CN219764290U

CN219764290U - Magnetic suspension ventricular assist device

Info

Publication number: CN219764290U
Application number: CN202321010167.7U
Authority: CN
Inventors: 康环; 黄霖; 蒋海洋
Original assignee: Shanghai Xinhengrui Medical Technology Co ltd
Current assignee: Shanghai Xinhengrui Medical Technology Co ltd
Priority date: 2023-04-28
Filing date: 2023-04-28
Publication date: 2023-09-29
Anticipated expiration: 2033-04-28

Abstract

The utility model provides a magnetic suspension ventricular assist device, which comprises a shell, a rotor assembly and an outlet pipeline; the outlet pipeline is fixedly connected with the shell, and the rotor assembly is provided with a through hole penetrating along the rotation axis of the rotor assembly; one end of the outlet pipeline is inserted into the through hole, and the other end of the outlet pipeline protrudes to the outside of the shell and is used for being inserted into a preset position; the outlet line is used to direct fluid exiting the rotor assembly to a predetermined location. The device pumps blood into main artery directly through outlet pipe, need not to implant artificial blood vessel between ventricular assist device and the aorta to avoid artificial blood vessel supply shortage and take place the influence that the inefficacy brought to ventricular assist device's research and development and use, still can reduce ventricular assist device's manufacturing cost, alleviate patient's economic burden.

Description

Magnetic suspension ventricular assist device

Technical Field

The utility model relates to the technical field of medical equipment, in particular to a magnetic suspension ventricular assist device.

Background

The magnetic suspension ventricular assist device applies work to blood by means of a magnetic suspension centrifugal pump, and the blood is drained from the left ventricle to the aorta through the artificial blood vessel, so that the blood is sent to the whole body. In the existing structure, the blood outflow port of the centrifugal blood pump and the aorta are connected through the artificial blood vessel, the artificial blood vessel production process is very complex, the manufacturing difficulty is very high, and the mature and reliable artificial blood vessel manufacturing technology is only mastered in the hands of a few companies at present. Therefore, vascular prostheses are expensive and have extremely low yields, resulting in very short supplies of vascular prostheses worldwide, which can seriously affect the development progress of the product and the supply of the finished product.

In addition, the magnetic suspension ventricular assist device has the advantages that the rotor is suspended and rotated in the pump shell by using a magnetic field, and the rotor and the pump shell are not in mechanical contact, so that the damage to blood is small. The magnetic suspension ventricular assist device has two sets of stator coils, respectively a levitation coil and a drive coil. When the levitation coil is electrified, the permanent magnet in the rotor and the levitation coil form a levitation magnetic circuit, so that the rotor is levitated in the inner cavity of the pump shell under the action of the magnetic levitation force. When the driving coil is electrified, the permanent magnet in the rotor and the driving coil form a driving rotary magnetic circuit, so that the rotor rotates in the inner cavity of the pump shell under the action of the rotating force. In the existing structure, the driving coil and the suspension coil share an iron core (shown in fig. 1), and the suspension magnetic circuit and the driving rotating magnetic circuit all pass through the shared iron core, so that the suspension magnetic circuit and the driving rotating magnetic circuit can be coupled and mutually influenced, the control system is very complex, the research and development difficulty of the magnetic suspension motor is high, and the research and development period is long.

Disclosure of Invention

The utility model aims to provide the magnetic suspension ventricular assist device, blood is directly pumped into a main artery through an outlet pipeline, and artificial blood vessels are not required to be implanted between the ventricular assist device and the aorta, so that the influence on the research and development and the use of the ventricular assist device caused by the shortage of supply quantity and the occurrence of failure of the artificial blood vessels is avoided, the production cost of the ventricular assist device is reduced, and the economic burden of a patient is lightened; in addition, the magnetic suspension ventricular assist device is provided with a relatively independent suspension magnetic circuit and a driving rotating magnetic circuit, so that the suspension and rotation of the rotor assembly can be controlled more simply.

In order to achieve the above purpose, the utility model provides a magnetic suspension ventricular assist device, comprising a shell, a rotor assembly and an outlet pipeline; the outlet pipeline is fixedly connected with the shell, and the rotor assembly is provided with a through hole penetrating along the rotation axis of the rotor assembly; one end of the outlet pipeline is inserted into the through hole, and the other end of the outlet pipeline protrudes to the outside of the shell and is used for being inserted into a preset position; the outlet line is for directing fluid exiting the rotor assembly to the predetermined location.

