CN216366322U

CN216366322U - Ventricular assist device

Info

Publication number: CN216366322U
Application number: CN202122698676.0U
Authority: CN
Inventors: 张家良; 吴婷婷
Original assignee: Magassist Inc
Current assignee: Xinqing Medical Suzhou Co ltd
Priority date: 2021-11-05
Filing date: 2021-11-05
Publication date: 2022-04-26
Anticipated expiration: 2031-11-05

Abstract

The application relates to a ventricular assist device, which comprises a motor, a conduit, a driving shaft and a pump assembly, wherein the pump assembly comprises a pump shell and an impeller accommodated in the pump shell; the impeller comprises a hub and a blade, wherein the blade is provided with a blade root connected to the hub and a blade tip connected with the blade root; the blades are made of flexible materials and have a folding configuration and an unfolding configuration; the blade tip of the blade in the folding configuration is close to the hub, and the blade tip of the blade in the unfolding configuration is far away from the hub; the impeller has a first state in which the blades are driven to rotate in the deployed configuration to pump blood, and a second state in which the blades are driven to rotate in the deployed configuration to pump a fluid medium having a viscous resistance less than that of blood; the diameter of the blade in the first state is larger than that of the blade in the second state, so that the performance of the impeller is guaranteed, failure caused by reverse bending is avoided, the service life of the impeller is prolonged, the stability of the impeller is improved, and the ventricle auxiliary device is high in reliability and good in performance.

Description

Ventricular assist device

Technical Field

The utility model relates to a ventricular assist device, and belongs to the technical field of medical instruments.

Background

The pump assembly of the ventricular assist device disclosed in the prior art is collapsible, wherein the vanes of the impeller of the catheter pump are made of a flexible elastic material to allow collapsing, and the vanes can be self-expanding by release of the collapsing energy storage. When the impeller pumps blood, reverse bending with different degrees occurs because the fluid back pressure of the blood to the blades is larger than the fluid back pressure of the air to the blades.

SUMMERY OF THE UTILITY MODEL

The utility model aims to provide a ventricular assist device with good performance and high reliability.

In order to achieve the purpose, the utility model provides the following technical scheme:

a ventricular assist device of a first aspect of the utility model includes:

a motor;

a conduit;

a drive shaft passing through the catheter, the proximal end being connected to the motor;

a pump assembly, comprising: a pump housing connected to the distal end of the conduit and having an inlet end and an outlet end, an impeller received within the pump housing, a hub of the impeller being connected to the distal end of the drive shaft; the impeller is capable of being driven to rotate so as to suck blood into the pump housing from the inlet end and discharge the blood from the outlet end;

wherein the impeller comprises a blade, a hub connected to the drive shaft, the blade having a blade root connected to the hub, a blade tip connected to the blade root; the blades are made of flexible materials and have a folding configuration and an unfolding configuration; the tip of the blade in the folded configuration is close to the hub, and the tip of the blade in the unfolded configuration is far away from the hub;

wherein the impeller has a first state in which the vanes are driven to rotate in the deployed configuration to pump blood, and a second state in which the vanes are driven to rotate in the deployed configuration to pump a fluid medium having a viscous resistance less than that of the blood;

wherein the diameter of the blade in the first state is greater than the diameter of the blade in the second state.

A ventricular assist device of a second aspect of the present invention includes:

a motor;

a conduit;

wherein the amount of deformation of the blade in the first state in the counter-rotational direction is greater than the amount of deformation of the blade in the second state in the counter-rotational direction.

A ventricular assist device of a third aspect of the utility model includes:

a motor;

a conduit;

wherein the radius of curvature of the blade in the first state is greater than the radius of curvature of the blade in the second state.

Preferably, the direction of curvature of the blades in the first state is the same as the direction of curvature of the blades in the deployed configuration and not driven for rotation.

Preferably, the direction of curvature of the blade in the first state is the same as the direction of curvature of the blade in the second state.

Preferably, the blade in the first state and the blade in the second state are deformed in the reverse rotation direction.

Preferably, the distance between the blade tip and the blade root of the blade in the first state is greater than the distance between the blade tip and the blade root of the blade in the second state.

