CN116637290A

CN116637290A - parallel blood pump

Info

Publication number: CN116637290A
Application number: CN202310585438.XA
Authority: CN
Inventors: 解启莲; 刘欢; 冯启涛; 李帅康
Original assignee: Anhui Tongling Bionic Technology Co Ltd
Current assignee: Anhui Tongling Bionic Technology Co Ltd
Priority date: 2023-05-23
Filing date: 2023-05-23
Publication date: 2023-08-25

Abstract

The invention aims to provide a parallel blood pump capable of reducing shear stress while meeting pumping flow, which comprises n pumping units and a butting unit, wherein the proximal ends of the pumping units are connected with control wires, the control wires and the butting unit form axial sliding and circumferential rotation fit, the outer walls of the pumping units are provided with guide surfaces forming mutual guide, and the control wires are pulled to drive the pumping units to move to the proximal ends of the pumping units in a specific gesture under the guide action of the guide surfaces so as to be inserted into the butting unit to form a parallel structure. The blood pump is composed of a plurality of pumping units in parallel connection, the pump blood flow of the whole blood pump is equal to the sum of the pump blood flows of n pumping units, so that larger pump blood flow can be provided, the rotating speed of the impeller of the pumping unit is lower, the generated shearing force is smaller, the damage to blood can be reduced, the pumping unit is provided with a guide surface, the self-guide of the pumping unit is completed, the additional guide structure is not needed, and the structure is simple and convenient to operate.

Description

Parallel blood pump

Technical Field

The invention relates to the technical field of medical appliances, in particular to a parallel blood pump.

Background

The occurrence of cardiovascular diseases can lead to heart failure, which is manifested by dysfunction of the systolic function and/or the diastolic function of the heart, and the venous return blood volume can not be fully discharged out of the heart, so that ventricular blood stasis is caused, and the arterial intervention type heart and kidney combined auxiliary system has insufficient blood perfusion, so that the heart blood circulation is impaired, and life hazards such as organ failure, shock and the like are caused. Currently, mechanical circulatory support devices, or blood pumps, are available that assist or replace cardiac pumping to provide life support based on hemodynamic forces for cardiogenic shock and acute heart failure.

The patent named blood pump (publication number: EP4069347A 1) discloses a blood pump, which comprises a motor, wherein the far end of the motor is connected with an impeller, the periphery of the impeller is sleeved with a blood flow channel, the near end of the blood flow channel is a blood inflow port, the periphery of the far end of the blood flow channel is provided with a blood outflow port, and the motor drives the impeller to rotate so as to pump blood in a blood vessel to the downstream. Since the blood pump is inserted far (via the femoral or axillary arteries, as the case may be), the size of the blood pump is significantly limited, i.e. the size of structures that travel through the patient's blood vessels is limited to be only slightly larger than those of the structures themselves, since those vessels can only stretch a limited amount before they are damaged. This means that the actual physical size of the blood pump (including the motor) is limited. Thus, in order for the blood pump to provide a sufficient amount of blood flow to adequately assist the patient's heart, the impeller of the blood pump must be rotated at a very high speed (typically the higher the rotational speed of the impeller, the more blood the pump will pump). However, such high impeller speeds create large shear stresses on the pumped blood elements, resulting in platelet activation, von willebrand factor multimer destruction, erythrocyte destruction, and thrombosis, possibly even resulting in embolic stroke or pump thrombosis.

Disclosure of Invention

The invention aims to provide a parallel blood pump which can meet the pumping flow and simultaneously reduce the shearing stress.

In order to achieve the above purpose, the technical scheme adopted by the invention is as follows: the parallel blood pump comprises n pumping units and a butting unit, wherein the proximal ends of the pumping units are connected with control wires, the control wires and the butting unit form axial sliding and circumferential running fit, guide surfaces forming mutual guide are arranged on the outer walls of the pumping units, and the pumping units are driven by the control wires to move to the proximal ends of the pumping units in a specific gesture under the guiding action of the guide surfaces to be inserted into the butting unit to form a parallel structure.

The pumping unit comprises a motor, a rotating shaft of the motor protrudes towards the far end and is connected with an impeller, a blood flow channel is arranged on the periphery of the impeller, and the guide surface is arranged on the outer surface of the blood flow channel and/or the motor shell.