Optionally, the magnetic suspension ventricular assist device includes a suspension coil for suspending the rotor assembly and a driving coil for driving the rotor assembly to rotate, a cavity is formed on a side surface of the housing, and the suspension coil and the driving coil are both fixed in the cavity on the side surface of the housing; the rotor assembly is disposed in an interior space defined by the housing and the outlet conduit and is capable of levitation and rotation within the interior space.

Optionally, the number of the suspension coils is two, the number of the driving coils is one, and the two suspension coils are respectively arranged on two adjacent sides of the driving coils.

Optionally, the rotor assembly includes a rotor outer cover plate and a permanent magnet, the permanent magnet is covered by the rotor outer cover plate, and the levitation coil and the driving coil respectively correspond to the positions of the permanent magnet; the permanent magnet, the driving coil and the levitation coil are all annular in shape, and the central axis of the levitation coil, the central axis of the driving coil and the rotating axis of the permanent magnet are all coincident.

Optionally, the rotor assembly further comprises a blade and a hub, wherein the hub is arranged on the inner side of the rotor outer cover plate; the number of the blades is multiple, the blades are arranged at intervals along the circumferential direction of the hub, one side of each blade is connected with the outer rotor cover plate, and the other side of each blade is connected with the hub.

Optionally, the housing has a fluid inlet, and the outlet conduit forms a fluid outlet at an end remote from the rotor assembly; the fluid comprises a main flow and a secondary flow, and the path through which the main flow flows is a main flow channel; the space between the rotor outer cover plate and the hub forms a first channel, which is part of the main flow channel;

when the rotor assembly is driven to suspend and rotate in the shell, the main flow is sucked into the rotor assembly from the fluid inlet, flows into the first channel and flows out of the fluid outlet through the through hole penetrated by the rotor assembly after the rotor assembly is subjected to work and pressure boosting through the blades.

Optionally, a second channel is arranged between the rotor outer cover plate and the shell, and a third channel is arranged between the through hole and the outlet pipeline; the secondary stream comprises the following two parts: one part of the air flows through the second channel at the periphery of the rotor outer cover plate and reenters the first channel at the side of the rotor assembly close to the fluid inlet, and the other part of the air flows through the third channel in the through hole and reenters the first channel at the side of the rotor assembly close to the fluid inlet.

Optionally, at a side of the rotor assembly near the fluid inlet, the fluid pressure of the second channel at the outer periphery of the rotor cover plate is higher than the fluid pressure of the first channel at the fluid inlet, and the secondary flow is formed under a pressure difference between the fluid pressure of the second channel at the outer periphery of the rotor cover plate and the fluid pressure of the first channel at the fluid inlet;

the fluid pressure of the third passage in the through hole is higher than the fluid pressure of the first passage at the fluid inlet on the side of the rotor assembly near the fluid inlet, and the secondary flow is formed under a pressure difference between the fluid pressure of the third passage in the through hole and the fluid pressure of the first passage at the fluid inlet.

Optionally, the rotor assembly has connected first and second sections along its own axis of rotation, the first section being closer to the fluid inlet than the second section, the second section having an outer diameter greater than the outer diameter of the first section; the permanent magnets are covered by the rotor outer cover plate in the first section.

Optionally, the bottom of the housing comprises a volute structure, and an outlet end of the volute structure is connected with one end of the through hole far away from the fluid inlet; the main flow is thrown into the volute structure after working and pressurizing of the blades, and flows into the through hole.

The magnetic suspension ventricular assist device provided by the utility model pumps blood into the main artery directly through the outlet pipeline. When in actual implantation, the outlet pipeline is aligned with the aortic valve hole, and the blood flowing out of the outlet pipeline passes through the aortic valve hole and is directly pumped into the main artery, so that artificial blood vessels are not implanted between the ventricular assist device and the aorta, the influence of shortage of supply quantity and failure of the artificial blood vessels on research and development and use of the ventricular assist device is avoided, the production cost of the ventricular assist device is reduced, and the economic burden of a patient is lightened.

