Flexible Membrane Armature Driven Blood Pump

Abstract

The present invention discloses a flexible membrane armature-driven blood pump, which comprises a pump housing, and an armature driver and a wave transmission assembly are arranged inside the pump housing, wherein: the wave transmission assembly includes a flow channel component forming a wave transmission flow channel, and a flexible membrane arranged inside the flow channel component is connected to the armature assembly of the armature driver, so that the armature assembly drives the flexible membrane to vibrate in the wave transmission flow channel under the electromagnetic driving action generated by the armature driver to generate a wave motion, thereby enabling the blood flowing into the pump housing to generate a wave pumping effect with physiological characteristics. The present invention realizes the wave transportation of blood, enables the blood flow to have a pulsatile physiological characteristic, and has stable and reliable operation, is not prone to failure, has a low cost, and is suitable for popularization.

Description

Technical Field

[0001] The present invention relates to a flexible membrane armature-driven blood pump, belonging to the technical field of blood pumps. Background Art

[0002] At present, the number of heart failure patients in China is increasing year by year. One of the effective means for heart failure treatment is the artificial implantation of mechanical ventricular assist devices, and mainly left ventricular assist devices. However, the standard blood pumps available for clinical use are mainly divided into axial flow pumps and centrifugal pumps, both of which belong to rotary pumps. The high-speed rotation of their rotors will damage blood components, resulting in hemolysis, thrombosis and bleeding complications. In addition, they operate at a single pump speed, which will cause a decrease in the patient's pulse pressure during clinical use, and then complications related to continuous non-physiological blood pumping will occur, such as gastrointestinal bleeding, aortic valve insufficiency or stroke. Therefore, researchers have developed a pulsation algorithm for this type of rotary pump, aiming to improve the flushing situation and thus reduce the formation of thrombus and the like. However, the actual clinical effect is not good, and the developed pulsation algorithm cannot overcome the above-mentioned disadvantages to better restore physiological pulse.

[0003] The Chinese patent application with the publication number CN110636873A discloses an implantable system with a rectangular flexible membrane, which proposes a film that can perform undulating motion and well solves the above-mentioned disadvantages. However, it uses an electromagnetic actuator to drive the film to perform undulating motion, with limited driving force, and the limited force density will cause significant heating of the coil and local hot spots, and the motion stability is not good. In addition, the reciprocating mover inside is a coil, which is extremely prone to failure and is not suitable as the power source of the blood pump.

[0004] The Chinese patent application with the publication number CN114712700A discloses a flexible membrane reluctance-driven implantable blood pump and an artificial blood pump system, which well solves the problems existing in the Chinese patent application with the publication number CN110636873A. However, its component composition is relatively large. Especially, the vibration component that drives the flexible membrane to perform undulating motion needs to be installed on the linear guiding component of the hybrid reluctance actuator, and the assembly of the two requires a high degree of matching. Otherwise, it will affect the motion effect of the flexible membrane. It can be seen that the manufacturing and assembly are difficult, and faults are also likely to occur during the motion process. Summary of the Invention

[0005] The purpose of the present invention is to provide a flexible membrane armature-driven blood pump, which realizes the pulsating transportation of blood, makes the blood flow have pulsating physiological characteristics, and is stable and reliable in operation, not prone to failure, low in cost, and suitable for popularization.

[0006] In order to achieve the above purpose, the present invention adopts the following technical solutions:

[0007] A flexible membrane armature-driven blood pump, characterized in that: it includes a pump housing, and an armature driver and a wave transmission component are arranged in the pump housing, wherein: the wave transmission component includes a flow channel component forming a wave transmission flow channel, and a flexible membrane arranged in the flow channel component is connected to the armature component of the armature driver, so that the armature component drives the flexible membrane to vibrate in the wave transmission flow channel under the electromagnetic driving action generated by the armature driver to generate a wave motion, thereby making the blood flowing into the pump housing produce a wave pumping effect with physiological characteristics.