The guiding surfaces are provided with electromagnetic magnetic attraction elements, and the guiding surfaces of two adjacent pumping units are attracted with each other under the condition of electrification.

The blood flow channel and the outer surface of the motor shell are provided with guide surfaces, the guide surfaces are two planes cut by the cylindrical outer surface, and the included angle between the two planes is theta=360 degrees/n.

The electromagnetic magnetic attraction element is arranged inside the guide surface of the blood flow channel.

The blood pump comprises 3 pumping units, and the included angle between two planes of the guide surface is θ=120°.

The butt joint unit comprises a straight pipe section with a proximal end connected with the catheter, and a storage part with a distal end in limit fit with the pumping unit, wherein the storage part comprises a storage surface matched with the proximal end of the pumping unit in shape, and a guide hole for a control line to pass through is formed in the storage surface.

The external diameter of the containing part is larger than the external diameter of the straight pipe section and is connected with the straight pipe section in a smooth way, the axes of the guide holes and the axes of the straight pipe section are arranged in an included angle mode, and the 3 guide holes are gradually closed from the far end to the near end.

The control line outside cladding of pumping unit proximal end department has the stereoplasm outer tube, and the distal end and the pumping unit proximal end fixed connection of stereoplasm outer tube and two parallel arrangement, and the external diameter of stereoplasm outer tube coincides with the aperture of guiding hole, and the stereoplasm outer tube inserts and constitutes fixed connection in the guiding hole.

The section of the proximal ends of the pumping units is gradually reduced, gaps are formed among the proximal ends of the 3 pumping units, and the containing part is clamped in the gaps surrounded by the proximal ends of the 3 pumping units and forms a closed structure.

A fixed seat is arranged in the straight pipe section, the whole fixed seat is a cylindrical cushion block, the outer diameter of the cushion block is identical with the inner diameter of the straight pipe section, 3 through holes for a control line to pass through are formed in the middle of the cushion block, and the positions of the 3 through holes are in one-to-one correspondence with the guide holes.

The fixing base is provided with a plurality of fixing seats at intervals in the straight pipe section.

The docking unit is provided with an anchoring unit, the anchoring unit can radially expand/contract, and the anchoring unit contracts and wraps the periphery of the blood pump in a constrained mode; in the unconstrained configuration, the anchoring unit radially expands and anchors against the inner wall of the vessel adjacent the blood pump.

The anchoring unit is an elastic support net with a proximal end fixedly connected with the docking unit and an open distal end, the proximal end of the elastic support net surrounds the periphery of the docking unit in a conical shape, and the elastic support net is in a horn shape/funnel shape/bell shape with the opening facing the distal end in a constraint releasing state.

The blood flow channel is a tubular body, a gap is reserved between the impeller and the inner wall of the tubular body, a blood inlet is formed by the open far end of the tubular body, the proximal end of the tubular body is fixedly connected with the motor shell, and a plurality of blood outlets are formed on the peripheral wall of the tubular body close to the proximal end.

The blood outlet is arranged on the circular arc-shaped wall of the avoidance guide surface, and the rotation directions of the blood outlets of the 3 pumping units are consistent.

The scheme at least has the following beneficial effects:

1. the blood pump is formed by connecting a plurality of pumping units in parallel, and the pump blood flow of the whole blood pump is equal to the sum of the pump blood flows of the 3 pumping units, so that larger pump blood flow can be provided, and the pump blood requirement is met.

2. On the premise of meeting the requirement of the blood flow of the pump, the impeller of the pumping unit has lower rotating speed, and the generated shearing force is smaller, so that the damage to the blood can be reduced.

3. During intervention and taking out, each pumping unit of the blood pump can be arranged in a staggered manner in the axial direction, so that the outer diameter of the whole pump body is reduced, and the damage to blood vessels is reduced.

4. The pumping unit is provided with the guide surface, so that the self-guiding of the pumping unit is finished, the additional guide structure is not needed, and the structure is simple and the operation is simple.

5. The electromagnetic magnetic attraction element is arranged at the guide surface, so that 3 pumping units can be attracted together, and the running stability of the blood pump is ensured.

6. The periphery at the pump body is provided with the anchor unit for the position of blood pump is placed in the middle, and in the course of the work, the position of blood pump can not change, improves the auxiliary efficiency of blood pump.