In addition, the device can be used for sleeving the driving coil and the suspension coil outside the rotor assembly respectively and independently so as to form a relatively independent suspension magnetic circuit and a relatively independent driving rotating magnetic circuit, so that the motor can decouple the suspension control and the driving control of the rotor assembly, the suspension state and the rotating state of the rotor assembly can be controlled and regulated more simply and conveniently, the research and development period of the ventricular assist device can be shortened, the research and development difficulty of the ventricular assist device can be reduced, and the magnetic levitation motor can be ensured to be always stably and reliably operated and controlled.

Drawings

FIG. 1 is a schematic diagram of an application scenario of a ventricular assist device of the prior art;

fig. 2 is a schematic diagram showing an application scenario of the magnetic suspension ventricular assist device according to a preferred embodiment of the present utility model, wherein a solid line c represents a flow path of blood in a left ventricle, and a dotted line d represents a flow path of blood in an aorta;

FIG. 3 is a schematic cross-sectional view of a magnetic levitation ventricular assist device according to a preferred embodiment of the present utility model, wherein a solid line a represents a main flow path;

FIG. 4 is a schematic cross-sectional view of a rotor assembly according to a preferred embodiment of the present utility model, wherein a solid line a represents a primary flow path;

FIG. 5 is a schematic view showing blood flow in a rotor assembly according to a preferred embodiment of the present utility model, wherein a solid line a represents a primary flow path and a broken line b represents a secondary flow path;

FIG. 6 is a schematic view showing a partial cross-sectional structure of a magnetic levitation ventricular assist device according to a preferred embodiment of the present utility model, wherein a solid line a represents a main flow path;

fig. 7 is a schematic cross-sectional view of a magnetic suspension ventricular assist device according to another preferred embodiment of the present utility model, wherein a solid line a represents a main flow path and a solid line e represents a flow path of blood in a volute structure.

Reference numerals are described as follows:

a left ventricle 100; the aorta 200; aortic valve orifice 300;

a pump housing 110; a levitation coil 120; a driving coil 130; a core 140; a permanent magnet 150; a vascular prosthesis 160; a volute 170;

a ventricular assist device 10; a housing 1; a rotor assembly 2; a rotor outer cover plate 21; a permanent magnet 22; a blade 23; a hub 24; a through hole 25; a first section 26; a second section 27; a levitation coil 3; a driving coil 4; an outlet line 5; a fluid inlet 6; a fluid outlet 7; a volute structure 8; and a guide cone 9.

Detailed Description

The utility model is described in further detail below with reference to the drawings and the specific examples. The advantages and features of the present utility model will become more apparent from the following description. It should be noted that the drawings are in a very simplified form and are all to a non-precise scale, merely for convenience and clarity in aiding in the description of embodiments of the utility model.

The terms "center," "longitudinal," "transverse," "length," "width," "thickness," "upper," "lower," "front," "rear," "left," "right," "vertical," "horizontal," "top," "bottom," "inner," "outer," "clockwise," "counter-clockwise," "axial," "radial," "circumferential," etc. refer to an orientation or positional relationship based on that shown in the drawings, merely for convenience of description and to simplify the description, and do not indicate or imply that the devices or elements referred to must have a particular orientation, be constructed and operated in a particular orientation, and therefore should not be construed as limiting the utility model.

In the present utility model, unless explicitly specified and limited otherwise, the terms "mounted," "connected," "secured," and the like are to be construed broadly and include, for example, either fixedly attached, detachably attached, or integrally formed; may be mechanically connected, may be electrically connected or may be in communication with each other; either directly, or through an intermediary, may be internal to the two elements or in an interactive relationship with the two elements, unless explicitly defined otherwise. The specific meaning of the above terms in the present utility model can be understood by those of ordinary skill in the art according to the specific circumstances. In the description of the present utility model, "plurality" means at least two, for example, two or three or more, etc.

As shown in fig. 1, in the conventional ventricular assist device, a blood outflow port of a centrifugal blood pump and an aorta are connected by an artificial blood vessel 160, and the artificial blood vessel production process is very complicated, the manufacturing difficulty is very high, and the mature and reliable artificial blood vessel manufacturing technology is only known in the hands of a few companies. Therefore, vascular prostheses are expensive and have extremely low yields, resulting in very short supplies of vascular prostheses worldwide, which can seriously affect the development progress of the product and the supply of the finished product.