[0008] The advantages of the present invention are:

[0009] On the one hand, the present invention forms the effects of upper and lower liquid bags through the flexible membrane and the flow channel component. Based on the fluid-structure interaction, the undulating transportation of blood is realized, making the blood flow produce pulsatility with physiological characteristics, minimizing the damage to the blood, and reducing the risk of complications such as hemolysis and thrombosis. On the other hand, the armature driver provides a high force density, strong and reliable driving performance, which guarantees the stable fluctuation of the flexible membrane. On the other hand, the structure of the present invention is simple. In particular, the armature component that drives the flexible membrane to move up and down is easy to assemble and is not prone to failure, ensuring the movement effect of the flexible membrane, with low cost and good blood compatibility, and is suitable for clinical promotion. Description of the Drawings

[0010] Figure 1 is a schematic diagram of the first preferred embodiment of the flexible membrane armature-driven blood pump of the present invention.

[0011] Figure 2 is a schematic diagram of the structure of the armature driver.

[0012] Figure 3 is a schematic diagram of the structure of the armature component.

[0013] Figure 4 is a schematic diagram of the structure of the wave transmission component.

[0014] Figure 5 is a schematic diagram of the structure of the flexible membrane.

[0015] Figure 6A is a schematic diagram of the flexible membrane of the first preferred embodiment of the flexible membrane armature-driven blood pump of the present invention in a fluctuating state (the armature plate swings upward).

[0016] Figure 6B is a schematic diagram of the flexible membrane of the first preferred embodiment of the flexible membrane armature-driven blood pump of the present invention in a fluctuating state (the armature plate swings downward).

[0017] Figure 7 is a schematic diagram of the structure of the armature driver of the second preferred embodiment of the flexible membrane armature-driven blood pump of the present invention.

[0018] Figure 8 It is a schematic structural diagram of the armature assembly. Specific Embodiment

[0019] As Figures 1 to 8 , the flexible membrane armature-driven blood pump of the present invention includes a pump housing 10, and an armature driver and a wave transmission assembly are arranged in the pump housing 10, wherein: the wave transmission assembly includes a flow channel component 60 forming a wave transmission flow channel 61, and a flexible membrane 70 arranged in the flow channel component 60 is connected to the armature assembly 20 of the armature driver, that is, the armature driver provides a reliable power source for the flexible membrane 70, so that the armature assembly 20 drives the flexible membrane 70 to vibrate in the wave transmission flow channel 61 under the electromagnetic driving action generated by the armature driver, so that the flexible membrane 70 generates a wave motion, thereby making the blood flowing into the pump housing 10 generate a wave pumping effect with physiological characteristics.

[0020] Referring to Figure 1 and Figure 2 for understanding, the armature driver includes a U-shaped upper spool 31 and an inverted U-shaped lower spool 32 that are symmetric up and down. An electromagnetic coil 30 is wound around the upper spool 31 and the lower spool 32 together. On one side of the upper spool 31 and the lower spool 32, there are respectively a plate-shaped upper magnet 51 and a plate-shaped lower magnet 52. A ring-shaped magnetic yoke 40 surrounds the outside of the upper magnet 51 and the lower magnet 52. The upper magnet 51 and the lower magnet 52 are symmetric up and down and have opposite magnetic polarities. Usually, the upper magnet 51 and the lower magnet 52 are respectively fixed on the inner top wall and the inner bottom wall of the magnetic yoke 40. The magnetic yoke 40 is in the same circumferential direction as the electromagnetic coil 30. The space between the upper spool 31 and the lower spool 32 and the space between the upper magnet 51 and the lower magnet 52 together form a vibration space 80. The vibration space 80 is communicated with the wave transmission flow channel 61 formed by the flow channel component 60, that is, the flow channel component 60 is arranged on one side of the magnetic yoke 40, and the magnetic yoke 40 is between the upper and lower spools 31, 32 and the flow channel component 60, wherein:

[0021] The armature driver further includes an armature assembly 20. The armature assembly 20 includes an armature plate 21, a base plate 22, and a support plate 23 connecting the armature plate 21 and the base plate 22. The armature plate 21, the base plate 22, and the support plate 23 form a lying U-shaped structure. The armature plate 21 is in the vibration space 80, while the base plate 22 and the support plate 23 are outside the vibration space 80. The armature plate 21 penetrates through the vibration space 80, and the suspended end 211 of the armature plate 21 extends from the vibration space 80 into the wave transmission flow channel 61 and is connected to the connection end 71 of the flexible membrane 70, that is, the armature plate 21 of the armature assembly 20 is longer than the base plate 22. The base plate 22 is sandwiched between the lower spool 32 wound with the electromagnetic coil 30, the lower magnet 52, and the inner wall of the pump housing 10. The armature plate 21 is suspended in the vibration space 80.

[0022] In actual design, the upper spool 31 and the lower spool 32 that function to constrain the electromagnetic coil 30 are made of non-magnetic materials (such as well-known materials like titanium alloy), and in addition, to avoid blood compatibility problems caused by the contact between the electromagnetic coil 30 and blood, a protective layer made of a non-magnetic material (such as well-known materials like titanium alloy) can be covered on the inner wall of the electromagnetic coil 30.

[0023] Preferably, the upper spool 31 and the lower spool 32 can be integrally formed into a ring shape, which not only reduces the assembly difficulty but also directly avoids blood compatibility problems. Of course, an electromagnetic coil without spool support can also be used, and to avoid blood compatibility problems, a non-magnetic material that can avoid blood compatibility problems can be provided on the inner wall of the electromagnetic coil.

[0024] The electromagnetic coil 30 is made of copper or aluminum wire, and the cable led out from the electromagnetic coil 30 extends out through the corresponding holes opened on the pump housing 10 and is connected to an external power supply device.

[0025] In actual design, the upper magnet 51 and the lower magnet 52 can be permanent magnets, or magnets formed by combining single or multiple magnetic bodies that can attract substances such as iron, cobalt, or nickel.

[0026] The yoke 40 can be made of materials such as soft iron, A3 steel, ferrite, or soft magnetic alloy with good magnetic conductivity, mainly used to improve the magnetic induction efficiency and play the roles of suppressing electromagnetic interference and reducing the heat generation of metal components.

[0027] In actual design, similarly, to avoid blood compatibility problems, a protective layer made of a non-magnetic material (such as well-known materials like titanium alloy) can be covered on the inner walls of the upper magnet 51, the lower magnet 52, and the yoke 40 facing the vibration space 80.

[0028] In actual design, the suspended end 211 of the armature plate 21 should be wider and flat than other parts of the armature plate 21. Correspondingly, the size of the connecting end 71 of the flexible film 70 should be adapted to the size of the suspended end 211 of the armature plate 21 so that the two can be firmly connected. In actual production, the armature plate 21 and the flexible film 70 can be connected into one body by means such as bonding or dipping, without limitation.

[0029] In the present invention, the flexible film 70 is designed, for example, as a soft, deformable, elastic, and biocompatible thin sheet made of silicone or polyurethane composite material. The shape, thickness, and installation method (such as bonding with epoxy resin glue, screw fixing, etc.) of the flexible film 70 are not limited, as long as it can produce a large deformation fluctuation effect along the blood flow direction under the combined action of vibration force, fluid force, etc.

[0030] Furthermore, the flexible film 70 should have a relatively low density. In this way, compared with materials of higher density, it not only reduces the mass of the flexible film, increases the sensitivity, and improves the response speed, but also reduces the stiffness required for the armature assembly 20. At the same time, the flexible film 70 needs to have a low elastic modulus to produce a large-deformation fluctuation effect. In actual production, the flexible film 70 can be designed to have a specific modulus less than 8500 Pa / (kg / m 3 ), where the specific modulus of a material is equal to the elastic modulus / density and is also equal to the stress / strain of the material. Additionally, the modulus of the material forming the flexible film 70 can be isotropic or anisotropic, without limitation.