Preferably, the diameter of the blade in the first state is smaller than the distance between the hub and the pump casing.

Preferably, the shore hardness of the material of the blade is 80A-70D.

Preferably, the blades are helically wound around the hub in at least sections.

Preferably, the blades have a profile with an arc, the curvature of the arc varying in the direction of the axis of the hub.

Preferably, the stiffness of the blade varies along the radial extension of the blade.

Preferably, the stiffness of the blade root is greater than the stiffness of the blade tip.

Preferably, the curvature of the blade varies along the radial extension of the blade.

Preferably, the curvature of the blade increases with increasing distance from the hub.

Preferably, the thickness of the blade decreases with increasing distance from the hub.

The utility model has the beneficial effects that: the diameter of the blade of the impeller of the ventricular assist device is larger than that of the blade of the fluid medium with the pumping viscous resistance smaller than that of the blood when the impeller of the ventricular assist device pumps the blood, so that the performance of the impeller is ensured, the failure caused by reverse bending is avoided, the service life of the impeller is prolonged, the stability of the impeller is improved, and the ventricular assist device is high in reliability and good in performance.

Drawings

FIG. 1 is a perspective view of a ventricular assist device provided by the present invention;

FIG. 2 is another perspective view of a ventricular assist device provided in accordance with the present invention

FIG. 3 is a perspective view of an impeller provided by the present invention;

FIG. 4 is another perspective view of the impeller provided by the present invention;

fig. 5 is a cross-sectional view of a portion of the impeller shown in fig. 3 in the radial direction.

Detailed Description

The present invention will be described in detail below with reference to specific embodiments shown in the drawings. These embodiments are not intended to limit the present invention, and structural, methodological, or functional changes made by those skilled in the art according to these embodiments are included in the scope of the present invention.

The terms "proximal", "posterior" and "distal", "anterior" are used herein with respect to the clinician administering the ventricular assist device of this embodiment. The terms "proximal", "posterior" refer to the portion that is relatively close to the clinician, and the terms "distal", "anterior" refer to the portion that is relatively far from the clinician. For example, the motor is at the proximal and rear ends, and the guard head is at the distal and front ends; for another example, the proximal end of a component/assembly is shown as being relatively close to the motor, while the distal end is shown as being relatively close to the protective head.

The ventricular assist device of the present invention defines an "axial" or "axial extension direction" with the extension direction of the drive shaft. As used herein, the term "inner" and "outer" are used with respect to an axially extending centerline, with the direction toward the centerline being "inner" and the direction away from the centerline being "outer".

It is to be understood that the terms "proximal," "distal," "rear," "front," "inner," "outer," and these terms are defined for convenience of description. However, ventricular assist devices may be used in many orientations and positions, and thus these terms of expressing relative positional relationships are not intended to be limiting and absolute. For example, the above definitions of the directions are only for convenience of illustrating the technical solution of the present invention, and do not limit the directions of the ventricular assist device of the present invention in other scenarios, including but not limited to product testing, transportation, and manufacturing, which may cause the device to be inverted or to change its position. In the present invention, the above definitions shall follow, if any, if they are otherwise explicitly defined and limited.

In the present invention, the terms "connected" and the like are to be understood broadly, unless otherwise explicitly specified or limited. For example, the connection can be fixed connection, detachable connection, movable connection or integration; either directly or indirectly through intervening media, either internally or in any other relationship. The specific meanings of the above terms in the present invention can be understood by those skilled in the art according to specific situations.

In addition, the technical features involved in the different embodiments of the present invention described below may be combined with each other as long as they do not conflict with each other.

Referring to fig. 1 to fig. 4, a ventricular assist device 100 according to an embodiment of the present invention may at least partially assist a blood pumping function of a heart, so as to at least partially reduce a burden on the heart.

In one scenario, the ventricular assist device 100 may be used as a left ventricular assist device, with the pump assembly 3 being insertable into the left ventricle, and the impeller 32 of the pump assembly 3 being operable to pump blood in the left ventricle into the ascending aorta.

Of course, the ventricular assist device 100 may also be used as a right ventricular assist device, with the pump assembly 3 being interposed in the right ventricle, the pump assembly 3 being operative to pump blood in the veins into the right and left ventricles.