To solve the above problems, the present utility model provides a magnetic levitation ventricular assist device that pumps blood directly into the main artery 200 through the outlet line 5. In actual implantation, the outlet line 5 is aligned with the aortic valve orifice 300, and the blood exiting the outlet line 5 is pumped directly into the main artery 200 through the aortic valve orifice 300, thus eliminating the implantation of an artificial blood vessel between the ventricular assist device 10 and the main artery 200.

The utility model will now be described in detail with reference to the drawings and a preferred embodiment. The following embodiments and features of the embodiments may be complemented or combined with each other without conflict.

As shown in fig. 2, a preferred embodiment of the present utility model provides a magnetically levitated ventricular assist device 10 (hereinafter ventricular assist device 10), the ventricular assist device 10 being adapted to be implanted in a patient's apex to replace or assist in pumping blood by the heart. When the ventricular assist device 10 is implanted in the apex of the left ventricle 100, blood in the left ventricle 100 can be continuously delivered into the aorta 200 of the human body by pressurization after being sucked into the ventricular assist device 10.

As shown in fig. 2 to 6, the ventricular assist device 10 includes a housing 1, a rotor assembly 2, and an outlet pipe 5, the outlet pipe 5 being fixedly connected to the housing 1, the rotor assembly 2 having a through hole 25 penetrating along its rotation axis, one end of the outlet pipe 5 being inserted into the through hole 25, the other end protruding to the outside of the housing 1 and being inserted into a predetermined position, the outlet pipe 5 being for guiding fluid flowing out of the rotor assembly 21 to the predetermined position.

It should be understood that the fluid to which the present utility model relates is typically blood and is schematically illustrated with blood, but it is not excluded that the fluid is not blood. It is also understood that the predetermined position refers to the location where the outlet line 5 of the ventricular assist device is to be implanted in the body. When the ventricular assist device 10 is implanted in the left ventricle 100, the predetermined position is to indicate that the orifice line 5 is aligned with the aortic valve orifice 300 of the human body; when the ventricular assist device 10 is implanted in the right ventricle, the predetermined position is to indicate that the orifice tube 5 is aligned with the pulmonary valve orifice of the human body.

Specifically, as shown in fig. 2 and 3, in actual implantation, one end of the outlet tube 5 may be aligned with the aortic valve orifice 300, so that the blood flowing out of the outlet tube 5 is directly pumped into the main artery 200 through the aortic valve orifice 300, thereby supplying the whole body of the patient with blood. When the left ventricle 100 contracts, blood flows into the left ventricle 100, is sucked into the fluid inlet 6 of the ventricular assist device 10, is subjected to work pressurization by the vane 23 of the ventricular assist device 10, and flows out from the fluid outlet 7 of the ventricular assist device 10.

Further, the ventricular assist device 10 further includes a levitation coil 3 for levitating the rotor assembly 2 and a drive coil 4 for driving the rotor assembly 2 to rotate. The side of the housing 1 is provided with a cavity, the levitation coil 3 and the driving coil 4 are both fixed in the side cavity of the housing 1, and the rotor assembly 2 is arranged in an inner space formed by the housing 1 and the outlet pipeline 5 and can levitate and rotate in the inner space.

Further, the levitation coil 3 and the driving coil 4 are sequentially sleeved outside the rotor assembly 2 along the rotation axis of the rotor assembly 2. In the present embodiment, the rotor assembly 2 is disposed coaxially with the housing 1 such that the rotational axis of the rotor assembly 2 coincides with the central axis of the housing 1. Glue is coated outside the suspension coil 3 and the driving coil 4 to play an insulating role, so that short circuit between the suspension coil 3 and the driving coil 4 is avoided; in addition, through outside coating glue, can glue suspension coil 3 and drive coil 4 in the side cavity of casing 1, need not to use the spacing stator coil of iron core. So constructed, the levitation coil 3 and the driving coil 4 do not need to share a common iron core, can form a relatively independent levitation magnetic circuit and a driving rotating magnetic circuit, and can decouple levitation control and driving control of the rotor assembly 2, so that the levitation state and the rotating state of the rotor assembly 2 can be controlled and adjusted more simply, the research and development period of the ventricular assist device 10 can be shortened, the research and development difficulty of the ventricular assist device 10 can be reduced, and stable and reliable operation control of the magnetic levitation motor can be ensured all the time.