Drawings

FIG. 1 is a schematic view of a blood pump with axial misalignment;

FIG. 2 is a schematic view of the structure of the blood pump after assembly;

FIG. 3 is a perspective view of a docking unit;

FIG. 4 is a cross-sectional view of 3 blood flow channels in an assembled state;

fig. 5 is a schematic structural diagram of the fixing base and the control line.

Detailed Description

For ease of understanding, we first define the orientations referred to hereinafter: "proximal", "proximal" refers to the side proximal to the operator/physician and "distal" refers to the side distal to the operator/physician, i.e., the side proximal to the heart, as discussed in further detail below in connection with fig. 1-5.

As shown in fig. 1 and 2, a parallel blood pump includes n pumping units 10 and a docking unit 20, a control line 30 is connected to the proximal end of the pumping unit 10, the control line 30 and the docking unit 20 form an axial sliding and circumferential running fit, a guiding surface a forming a mutual guiding is arranged on the outer wall of the pumping unit 10, and the pumping unit 10 is driven by the control line 30 to move to the proximal end of the pumping unit 10 in a specific gesture under the guiding action of the guiding surface a, so that the proximal end of the pumping unit 10 is inserted into the docking unit 20 to form a parallel structure. Because the control line 30 and the docking unit 20 form axial sliding and circumferential running fit, in the process of intervention, the pumping units 10 are mutually staggered in the axial direction, and adjacent pumping units 10 do not have overlapping parts in the axial direction, so that the outer diameter of the whole blood pump is smaller, and the outer diameter of only one pumping unit 10 is approximately larger, or is slightly larger than the outer diameter of one pumping unit 10, thereby ensuring that the blood pump can be easily inserted into the body from a blood vessel; after the n pumping units 10 and the docking unit 20 are all interposed in place, the control line 30 is pulled from the outside, the n pumping units 10 are assembled to the docking unit 20 to form the blood pump, and the pumping flow of the blood pump device having the plurality of pumping units 10 operated in parallel is equal to the sum of the pumping flows of the n pumping units 10, so that the required blood flow can be provided, and the rotational speed of the pumping unit 10 is much smaller when the two pumping flows are the same as compared with the blood pump having only one pumping unit, so that the impeller 12 generates much smaller shearing stress and maintains reliability and durability.

More importantly, the outer wall of the pumping unit 10 is provided with guiding surfaces a forming mutual guiding, and limiting and positioning are performed through the structure of the pumping unit 10, so that the pumping unit 10 can be gradually guided and assembled on the docking unit 20 in a specific posture in the assembling process, namely, in the process of pulling the control line 30 to drive the pumping unit 10 to move proximally, and the proximal ends of the n pumping units 10 are constrained by the docking unit 20, so that the assembled pumping units 10 are tightly attached, and the outer diameter of the whole blood pump is small.

Preferably, the pumping unit 10 comprises a motor 11, a rotating shaft of the motor 11 protrudes distally and is connected with an impeller 12, a blood flow channel 13 is covered on the periphery of the impeller 12, and the guiding surface a is arranged on the outer surface of the blood flow channel 13 and/or a shell of the motor 11. Three schemes are included herein: the first scheme is that the guide surface a is only arranged on the outer surface of the blood flow channel 13, and the outer surface of the shell of the motor 11 is cylindrical; in the second scheme, the guide surface a is only provided with the outer surface of the shell of the motor 11, and the outer surface of the blood flow channel 13 is cylindrical; in the third scheme, the blood flow channel 13 and the outer surface of the motor 11 shell are provided with guide surfaces a. Here, the third preferred embodiment can improve the guiding accuracy between the pumping units 10.

Considering that the axial and radial positions of the pumping units 10 are required to be stable in the blood pumping process, the hemolysis is reduced, and meanwhile, the stability of the blood flow of the pump is maintained, so that the electromagnetic magnetic attraction elements are arranged on the guide surfaces a, and the guide surfaces a of two adjacent pumping units 10 are attracted to each other under the electrifying condition, so that the positions among the pumping units 10 are restrained in the axial direction and the radial direction, and the proximal ends of the pumping units 10 are fixedly connected with the butting units 20, so that the stability of the position and the posture of the whole blood pump in the operation process is ensured, and the hemolysis is reduced while the stability of the blood of the pump is ensured. The electromagnetic type magnetic attraction elements are arranged on the guide surface a, the electromagnetic type magnetic attraction elements are not electrified in the intervention, assembly and extraction processes of the pumping units 10, the independent movement of each pumping unit 10 is facilitated, after each pumping unit 10 is assembled in place, the electromagnetic type magnetic attraction elements are electrified, and the pumping units 10 are mutually attracted to form an integral structure, so that the position is stable.