The following will be described primarily in the context of the ventricular assist device 100 being used as a left ventricular assist. It will nevertheless be understood that no limitation of the scope of the embodiments of the utility model is thereby intended, as illustrated in the accompanying drawings.

The ventricular assist device 100 includes a motor 1, a catheter 2, a drive shaft (not shown) inserted in the catheter 2 and connected to the motor 1 at a proximal end thereof, and a pump assembly 3. The power transmission between the motor 1 and the impeller 32 of the pump assembly 3 is realized through the driving shaft so as to drive the pump assembly 3 to realize the blood pumping function. The transmission of the motor 1 to the drive shaft may be any suitable known technique, such as magnetic coupling, and will not be described further herein.

In use of the ventricular assist device 100, the pump assembly 3 and the forward end portion of the catheter 2 are fed into and held within the subject, and it is desirable that the pump assembly 3 and the catheter 2 be as small in size as possible. The smaller size of the pump assembly 3 and catheter 2 allows access to the body via the smaller interventional size, reducing the pain to the subject from the interventional procedure and reducing complications due to the oversized interventional procedure.

The drive shaft includes flexible axle and the hard axle that is connected to the flexible axle distal end, and the flexible axle is worn to establish in pipe 2, and the hard axle is worn to establish in the hollow passage of wheel hub 321 of impeller 32, realizes fixedly through the bonding between hard axle outer wall and the hollow passage inner wall.

The pump assembly 3 comprises a frame 313 having proximal and distal ends connected to proximal and distal bearing chambers (not shown) and 5, respectively, in which proximal and distal bearing chambers 5 and proximal and distal bearings (not shown) are provided, respectively. The near end and the far end of the hard shaft are respectively arranged in the near end bearing and the far end bearing in a penetrating way. Thus, the rigid shaft is supported at both ends by two bearings, and the higher rigidity of the rigid shaft allows the impeller 32 to be better retained within the pump casing 31.

The flexible axle is worn to establish in pipe 2, and pipe 2 avoids drive shaft and external contact, ensures the normal work of drive shaft on the one hand, and on the other hand avoids direct contact examinee in the drive shaft working process, causes the injury to the examinee.

At the distal end of the pump assembly 3, in particular the distal bearing chamber 5, a protective head 4 is provided, which is configured to be soft so as not to damage the tissue of the subject, the protective head 4 being made of any material that macroscopically exhibits flexibility. Specifically, the protection head 4 is a flexible protrusion with an arc-shaped or winding end, the flexible end is supported on the inner wall of the ventricle in a non-invasive or non-destructive manner, the suction inlet of the pump assembly 3 is separated from the inner wall of the ventricle, the suction inlet of the pump assembly 3 is prevented from being attached to the inner wall of the ventricle due to the reaction force of the fluid (blood) in the working process of the pump assembly 3, and the effective pumping area is ensured.

As described above, the pump assembly 3, which can be delivered to a desired location of a heart chamber, such as the left ventricle of a heart, through the conduit 2, includes a pump housing 31 connected to the distal end of the conduit 2 and having an inlet end 311 and an outlet end 312, an impeller 32 housed within the pump housing 31.

In the present embodiment, the pump housing 31 includes a holder 313 made of nickel or titanium alloy and having a metal lattice structure, and an elastic coating 314 covering the holder 313. The metal lattice of the stent 313 has a mesh design, the cover 314 covers the middle and rear end portions of the stent 313, and the mesh of the portion of the stent 313 not covered by the cover 314 at the front end forms the inlet end 311. The rear end of the coating 314 covers the distal end of the catheter 2, and the outlet end 312 is an opening formed at the rear end of the coating 314.

Referring to fig. 3 and 4, the impeller 32 includes a hub 321 and blades 322 supported on an outer wall of the hub 321. The blade 322 has a blade root connected to the hub 321, and a blade tip connected to the blade root. The impeller 32 can be driven to rotate to draw blood into the pump housing 31 from the inlet end 311 and discharge the blood from the outlet end 312.