[0031] For example Figure 3 , a plurality of limiting protrusions 210 can be symmetrically provided on the upper and lower surfaces of the armature piece 21. Each limiting protrusion 210 is located between the upper magnet 51 and the lower magnet 52, where: when no current is passed through the electromagnetic coil 30, the armature piece 21 is in the middle of the vibration space 80 in the up-down direction, that is, the armature piece 21 is in a balanced state.

[0032] Furthermore, when current is passed through the electromagnetic coil 30, the armature piece 21 will be attracted and pulled upward or downward under the combined magnetic action of the induced magnetic field generated by the electromagnetic coil 30 and the magnetism of the upper magnet 51 or the lower magnet 52. Thus, under the action of passing an alternating current through the electromagnetic coil 30, the armature piece 21 produces an up-down swinging effect, or rather the suspended end 211 moves up and down. Subsequently, the armature piece 21 transmits its swinging effect to the flexible film 70, that is, drives the flexible film 70 to swing, and then the flexible film 70 produces a fluctuation motion effect along the blood flow direction.

[0033] In the present invention, the function of the limiting protrusions 210 is to limit the up-down swinging angle of the armature piece 21 to prevent the armature piece 21 from touching the upper magnet 51 and the lower magnet 52, especially to prevent the suspended end 211 of the armature piece 21 from touching the inner wall of the flow channel component 60. Compared with setting limiting protrusions or other forms of buffers on the upper spool 31, the lower spool 32, or the upper magnet 51 and the lower magnet 52, the setting of the limiting protrusions 210 on the armature piece 21 can reduce the cost to a greater extent.

[0034] In the present invention, the armature assembly 20 can be made of stainless steel, silicon steel, or other biocompatible steel materials. The function of the armature piece 21 is to sense the magnetic field and generate a swinging motion.

[0035] In actual design, for example Figure 1, only one armature driver may be provided in the pump housing 10, and this one armature driver and a wave transmission assembly are arranged along the length direction of the pump housing 10, wherein: the vibration space 80 is opposite to the pump inlet 11 on the pump housing 10, so that blood is transmitted through the vibration space 80; a circulation port 230 is provided on the support piece 23 of the armature assembly 20 of the armature driver, and the armature sheet 21 divides the vibration space 80 into upper and lower parts. The pump inlet 11 of the pump housing 10 is directly communicated with the upper part of the vibration space 80, and the pump inlet 11 of the pump housing 10 is communicated with the lower part of the vibration space 80 through the circulation port 230; the wave transmission channel 61 formed by the flow channel member 60 is opposite to the pump outlet 12 on the pump housing 10, so that blood is conveyed out through the wave transmission channel 61. Here, the armature sheet 21 also has the function of shunting blood up and down.

[0036] In addition, with reference to Figure 7 and Figure 8 for understanding, two armature drivers are provided side by side and separately along the width direction of the pump housing 10 in the pump housing 10. These two armature drivers and a wave transmission assembly are arranged along the length direction of the pump housing 10. The suspended ends 211 of the armature sheets 21 of these two armature drivers are connected into one body after extending out of their respective vibration spaces 80 and are connected to the flexible membrane 70, wherein: the blood delivery space 230' formed between these two armature drivers is opposite to the pump inlet 11 on the pump housing 10 for transmitting blood; the vibration spaces 80 and the blood delivery space 230' formed by these two armature drivers respectively communicate with the wave transmission channel 61 formed by the flow channel member 60; the wave transmission channel 61 is opposite to the pump outlet 12 on the pump housing 10 for delivering blood; the current directions of the electromagnetic coils 30 of these two armature drivers are the same and the switching of the current directions is synchronously controlled. Here, the suspended ends 211 connected into one body in the two armature drivers also have the function of shunting.

[0037] In actual design, such as Figure 7 , in order to avoid the problem of blood compatibility caused by the contact between the electromagnetic coil 30, the yoke 40 and blood, preferably, a protective cover made of a non-magnetic material (such as well-known materials such as titanium alloy material) can be provided outside the two armature drivers. Here, the amount of blood flowing from the wave transmission channel 61 into the vibration space 80 is extremely small and can be ignored. Of course, protective measures to avoid blood compatibility problems can also be designed at the position where the suspended ends 211 of the armature sheet 21 extend out of the vibration space 80, which will not be elaborated here.