The outer surfaces of the blood flow channel 13 and the motor 11 casing are both provided with a guiding surface a, as in the third scheme, the guiding surface a is two planes cut by the cylindrical outer surface, the included angle between the two planes is θ=360 °/n, or the guiding surface a is two adjacent surfaces of a cylindrical circumscribed polygon, and the two planes are used as the guiding surfaces a between the pumping unit 10 and the pumping units 10 on the left side and the right side, so as to realize the assembly of the pumping unit 10.

In order to reduce the influence on the magnetic field of the motor 11 itself, the electromagnetic magnetic attraction element is disposed inside the guide surface a of the blood flow channel 13, so that the attraction effect is achieved, and the basic performance of the motor 11 is not affected. The distal end of each pumping unit 10 is restrained by an electromagnetic magnetic attraction element, and the proximal end is restrained by a butt joint unit 20, so that the structure of the whole pump body is stable and reliable.

Preferably, the blood pump comprises 3 pumping units 10 in total, and the included angle between the two planes of the guiding surface a is θ=120°, as shown in fig. 4. The reason for selecting 3 pumping units 10 is as follows: 1. on the premise of meeting the requirement of the blood flow of the pump, the rotating speed of the 3 pumping units is obviously reduced, and the hemolysis condition meets the requirement; 2. based on the stability of the triangle, when the 3 pumping units 10 are combined together, the structure is the most stable and reliable; 3. after the guide surfaces a of the 3 pumping units 10 are enclosed together, the guide surfaces a of the pumping units 10 are closely attached, no gap exists in the middle, blood does not enter, and the thrombus phenomenon is avoided.

Further, referring to fig. 3, the docking unit 20 includes a straight tube section 21 with a proximal end connected to the catheter 40, and a receiving portion 22 with a distal end in a limit fit with the pumping unit 10, where the receiving portion 22 includes a receiving surface 221 matching with the proximal end of the pumping unit 10, and a guiding hole 222 for the control wire 30 to pass through is formed at the receiving surface 221.

Since the receiving portion 22 is to be simultaneously matched with the proximal ends of the 3 pumping units 10, the sections thereof need to be set larger, the outer diameter of the receiving portion 22 is larger than the outer diameter of the straight tube section 21, and the two portions are smoothly connected, the axis of the guide hole 222 and the axis of the straight tube section 21 are arranged in an included angle, and the 3 guide holes 222 are gradually closed from the distal end to the proximal end, and then are retracted into the straight tube section 21 at the proximal end.

In order to further enhance the restraining effect of the docking unit 20 on the pumping unit 10, the control wire 30 at the proximal end of the pumping unit 10 is externally coated with a hard outer tube 31, the distal end of the hard outer tube 31 is fixedly connected with the proximal end of the pumping unit 10 and is arranged in parallel with the proximal end of the pumping unit, the outer diameter of the hard outer tube 31 is matched with the aperture of the guide hole 222, and the hard outer tube 31 is inserted into the guide hole 222 to form fixed connection. Due to the presence of the rigid outer tube 31, the proximal end of the pumping unit 10 is firmly fixed to the docking unit 20, ensuring stability of the blood pump during operation, and the rigid outer tube 31 needs to be pushed out of the guide hole 222 with a small effort during removal.

The section of the proximal ends of the pumping units 10 is gradually reduced, gaps are formed among the proximal ends of the 3 pumping units 10, and the containing part 22 is clamped in the gaps surrounded by the proximal ends of the 3 pumping units 10 and forms a closed structure. That is, the proximal section of the pumping unit 10 is varied and cooperates with the receiving portion 22 to provide a space for the receiving portion 22 to be added, and to be transitionally engaged with the straight tube section 21, and the proximal ends of the 3 pumping units 10 form a closed structure around the receiving portion 22, so that blood can be prevented from entering the gap and thrombus can be prevented from forming.