In the present embodiment, the pump assembly 3 is a collapsible pump having a compressed state and an expanded state. Specifically, the pump casing 31 and the impeller 32 are configured to: in a corresponding interventional configuration of the pump assembly 3, is in a compressed state such that the pump assembly 3 is delivered in the vasculature of a subject with a first, smaller outer diameter dimension, and, in a corresponding working configuration of the pump assembly 3, is in an expanded state such that the pump assembly 3 pumps blood at a desired location with a second, larger radial dimension than the first radial dimension.

In the art, the size and hydrodynamic performance of the pump assembly 3 are two conflicting parameters. In short, it is desirable that the pump assembly 3 be small in size from the viewpoint of alleviating pain of the subject and ease of intervention. Whereas a large flow rate of the pump assembly 3 is desirable for providing a strong assisting function to the subject, a large flow rate generally requires a large size of the pump assembly 3.

By providing a collapsible pump assembly 3, the pump assembly 3 has a smaller collapsed size and a larger deployed size, which allows for ease of intervention and ease of pain relief for the subject during the intervention/delivery process, as well as providing a high flow rate.

By the design of the multiple meshes, especially the diamond meshes, of the pump shell 31, folding can be achieved well, and unfolding can be achieved by means of the memory property of the nickel-titanium alloy.

The blades 322 of the impeller 32 are made of a flexible material or a shape memory material, and can be bent with respect to the hub 321 to have a folded configuration and an unfolded configuration. The tips of the blades 322 in the collapsed configuration are proximate to the hub 321 and the tips of the blades 322 in the expanded configuration are distal to the hub 321.

The blades 322 store energy when being folded, and after the external constraint is removed, the energy storage of the blades 322 is released, so that the blades 322 are unfolded.

In the pump assembly 3 corresponding to the intervention configuration, the blades 322 are in a folded configuration, wrapped on the outer wall of the hub 321 and at least partially in contact with the inner wall of the pump casing 31; the blades 322 extend radially outward from the hub 321 and are spaced from the inner wall of the pump assembly 3 when the pump assembly 3 is in the deployed configuration corresponding to the operating configuration.

The pump assembly 3 is folded by means of external restraint, and the pump assembly 3 is self-unfolded after the restraint is removed. In the present embodiment, the "compressed state" refers to a state in which the pump assembly 3 is radially constrained, that is, a state in which the pump assembly 3 is radially compressed to be folded into a minimum radial dimension by the external pressure. The "expanded state" refers to a state in which the pump assembly 3 is not radially constrained, that is, a state in which the bracket 313 and the impeller 32 are expanded radially outward to the maximum radial dimension.

The application of the external restraint described above is accomplished by a folded sheath (not shown) that is slidably fitted over the catheter 2. When the folding sheath tube moves forwards outside the catheter 2, the pump assembly 3 can be integrally contained in the folding sheath tube, and the pump assembly 3 is forcibly folded. When the folded sheath is moved backwards, the radial constraint on the pump assembly 3 is removed and the pump assembly 3 self-expands.

As described above, the folding of the pump unit 3 is performed by the radial restraining force applied by the folded sheath tube, and the impeller 32 included in the pump unit 3 is housed in the pump housing 31. Thus, in essence, the collapsing process of the pump assembly 3 is: the folded sheath exerts a radial restraining force on the pump casing 31, and when the pump casing 31 is radially compressed, a radial restraining force is exerted on the impeller 32.

That is, the pump casing 31 is folded directly by the folding sheath, and the impeller 32 is folded directly by the pump casing 31. As described above, the impeller 32 has elasticity. Therefore, although in the collapsed state, the impeller 32 is collapsed and stored with energy so that it always has a tendency to expand radially, and the impeller 32 contacts the inner wall of the pump housing 31 and exerts a reaction force on the pump housing 31.

After the constraint of the folded sheath is removed, the pump shell 31 supports the elastic coating 314 to unfold under the action of the self memory characteristic, and the impeller 32 automatically unfolds under the action of released energy storage.

The number of the blades 322 may be one or more. In this embodiment, the number of the blades 322 is two, and the two blades 322 are symmetrically distributed at equal intervals. In addition, the plurality of blades 322 connected to the hub 321 may be the same or different, and are not particularly limited herein. The blades 322 are integrally formed, so that a protruding structure caused by connection of parts is avoided, and damage to blood is reduced.