As shown in fig. 3, in one embodiment, the number of levitation coils 3 is two, the number of drive coils 4 is one, and the two levitation coils 3 are disposed on two adjacent sides of the drive coils 4 along the rotational axis of the rotor assembly 2, respectively. When the suspension coil is electrified, the permanent magnet and the suspension coil in the rotor form a suspension magnetic circuit, so that radial tension is generated on the rotor, and the rotor is suspended. After the two suspension coils 3 are electrified, two groups of radial pulling forces are generated on the rotor, so that the suspension reliability of the rotor assembly 2 can be improved. Simultaneously, two suspension coils 3 are arranged at intervals on two sides of the driving coil 4, so that two groups of tensile forces born by the rotor assembly 2 have a certain axial distance, and the suspension stability of the rotor assembly 2 is further improved.

Of course, in other embodiments, the number of levitation coils 3 and drive coils 4 may be one or more as desired.

As shown in fig. 3 and 4, the rotor assembly 2 includes a rotor outer cover plate 21 and permanent magnets 22 embedded in an inner cavity of the rotor outer cover plate 21, i.e., the permanent magnets 22 are covered by the rotor outer cover plate 21. The levitation coil 3 and the drive coil 4 respectively correspond to the positions of the permanent magnets 22 in the direction of the rotational axis of the rotor assembly 2.

When the ventricular assist device 10 is not powered, the rotor assembly 2 rests on the bottom wall of the housing 1. When the levitation coil 3 is powered by the control system, the electrified levitation coil 3 can generate magnetic force with the permanent magnet 22, the magnetic force is represented as radial tensile force applied to the permanent magnet 22, and the permanent magnet 22 can levitate in the housing 1. Then, the driving coil 4 is powered by the control system, and the powered driving coil 4 can generate magnetic force with the permanent magnet 22, wherein the magnetic force represents a rotating force of circumferential rotation received by the permanent magnet 22, so that the permanent magnet 22 rotates along the circumferential direction of the permanent magnet according to a preset speed.

In a preferred embodiment, the permanent magnet 22, the driving coil 4 and the levitation coil 3 are all annular in shape, and the central axis of the levitation coil 3, the central axis of the driving coil 4 and the rotation axis of the permanent magnet 22 are all coincident, so that the interaction between the levitation coil 3 and the driving coil 4 and the permanent magnet 22 can be facilitated, and the permanent magnet 22 can rotate in a levitated manner in the housing 1.

As shown in fig. 4, in an example, the permanent magnet 22 is covered by the rotor outer cover plate 21. Specifically, the rotor outer cover plate 21 has a receiving hole penetrating in the circumferential direction thereof in a circumferential direction thereof on a circumferential side wall thereof, and the ring-shaped permanent magnets 22 can be positioned in the receiving hole so that all the permanent magnets 22 are covered by the rotor outer cover plate 21.

Preferably, the total length of the levitation coil 3 and the driving coil 4 along the rotation axis of the rotor assembly 2 is equal to the total length of the permanent magnet 22 along the rotation axis of the rotor assembly 2, so that the overall size of the ventricular assist device 10 can be reduced while minimizing the levitation and driving magnetic paths and enhancing the magnetic force.

As shown in fig. 4, the rotor assembly 2 further includes blades 23 and a hub 24, the hub 24 being disposed inside the rotor outer cover 21, the position of the hub 23 corresponding to the position of the rotor outer cover 21. The number of the blades 23 is plural, the plurality of blades 23 are arranged at intervals along the circumferential direction of the hub 24, each blade 23 is arranged between the rotor outer cover plate 21 and the hub 24, and the blades 23 are arranged at intervals around the circumferential direction between the rotor outer cover plate 21 and the hub 24. Wherein one side of each blade 23 is connected to the rotor outer cover 21 and the other side is connected to the hub 24, such that the rotor outer cover 21, the permanent magnets 22, the blades 23 and the hub 24 form a common rotatable unit.