The inside of the straight pipe section 21 is provided with a fixed seat 23, as shown in fig. 5, the fixed seat 23 is integrally provided with a cylindrical cushion block, the outer diameter of the cushion block is matched with the inner diameter of the straight pipe section 21, and the middle part of the cushion block is provided with 3 through holes 231,3 through holes 231 for the control line 30 to pass through, and the positions of the through holes 231 are arranged in one-to-one correspondence with the guide holes 222. The advantage of this arrangement is that it ensures that the control lines 30 are used on the same straight line, and therefore the corresponding pumping unit 10 can be pulled into the corresponding receiving surface in a particular attitude, completing accurate assembly.

Preferably, a plurality of fixing seats 23 are arranged in the straight pipe section 21 at intervals.

The docking unit 20 is provided with an anchoring unit 50, the anchoring unit 50 can radially expand/contract, and in a constrained mode, the anchoring unit 50 contracts and wraps the periphery of the blood pump; in the unconstrained configuration, the anchoring unit 50 radially expands and anchors against the inner wall of the vessel adjacent the blood pump. Blood pump during transvascular interventions, it is necessary to resort to constraining members (most commonly sheaths) which are arranged outside the expandable anchoring unit 50 to constrain the anchoring unit 50 in a constrained configuration for delivery of the anchoring unit 50. After the operation, the constraining member is still used in the process of withdrawing the blood pump from the body, the expanding anchor unit 50 is retracted to the inside of the constraining member to be in a contracted constraining form, and the blood pump is withdrawn to the outside along with the blood pump, so that the damage to the blood vessel is avoided.

The anchoring unit 50 is an elastic support net with a proximal end fixedly connected with the docking unit 20 and an open distal end, the proximal end of the elastic support net is conical and surrounds the periphery of the docking unit 20, and in the constraint releasing mode, the elastic support net is in a horn shape/funnel shape/bell shape with the opening facing the distal end. In the intervention process of the blood pump, the elastic support net is arranged in the sheath tube to be contracted, and at the moment, the external diameter of the elastic support net is small, so that the intervention of the blood pump is not influenced; after the blood pump reaches the designated position, the sheath tube is withdrawn, the restriction on the elastic support net is released, and the elastic support net is expanded and supported on the inner wall of the blood vessel, so that the position of the blood pump is fixed. Because the elastic support net is cone-shaped, the sheath can be easily retracted when withdrawn, and the blood vessel is not damaged; the shape of the distal end of the elastic support net can be regarded as bell shape/horn shape/funnel shape, when the constraint is released, the main body of the elastic support net naturally expands, and the distal end of the elastic support net needs to be round and smooth, so that the damage to the inner wall of the blood vessel is avoided. The position of the blood pump is centered, and in the working process, the position of the blood pump cannot change, so that the auxiliary efficiency of the blood pump is improved.

Further, the blood flow channel 13 is a tubular body, a gap is reserved between the impeller 12 and the inner wall of the tubular body, a blood inlet 131 is formed by the open distal end of the tubular body, the proximal end of the tubular body is fixedly connected with the housing of the motor 11, and a plurality of blood outlets 132 are formed on the outer peripheral wall of the tubular body adjacent to the proximal end.

In the assembled state, the guide surfaces a of the 3 pumping units 10 are mutually attached, so that the blood outlet 132 is not required to be arranged on the guide surface a, the blood outlet 132 is arranged on the circular arc-shaped wall of the avoidance guide surface a, the rotation directions of the blood outlets 132 of the 3 pumping units 10 are consistent, the blood pumped from the blood outlets 132 of the different pumping units 10 is prevented from mutually colliding, the blood flow rate is reduced while the blood is damaged, and the pumping effect is not facilitated.

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

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

Claims

1. A parallel blood pump, characterized in that: the device comprises n pumping units (10) and a butt joint unit (20), wherein the proximal end of the pumping unit (10) is connected with a control line (30), the control line (30) and the butt joint unit (20) form axial sliding and circumferential running fit, a guide surface (a) forming mutual guide is arranged on the outer wall of the pumping unit (10), the pumping unit (10) is driven by the control line (30) to move to the proximal end of the pumping unit (10) in a specific gesture under the guide action of the guide surface (a), and the proximal end of the pumping unit (10) is inserted into the butt joint unit (20) to form a parallel structure.

2. The parallel blood pump of claim 1, wherein: the pumping unit (10) comprises a motor (11), a rotating shaft of the motor (11) protrudes towards the far end and is connected with an impeller (12), a blood flow channel (13) is arranged on the periphery of the impeller (12), and a guide surface (a) is arranged on the outer surface of the blood flow channel (13) and/or a shell of the motor (11).