The blades 322 are helically wound around the hub 321, at least in sections. Specifically, the blades 322 extend spirally in the axial direction of the hub 321. The blades 322 are wound in a part of a turn, a full turn or several turns with respect to the rotational axis of the hub 321. Preferably, the blade 322 is wound at least one turn around the hub 321. Due to the design, the contact area of the blades 322 and blood is small, the blood flows according to a natural path for guiding the blood, the thrust of the blades 322 can be reduced by fully utilizing the self thrust of the blood of a human body, and the working efficiency of the impeller 32 is improved.

The blades 322 have a profile with an arc, the curvature of which varies in the direction of the axis of the hub 321. The curvature of the arc line can be gradually increased, or gradually decreased, or first increased and then decreased, or other changing modes, and the curvature can be specifically set according to hydrodynamics.

In a preferred embodiment, the blades 322 have a smaller curvature near the inlet end 311 of the pump casing 31 than near the outlet end 312 of the pump casing 31, which arrangement makes it easier for the impeller 32 to be folded from the deployed configuration to the collapsed configuration.

The curvature of the blades 322 varies along the radial extension of the blades 322. When the blades 322 are in the deployed configuration and the impeller 32 is not driven to rotate, the blades 322 assume a curved configuration. Specifically, the curvature of the blade 322 increases with increasing distance from the hub 321. Thereby reducing the radial size of the impeller 32 and also improving the ability of the impeller 32 to pump blood.

As described above, the blades 322 need to be bent and folded, and in order to enable the blades 322 to be smoothly converted into the folded configuration under the action of an external force, the hardness of the blades 322 needs to be relatively small, so as to reduce the bending and folding difficulty. However, the impeller 32 needs to rotate to pump blood, and the hardness of the blades 322 should be relatively large to ensure the blood pumping capability, and avoid the reverse rotation failure due to the relatively soft blades 322 when the rotation speed of the impeller 32 is too high. In a preferred embodiment, the blades 322 are made of a material having a Shore hardness of 80A-70D to meet the requirement.

It is noted that the above numerical values include all values of lower and upper values that are incremented by one unit from the lower limit value to the upper limit value, and that there may be an interval of at least two units between any lower value and any higher value.

For example, the blades 322 are illustrated as having a Shore hardness of 80A-70D, preferably 83A-67D, more preferably 86A-64D, and even more preferably 89A-61D, for the purpose of illustrating equivalents such as 90A, 95A, 55D, 57D, 58D not expressly enumerated above.

As mentioned above, the exemplary range of 3 intervals does not exclude increases in intervals of appropriate units, such as numerical units of 1, 2, 4, 5, etc. These are only examples of what is intended to be explicitly recited, and all possible combinations of numerical values between the lowest value and the highest value that are explicitly recited in the specification in a similar manner are to be considered.

Unless otherwise indicated, all ranges include the endpoints and all numbers between the endpoints. The use of "about" or "approximately" with a range applies to both endpoints of the range. Thus, "about 20 to 30" is intended to cover "about 20 to about 30", including at least the endpoints specified.

For other definitions of numerical ranges appearing herein, reference is made to the above description and further description is omitted.

Because the blade 322 is bent and folded to have its tip facing the hub 321, the root remains substantially unchanged. In another preferred embodiment, the blade root has a stiffness greater than the blade tip stiffness so that the blade root supports the blade tip in the deployed configuration of the impeller 32, which ensures stability of the blade 322 during rotational operation and better achieves bending of the blade 322.

In a further preferred embodiment, the stiffness of the blades 322 varies along the radial extension of the blades 322, in particular, the stiffness of the blades 322 decreases gradually along the blade root to the blade tip, and the impeller 32 has optimal stability and good reversible shrinkage of the blades 322 in the deployed state.

Furthermore, the thickness of the blades 322 decreases with increasing distance from the hub 321, i.e. the thickness of the blade root is greater than the thickness of the blade tip, in order to ensure that the performance of the impeller 32 is at its optimum.

As described above, the impeller 32 is self-expandable by releasing stored energy, and at this time, reverse bending may occur to affect the performance of the impeller 32. Therefore, it is desirable that the impeller 32 not be bent in the reverse direction.