[0038] In the present invention, the shape of the pump housing 10 is not limited. Such as Figure 1, the pump housing 10 is generally in the shape of a rectangular body, and its height, width, and length directions are as shown in the figure. In the present invention, the blood flow direction is defined in the length direction of the pump housing 10, that is, the blood flow direction is from the pump inlet 11 to the pump outlet 12. The height direction of the pump housing 10, that is, the up-and-down direction, is defined as the direction in which the armature piece 21 swings up and down.

[0039] Taking Figure 1 the blood pump of the present invention shown as an example, inside the pump housing 10, the armature driver and the wave transmission assembly are arranged along the length direction of the pump housing 10. The upper shaft 31 and the lower shaft 32 of the armature driver are arranged along the height direction of the pump housing 10. Similarly, the upper magnet 51 and the lower magnet 52 are arranged along the height direction of the pump housing 10. The electromagnetic coil 30 and the yoke 40 are wound or surrounded with the length direction of the pump housing 10 as the axis. The suspended end 211 of the armature piece 21 of the armature assembly 20 and the swinging direction of the flexible membrane 70 it drives are along the height direction of the pump housing 10. The vibration space 80 and the wave transmission flow channel 61 are formed along the length direction of the pump housing 10. The direction in which the wave generated by the flexible membrane 70 pumps blood is along the length direction of the pump housing 10. More precisely, the blood flow direction is the direction in which blood flows from the pump inlet 11 to the pump outlet 12.

[0040] In the present invention, the pump housing 10 and the flow channel component 60 can be made of stainless steel, cobalt-based, titanium-based alloys, or other rigid materials with biocompatibility.

[0041] Such as Figure 4 , the flow channel component 60 is in the shape of a rectangular body. From the longitudinal section obtained by cutting the flow channel component 60 along the length direction of the pump housing 10, the wave transmission flow channel 61 is composed of a rectangular body-shaped inlet flow channel 611, a transition flow channel 612 with a lying trapezoidal longitudinal section, a flat plate-shaped main flow channel 613, and a lying frustum-shaped outlet flow channel 614 that are connected in sequence. Among them, the inlet flow channel 611, the transition flow channel 612, and the main flow channel 613 can be arranged throughout the width direction of the pump housing 10. Among them: the outlet of the inlet flow channel 611 is contracted into the inlet of the main flow channel 613 through the transition flow channel 612, and the outlet of the outlet flow channel 614 is larger than its own inlet; the suspended end 211 of the armature piece 21 extends into the inlet flow channel 611 and is connected to the connection end 71 of the flexible membrane 70. The wave end of the flexible membrane 70, that is, the other end opposite to the connection end 71, is in the main flow channel 613.

[0042] In the present invention, the purpose of the above structural design of the wave transmission flow channel 61 is that the blood flowing into the inlet flow channel 611 can accelerate its own flow rate through the contraction design of the transition flow channel 612, and then flow into the main flow channel 613. Thus, under the wave motion of the flexible membrane 70 in the main flow channel 613, a wave pumping effect with physiological characteristics is generated for the blood, and the blood will also produce an accelerated flow effect when passing through the outlet flow channel 614.

[0043] As Figure 6A and Figure 6B , the fluctuating transmission channel 61 divides the channel component 60 into upper and lower parts. Among them, a liquid pocket is formed between the upper part and the flexible membrane 70, and another liquid pocket is formed between the lower part and the flexible membrane 70.

[0044] In the present invention, by designing the up-and-down swing frequency and swing amplitude of the suspended end 211, and adjusting the pressure gradients in the inlet channel 611 and the transition channel 612, the flow rate of blood flow can be regulated. In actual design, preferably, the swing amplitude of the suspended end 211 of the armature assembly 20 is set to 1.2 mm, and the swing frequency of the suspended end 211 is set to 60 Hz. Among them, the average blood flow rate through the fluctuating transmission channel 61 is between 2.3 L / min and 3.8 L / min (pulsatile physiological flow rate) to meet the blood pressure difference of 60 mmHg for the blood entering and leaving the pump housing 10. Of course, the swing frequency of the suspended end 211 can be between 0 Hz and 120 Hz, and of course, it can also be designed as other swing frequencies.