When the permanent magnet 22 is levitated and rotated in the housing 1 by the levitation coil 3 and the driving coil 4, the rotor assembly 2 composed of the rotor outer cover plate 21, the blades 23 and the hub 24 can levitate and rotate at a high speed in the housing 1 following the permanent magnet 22.

In the present embodiment, the portion of the outlet pipe 5 extending out of the through hole 25 is welded to the inner wall of the housing 1 by a plurality of ribs (e.g., three) to achieve fixation of the outlet pipe 5.

As shown in fig. 3 and 4, the housing 1 has a fluid inlet 6, and the end of the outlet conduit 5 remote from the rotor assembly 2 forms a fluid outlet 7, the fluid outlet 7 being aligned with the aortic valve orifice 300. The opening of the outlet conduit 5 away from the rotor assembly 2 is preferably flared to increase the outer diameter of the fluid outlet 7 of the outlet conduit 5, thereby preventing blood from clogging in the outlet conduit 5.

The fluid includes a main flow and a secondary flow, and the main flow has a main flow passage a and the secondary flow has a secondary flow passage b. The space between the rotor outer cover 21 and the hub 24 forms a first channel (not numbered) which is part of the main flow channel a in which the blades 23 are arranged. When the rotor assembly 2 is driven to float and rotate in the housing 1, the main flow is sucked into the housing 1 from the fluid inlet 6, flows into the first passage and flows out from the fluid outlet 7 after being pressurized by the work of the blades 23.

As shown in fig. 3 and 4, there is a second passage (not numbered) between the rotor outer cover plate 21 and the housing 1, i.e., a gap between the outer wall of the rotor outer cover plate 21 and the inner wall of the housing 1 forms the second passage. A third passage (not numbered) is provided between the through-hole 25 and the outlet pipe 5, i.e. in the portion of the outlet pipe 5 inserted into the through-hole 25, a gap between the inner wall of the through-hole 25 and the outer wall of the outlet pipe 5 forms the third passage. In one example, the width of the third channel (i.e. the radial distance between the outlet conduit 5 and the hub 24) is 0.5mm.

As shown in fig. 5, the secondary stream includes the following two parts: a portion of the second passage passing through the outer periphery of the rotor cover plate 21 and re-entering the first passage at the side of the rotor assembly 2 near the fluid inlet 6 to form a secondary flow path b; another part passes through the third passage of the inner wall of the through hole 25 and re-enters the first passage at the side of the rotor assembly 2 close to the fluid inlet 6 to form another secondary flow path b. The secondary flow, after re-entering the first channel, can be boosted again by the blade 23 and then flows out of the fluid outlet 7.

As shown in fig. 5, on the side of the rotor assembly 2 near the fluid inlet 6, the fluid pressure of the second channel at the outer periphery of the rotor outer cover plate 21 is higher than the fluid pressure of the first channel at the fluid inlet 6, and a secondary flow is formed under the pressure difference between the fluid pressure of the second channel at the outer periphery of the rotor outer cover plate 21 and the fluid pressure of the first channel at the fluid inlet 6;

on the side of the rotor assembly 2 close to the fluid inlet 6, the fluid pressure of the third channel of the inner wall of the through hole 25 is higher than the fluid pressure of the first channel at the fluid inlet 6, and a secondary flow is formed under the pressure difference between the fluid pressure of the third channel of the inner wall of the through hole 25 and the fluid pressure of the first channel at the fluid inlet 6. The secondary flow is re-introduced into the primary flow passage a through the outer periphery of the rotor cover plate 21 and the inner wall of the through hole 25.

Since the rotor assembly 2 needs to float and rotate within the housing 1 and the positions of the housing 1 and the outlet pipe 5 are fixed, clearances need to be provided between the rotor assembly 2 and the housing 1 and between the rotor assembly 2 and the outlet pipe 5.

As shown in fig. 4 and 5, the rotor assembly 2 has a first section 26 and a second section 27 connected along its own axis of rotation. The first section 26 is closer to the fluid inlet 6 than the second section 27, the first section 26 of the rotor assembly 2 forming the inflow end of the first channel and the second section 27 of the rotor assembly 2 forming the outflow end of the first channel. The fluid can now flow in from the inflow end of the first channel on the first section 26 and out from the outflow end of the first channel on the second section 27 after being pressurized by the blade 23.