Referring to fig. 5, the blades 322 have an initial state a in which they are in the deployed configuration and the impeller 32 is not driven to rotate. When the blades 322 are in the deployed configuration and the impeller 32 is driven to rotate, the blades 322 are deformed compared to the initial state a of the impeller 32. It should be noted that the impeller 32 is driven to rotate in the deployed configuration as compared to the deformation of the impeller 32 in the initial state a, at least or primarily due to the fluid (blood or air) backpressure. Further, the centrifugal force due to the rotation also contributes to the above-described deformation of the blade 322.

In this embodiment, the impeller 32 has a first state b in which the blades 322 are driven to rotate in the deployed configuration to pump blood, and a second state c in which the blades 322 are driven to rotate in the deployed configuration to pump a fluid medium having a viscous resistance less than that of blood.

The blades 322 in the first state b and the second state c are deformed relative to the blades 322 in the initial state a. The fluid medium may be air or water, and because the viscous resistance of the fluid medium is less than the viscous resistance of blood, the fluid back pressure of the fluid medium against the blades 322 is less than the fluid back pressure of blood against the blades 322 when the impeller 32 is driven to rotate with the blades 322 in the deployed configuration. Therefore, the deformation of the blade 322 in the first state b is different from the deformation of the blade 322 in the second state c.

In one possible and not explicitly excluded scenario, the pump assembly 3 is located outside the subject's body, and the impeller 32 is driven to rotate in the deployed state. Although in practice this rotation is generally understood simply as idling rotation, in essence the impeller 32 is pumping air under this rotation.

The diameter of the blade 322 in the first state b is larger than the diameter of the blade 322 in the second state c. And the diameter of the blade 322 in the second state c is larger than the diameter of the blade 322 in the initial state a. That is, the diameter variation tendency of the blade 322 in the first state b is the same as the diameter variation tendency of the blade 322 in the second state c. That is, when the impeller 32 is in an operating state of being driven to rotate for pumping the fluid flow, the maximum projected outer diameter of the blades 322 is larger than the maximum projected outer diameter of the blades 322 in the initial state a. As the viscous drag of the pump output fluid increases, the maximum projected outer diameter of the vanes 322 increases.

That is, the distance between the tip and the root of the blade 322 in the first state b is greater than the distance between the tip and the root of the blade 322 in the second state c.

Specifically, when the blade 322 is in the initial state a, a linear distance d1 is between one end of the blade 322 away from the hub 321 and the central axis of the hub 321; when the blade 322 is in the first state b, a straight distance d2 is formed between one end of the blade 322 away from the hub 321 and the central axis of the hub 321; when the blade 322 is in the second state c, a straight distance between an end of the blade 322 away from the hub 321 and the central axis of the hub 321 is d3, d3 is greater than d2, and d2 is greater than d 1.

It should be noted that the diameter of the blade 322 in the first state b is smaller than the distance from the hub 321 to the pump casing 31, so that the radially outer end of the impeller 32 (i.e., the tip of the blade 322) is spaced from the inner wall of the pump casing 31 (specifically, the inner wall of the bracket 313), and the space is a pump gap. The presence of the pump gap allows the impeller 32 to rotate unimpeded without wall impingement. For hydrodynamic considerations, it is desirable that the pump gap size be of a small value and maintained.

In this embodiment, the diameter of the vanes 322 in the first state b is slightly less than the inner diameter of the bracket 313 so that the pump clearance is as small as possible given that the impeller 32 rotates without hitting the wall. The main means for maintaining the pump gap is the supporting strength provided by the bracket 313, which can resist the action of the back pressure of blood without deformation, so as to maintain the shape of the pump housing 31 to be stable, and the pump gap is also stably maintained, which is beneficial to obtaining better hydraulic effect. Therefore, the phenomenon that the blades 322 are scratched by the pump shell 31 due to the fact that the outer diameter of the blades is enlarged along the radial direction of the hub 321 under the influence of fluid pressure when the blades are driven to rotate is avoided, hemolysis failure is caused, and normal operation of the ventricular assist device 100 is guaranteed.