[0045] In the present invention, all components that need to come into contact with blood should be made of materials with excellent blood compatibility, such as titanium alloy materials.

[0046] The present invention is realized based on the principles of electromagnetic induction, mechanical vibration and fluid-structure interaction. The following takes Figure 1 the blood pump of the present invention shown as an example to illustrate the working process and driving principle. The working process and driving principle of the second preferred embodiment of the blood pump of the present invention with the Figure 7 shown armature driver are basically the same as those shown in Figure 1 , so they will not be described in detail.

[0047] As Figure 1 , it is set that the magnetic properties of the upper magnet 51 and the lower magnet 52 are N and S respectively.

[0048] When no current is passed through the electromagnetic coil 30, the attracting strengths of the armature plate 21 by the upper magnet 51 and the lower magnet 52 are equal and in opposite directions. Therefore, the armature plate 21 is in the middle position of the vibration space 80 in the up-and-down direction, that is, in a balanced state.

[0049] When a current is passed through the electromagnetic coil 30 and the direction of the induced magnetic field generated between the upper magnet 51 and the lower magnet 52 is the same as the blood flow direction, the armature plate 21 is attracted upward under the combined action of the electromagnetic force and the magnetic force. On the contrary, when a reverse current is passed through the electromagnetic coil 30 and the direction of the induced magnetic field generated between the upper magnet 51 and the lower magnet 52 is opposite to the blood flow direction, the armature plate 21 is attracted downward under the combined action of the electromagnetic force and the magnetic force.

[0050] Thus, by continuously switching the direction of the current flowing through the electromagnetic coil 30, the armature piece 21 can be swung up and down, so that the suspended end 211 of the armature piece 21 drives the flexible membrane 70 to swing up and down. Subsequently, the flexible membrane 70 generates undulating wave motion, and pumps the blood flowing in from the pump inlet 11 to the pump outlet 12 in a fluctuating manner.

[0051] Figure 6A Fig. shows the state at a certain moment during the upward movement of the suspended end 211. Blood flows into the space between the suspended end 211 and the flexible membrane 70 and the inner bottom wall of the inlet channel 611, and with the propagation of the fluctuation of the flexible membrane 70, the blood is pushed towards the outlet channel 614. At this time, a liquid bag A is formed between the upper part of the channel component 60 and the flexible membrane 70, and a liquid bag B is formed between the lower part of the channel component 60 and the flexible membrane 70. The liquid bag A and the liquid bag B show a tendency to flow towards the outlet channel 614 to push the blood out of the pump housing 10.

[0052] Figure 6B Fig. shows the state at a certain moment during the downward movement of the suspended end 211. Blood flows into the space between the suspended end 211 and the flexible membrane 70 and the inner top wall of the inlet channel 611, and with the propagation of the fluctuation of the flexible membrane 70, the blood is pushed towards the outlet channel 614. At this time, the liquid bag A gradually becomes smaller and disappears, and is replaced by a liquid bag C formed between the lower part of the channel component 60 and the flexible membrane 70. Similarly, the liquid bag B gradually becomes smaller and disappears, and is replaced by a liquid bag D formed between the upper part of the channel component 60 and the flexible membrane 70. The liquid bag C and the liquid bag D show a tendency to flow towards the outlet channel 614 to push the blood out of the pump housing 10.

[0053] Preferably, the speed of the wave generated by the flexible membrane 70 for propagating blood should be controlled between 1.0 m / s and 2.0 m / s, but of course it is not limited.