3. The parallel blood pump of claim 2, wherein: the guiding surfaces (a) are provided with electromagnetic magnetic attraction elements, and the guiding surfaces (a) of two adjacent pumping units (10) attract each other under the condition of electrifying.

4. The parallel blood pump of claim 2, wherein: the blood flow channel (13) and the outer surface of the motor (11) shell are both provided with a guide surface (a), the guide surface (a) is two planes cut out by the cylindrical outer surface, and the included angle between the two planes is theta=360 degrees/n.

5. A parallel blood pump according to claim 3, wherein: the electromagnetic magnetic attraction element is arranged inside the guide surface (a) of the blood flow channel (13).

6. The parallel blood pump of claim 4, wherein: the blood pump comprises 3 pumping units (10), and the included angle between two planes of the guide surface (a) is theta=120°.

7. The parallel blood pump of claim 1, wherein: the butt joint unit (20) comprises a straight pipe section (21) with the proximal end connected with the catheter (40) and a containing part (22) with the distal end in limit fit with the pumping unit (10), the containing part (22) comprises a containing surface (221) which is anastomotic with the proximal end of the pumping unit (10), and a guide hole (222) for a control line (30) to pass through is formed in the containing surface (221).

8. The parallel blood pump of claim 7, wherein: the outer diameter of the containing part (22) is larger than that of the straight pipe section (21) and the two parts are connected in a smooth way, the axes of the guide holes (222) and the axes of the straight pipe section (21) are arranged in an included angle mode, and the 3 guide holes (222) are gradually closed from the far end to the near end.

9. The parallel blood pump of claim 7, wherein: the control line (30) at the proximal end of the pumping unit (10) is externally coated with a hard outer tube (31), the distal end of the hard outer tube (31) is fixedly connected with the proximal end of the pumping unit (10) and is arranged in parallel, the outer diameter of the hard outer tube (31) is matched with the aperture of the guide hole (222), and the hard outer tube (31) is inserted into the guide hole (222) to form fixed connection.

10. The parallel blood pump of claim 7, wherein: the sections of the proximal ends of the pumping units (10) are gradually reduced, gaps are formed among the proximal ends of the 3 pumping units (10), and the containing part (22) is clamped in the gaps surrounded by the proximal ends of the 3 pumping units (10) to form a closed structure.

11. The parallel blood pump of claim 7, wherein: a fixed seat (23) is arranged in the straight pipe section (21), the fixed seat (23) is integrally a cylindrical cushion block, the outer diameter of the cushion block is identical with the inner diameter of the straight pipe section (21), 3 through holes (231) for a control line (30) to pass through are formed in the middle of the cushion block, and the positions of the 3 through holes (231) are arranged in one-to-one correspondence with the guide holes (222).

12. The parallel blood pump of claim 11, wherein: the fixing seats (23) are arranged in the straight pipe section (21) at intervals.

13. The parallel blood pump of claim 1, wherein: an anchoring unit (50) is arranged on the butt joint unit (20), the anchoring unit (50) can radially expand/contract, and under the constraint mode, the anchoring unit (50) contracts and wraps the periphery of the blood pump; in the unconstrained configuration, the anchoring unit (50) radially expands and anchors against the inner wall of the vessel adjacent the blood pump.

14. The parallel blood pump of claim 13, wherein: the anchoring unit (50) is an elastic support net with a proximal end fixedly connected with the docking unit (20) and an open distal end, the proximal end of the elastic support net is in a conical column shape and surrounds the periphery of the docking unit (20), and the elastic support net is in a horn shape/funnel shape/bell shape with the open distal end under the constraint releasing state.

15. The parallel blood pump of claim 2, wherein: the blood flow channel (13) is a tubular body, a gap is reserved between the impeller (12) and the inner wall of the tubular body, a blood inlet (131) is formed by the open far end of the tubular body, the proximal end of the tubular body is fixedly connected with the shell of the motor (11), and a plurality of blood outlets (132) are formed in the peripheral wall, close to the proximal end, of the tubular body.

16. The parallel blood pump of claim 15, wherein: the blood outlet (132) is arranged on the circular arc-shaped wall of the avoidance guide surface (a), and the rotation directions of the blood outlets (132) of the 3 pumping units (10) are consistent.