and / or the interlayer of the stent body, and a hollow tube type protective peripheral wall structure of the shell is formed after the film is covered, and the proximal end of the stent body is provided with an opening to form a blood outlet (12).

8. The parallel flow blood pump of claim 1, wherein: The foldable impeller (20) comprises a rigid hub and blades arranged on the outer periphery of the rigid hub, the rotating shaft (31) protrudes to the outside of the rigid hub to form a protruding section, and the protruding section is axially limited and circumferentially rotated with the fixed ring fixed in the blood flow channel (10).

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