As shown in fig. 4 and 5, as a specific example, the first section 26 and the second section 27 are both of a sleeve structure, the outer diameter of the second section 27 is larger than that of the first section 26, and the first section 26 and the second section 27 are connected by a smooth curved surface. The first section 26 and the second section 27 each comprise a rotor outer cover plate 21, blades 23 and a hub 24, the permanent magnets 22 being covered by the rotor outer cover plate 21 in the first section 26.

By this arrangement, the inner volume of the casing 1 can be fully utilized in the ventricular assist device 10 having a strictly limited size to increase the outer diameter of the blade 23 as much as possible, so that the rotational speed of the blade 23 can be reduced as much as possible while ensuring the required head of the ventricular assist device 10, and the damage to blood caused by the blade 23 during high-speed rotation can be reduced.

It is further preferred that the bottom of the housing 1 of the ventricular assist device 10 comprises a volute structure 8, as shown in fig. 7, the outlet end of the volute structure 8 being connected to the end of the through-hole 25 remote from the fluid inlet 6. The main flow in the first channel is thrown into the volute structure 8 after working and pressurizing through the blades 23, and then flows into the through holes 25.

In the present embodiment, the second section 27 is a volute structure, the outlet end of the volute structure 8 is connected to the end of the through-hole 25 remote from the fluid inlet 6, and blood entering the first section 26 of the first channel through the fluid inlet 6 can be thrown into the second section 27 of the first channel and can flow into the through-hole 25 through the volute structure 8 along the path shown by the solid line e after pressurization, and can then leave the ventricular assist device 10 from the fluid outlet 7.

As shown in fig. 3, in a preferred embodiment, the ventricular assist device 10 further includes a guide cone 9 for guiding the fluid in the direction of the through hole 25, the guide cone 9 is fixedly connected to the side of the housing 1 away from the fluid inlet 6, the guide cone 9 has a tapered outer shape, and the outer circumferential area gradually decreases toward the fluid inlet 6. The flow cone 9 can define the flow direction of the fluid around the rotor assembly 2 after being pressurized by the vane 23, so that the fluid around the rotor assembly 2 can flow in the direction of the through hole 25.

As shown in fig. 2 and 3, the ventricular assist device 10 may be implanted by inserting a portion of the housing 1 and the outlet line 5 into the ventricle by puncturing or removing a portion of the myocardium from the apex of the left ventricle 100 and aligning the fluid outlet 7 of the outlet line 5 with the aortic valve orifice 300. After the ventricular assist device 10 is in place, the levitation coil 3 may be powered by the control system, and the permanent magnet 22 may then drive the entire rotor assembly 2 to levitate within the housing 1. The drive coil 4 of the motor is then supplied with power by the control system, so that the permanent magnet 22 drives the whole rotor assembly 2 to rotate at a high speed in the housing 1 in a suspended manner. After the rotor assembly 2 rotates in a floating manner, blood in the left ventricle 100 can be sucked into the ventricular assist device 10 along a path indicated by a solid line c, and after the blood is subjected to work pressurization, the blood can enter the aorta 200 from the aortic valve orifice 300, and then can flow in the aorta 200 along a path indicated by a dotted line d.

Further, the control system of the ventricular assist device may control the operating state of the ventricular assist device 10 by reading the cardiac electrical signal of the heart. When the ventricle contracts, the control system can control the rotational pumping of the ventricular assist device 10; when the ventricles are relaxed, the control system may control the ventricular assist device 10 to stop the rotary blood pump, thus allowing the ventricular assist device 10 to perform the normal pumping function of the ventricles.

In summary, the magnetic suspension ventricular assist device provided by the utility model pumps blood directly into the main artery through the outlet pipeline. When in actual implantation, the outlet pipeline is aligned with the aortic valve hole, and the blood flowing out of the outlet pipeline passes through the aortic valve hole and is directly pumped into the main artery, so that artificial blood vessels are not implanted between the ventricular assist device and the aorta, the influence of shortage of supply quantity and failure of the artificial blood vessels on research and development and use of the ventricular assist device is avoided, the production cost of the ventricular assist device is reduced, and the economic burden of a patient is lightened.