The blade 322 in the first state b and the blade 322 in the second state c are deformed in the reverse rotation direction. When the impeller 32 rotates in the direction indicated by the arrow e in fig. 5, the deformation direction of the blades 322 in the first state b and the deformation direction of the blades 322 in the second state c are both opposite to the direction e.

Specifically, the amount of deformation in the reverse rotation direction of the blade 322 in the first state b is larger than the amount of deformation in the reverse rotation direction of the blade 322 in the second state c. That is, the radius of curvature of the blade 322 in the first state b is greater than the radius of curvature of the blade 322 in the second state c.

It should be noted that the bending direction of the blades 322 in the first state b is the same as the bending direction of the blades 322 in the deployed configuration and not driven to rotate. It is apparent that the bending direction of the blade 322 in the first state b is the same as the bending direction of the blade 322 in the second state c.

That is, when the impeller 32 pumps blood, the blades 322 are not reversely bent and always keep in the direction of the initial state a, so that the performance of the impeller 32 is ensured, the failure caused by the reverse bending is avoided, and the service life and the stability of the impeller 32 are improved.

In conclusion, the diameter of the blade of the impeller of the ventricular assist device is larger than that of the blade of the fluid medium with the pumping viscous resistance smaller than that of the blood when the impeller of the ventricular assist device pumps the blood, so that the performance of the impeller is ensured, the failure caused by reverse bending is avoided, the service life and the stability of the impeller are improved, and the ventricular assist device is high in reliability and good in performance.

The technical features of the above embodiments can be arbitrarily combined, and for the sake of brevity, all possible combinations of the technical features in the above embodiments are not described, but should be considered as the scope of the present specification as long as there is no contradiction between the combinations of the technical features.

The above examples only show some embodiments of the present invention, and the description thereof is more specific and detailed, but not to be construed as limiting the scope of the utility model. It should be noted that, for a person skilled in the art, several variations and modifications can be made without departing from the inventive concept, which falls within the scope of the present invention. Therefore, the protection scope of the present patent shall be subject to the appended claims.

Claims

1. A ventricular assist device, comprising:

a motor;

a conduit;

2. A ventricular assist device, comprising:

a motor;

a conduit;

3. A ventricular assist device, comprising:

a motor;

a conduit;

4. A ventricular assist device as claimed in any one of claims 1 to 3, wherein the direction of curvature of the blade in the first state is the same as the direction of curvature of the blade in the deployed configuration and not driven for rotation.

5. A ventricular assist device as claimed in any one of claims 1 to 3, wherein the direction of curvature of the blade in the first state is the same as the direction of curvature of the blade in the second state.

6. A ventricular assist device as claimed in any one of claims 1 to 3, wherein the vane in the first state and the vane in the second state are deformed against the direction of rotation.

7. A ventricular assist device as claimed in any one of claims 1 to 3, wherein the distance between the tip and the root of the blade in the first state is greater than the distance between the tip and the root of the blade in the second state.

8. A ventricular assist device as claimed in any one of claims 1 to 3, wherein the diameter of the blade in the first state is less than the distance between the hub and the pump casing.

9. A ventricular assist device as claimed in any one of claims 1 to 3, wherein the blades are of a material having a Shore hardness of 80A-70D.

10. A ventricular assist device as claimed in any one of claims 1 to 3, wherein the blades are at least partially helically wound around the hub.

11. A ventricular assist device as claimed in any one of claims 1 to 3, wherein the blade has a profile with an arc whose curvature varies in the direction of the axis of the hub.

12. A ventricular assist device as claimed in any one of claims 1 to 3, wherein the stiffness of the blade varies along the radial extent of the blade.

13. A ventricular assist device as claimed in any one of claims 1 to 3, wherein the stiffness of the blade root is greater than the stiffness of the blade tip.

14. A ventricular assist device as claimed in any one of claims 1 to 3, wherein the curvature of the blade varies along the radial extent of the blade.

15. A ventricular assist device as claimed in any one of claims 1 to 3, wherein the curvature of the blade increases with increasing distance from the hub.

16. A ventricular assist device as claimed in any one of claims 1 to 3, wherein the thickness of the blade decreases with increasing distance from the hub.