The above description is only illustrative of the preferred embodiments of the present utility model and is not intended to limit the scope of the present utility model, and any alterations and modifications made by those skilled in the art based on the above disclosure shall fall within the scope of the present utility model.

Claims

1. The magnetic suspension ventricular assist device is characterized by comprising a shell, a rotor assembly and an outlet pipeline; the outlet pipeline is fixedly connected with the shell, and the rotor assembly is provided with a through hole penetrating along the rotation axis of the rotor assembly; one end of the outlet pipeline is inserted into the through hole, and the other end of the outlet pipeline protrudes to the outside of the shell and is used for being inserted into a preset position; the outlet line is for directing fluid exiting the rotor assembly to the predetermined location.

2. A magnetically levitated ventricular assist device as claimed in claim 1 further comprising a levitation coil for levitating the rotor assembly and a drive coil for driving rotation of the rotor assembly, the housing having a cavity on a side thereof, the levitation coil and the drive coil being secured in the cavity on the side of the housing; the rotor assembly is disposed in an interior space defined by the housing and the outlet conduit and is capable of levitation and rotation within the interior space.

3. A magnetic levitation ventricular assist device as claimed in claim 2 wherein the number of levitation coils is two and the number of drive coils is one, the two levitation coils being disposed on opposite sides of the drive coils.

4. A magnetic levitation ventricular assist device as claimed in claim 2 wherein the rotor assembly includes a rotor outer cover plate and a permanent magnet, the permanent magnet being covered by the rotor outer cover plate, the levitation coil and the drive coil respectively corresponding to the position of the permanent magnet; the permanent magnet, the driving coil and the levitation coil are all annular in shape, and the central axis of the levitation coil, the central axis of the driving coil and the rotating axis of the permanent magnet are all coincident.

5. A magnetically levitated ventricular assist device as claimed in claim 4 wherein the rotor assembly further comprises a blade and a hub, the hub being disposed inside the rotor outer cover plate; the number of the blades is multiple, the blades are arranged at intervals along the circumferential direction of the hub, one side of each blade is connected with the outer rotor cover plate, and the other side of each blade is connected with the hub.

6. A magnetically levitated ventricular assist device as claimed in claim 5 wherein the housing has a fluid inlet and the end of the outlet conduit remote from the rotor assembly forms a fluid outlet; the fluid comprises a main flow and a secondary flow, and the path through which the main flow flows is a main flow channel; the space between the rotor outer cover plate and the hub forms a first channel, which is part of the main flow channel;

7. A magnetically levitated ventricular assist device as claimed in claim 6 wherein a second passageway is provided between the rotor outer cover and the housing, and a third passageway is provided between the through-hole and the outlet conduit; the secondary stream comprises the following two parts: one part of the air flows through the second channel at the periphery of the rotor outer cover plate and reenters the first channel at the side of the rotor assembly close to the fluid inlet, and the other part of the air flows through the third channel in the through hole and reenters the first channel at the side of the rotor assembly close to the fluid inlet.

8. A magnetic suspension ventricular assist device as claimed in claim 7 wherein the second passage at the outer periphery of the rotor cover plate has a higher fluid pressure than the first passage at the fluid inlet on a side of the rotor assembly adjacent the fluid inlet, the secondary flow being formed by a pressure difference between the fluid pressure of the second passage at the outer periphery of the rotor cover plate and the fluid pressure of the first passage at the fluid inlet;

9. A magnetically levitated ventricular assist device as claimed in claim 8 wherein the rotor assembly has connected first and second sections along its own axis of rotation, the first section being closer to the fluid inlet than the second section, the second section having an outer diameter greater than an outer diameter of the first section; the permanent magnets are covered by the rotor outer cover plate in the first section.

10. A magnetically levitated ventricular assist device as claimed in claim 9 wherein the bottom of the housing comprises a volute structure, an outlet end of the volute structure being connected to an end of the through-hole remote from the fluid inlet; the main flow is thrown into the volute structure after working and pressurizing of the blades, and flows into the through hole.