[0054] The advantages of the present invention are as follows:

[0055] On the one hand, the present invention forms the effect of upper and lower two liquid bags through the flexible membrane and the channel component. Based on the fluid-structure interaction, the undulating transportation of blood is realized, making the blood flow generate pulsatility with physiological characteristics, minimizing the damage to the blood, and reducing the risk of complications such as hemolysis and thrombosis. On the other hand, the armature driver provides a high force density, strong and reliable driving performance, which guarantees the stable fluctuation of the flexible membrane. On the other hand, the structure of the present invention is simple, especially the armature assembly that drives the flexible membrane to make undulating motion is easy to assemble and is not prone to failure, ensuring the motion effect of the flexible membrane, with low cost and good blood compatibility, and is suitable for clinical promotion.

[0056] The above are the preferred embodiments of the present invention and the technical principles applied thereto. For those skilled in the art, any obvious changes such as equivalent transformations and simple substitutions based on the technical solution of the present invention without departing from the spirit and scope of the present invention shall fall within the protection scope of the present invention.

Claims

1. A flexible membrane armature-driven blood pump, characterized in that: It includes a pump housing, in which an armature driver and a wave transmission component are arranged, where: The wave transmission component includes a flow channel component forming a wave transmission flow channel. A flexible membrane arranged in the flow channel component is connected to the armature component of the armature driver, so that the armature component drives the flexible membrane to vibrate in the wave transmission flow channel under the electromagnetic driving action generated by the armature driver, generating a wave motion, thereby making the blood flowing into the pump housing produce a wave pumping effect with physiological characteristics; The armature driver includes a U-shaped upper spool and an inverted U-shaped lower spool that are symmetric up and down. An electromagnetic coil is wound around the upper spool and the lower spool together. On one side of the upper spool and the lower spool, there are respectively a plate-shaped upper magnet and a plate-shaped lower magnet. An annular magnetic yoke surrounds the outside of the upper magnet and the lower magnet. The upper magnet and the lower magnet are symmetric up and down and have opposite magnetic polarities. The space between the upper spool and the lower spool and the space between the upper magnet and the lower magnet together form a vibration space, and the vibration space is communicated with the wave transmission flow channel formed by the flow channel component, where: The armature driver further includes an armature component, and the armature component includes an armature plate, a substrate, and a support piece connecting the armature plate and the substrate. The armature plate, the substrate, and the support piece form an inverted U-shaped structure. The armature plate is located in the vibration space while the substrate and the support piece are located outside the vibration space. The armature plate penetrates through the vibration space, and the suspended end of the armature plate extends from the vibration space into the wave transmission flow channel and is connected to the connection end of the flexible membrane; A plurality of limiting protrusions are symmetrically arranged on the upper and lower surfaces of the armature plate, and each limiting protrusion is located between the upper magnet and the lower magnet, where: When no current is passed through the electromagnetic coil, the armature plate is located exactly in the middle of the vibration space in the up and down direction.

2. The flexible membrane armature-driven blood pump according to claim 1, characterized in that: Only one said armature driver is arranged in the said pump housing, and this one said armature driver and one said wave transmission component are arranged along the length direction of the said pump housing, where: The said vibration space is opposite to the pump inlet on the said pump housing, so that blood is transmitted through the said vibration space; A circulation port is arranged on the said support piece of the said armature component of the said armature driver. The armature plate divides the vibration space into upper and lower parts. The pump inlet of the said pump housing is directly communicated with the upper part of the vibration space, and the pump inlet of the said pump housing is communicated with the lower part of the vibration space through the circulation port; The wave transmission flow channel formed by the said flow channel component is opposite to the pump outlet on the said pump housing, so that blood is transported out through the said wave transmission flow channel.

3. The flexible membrane armature-driven blood pump according to claim 1, characterized in that: Two of the armature drivers are provided side by side and separately along the width direction of the pump housing. The two armature drivers and a wave transmission component are arranged along the length direction of the pump housing. The armature sheets of the two armature drivers extend out of their respective vibration spaces, and the suspended ends thereof are connected into one body and connected to the flexible membrane. Wherein: the blood delivery space formed between the two armature drivers is opposite to the pump inlet on the pump housing for transporting blood; the vibration spaces and blood delivery spaces formed by the two armature drivers respectively communicate with the wave transmission flow channel formed by the flow channel component; the wave transmission flow channel is opposite to the pump outlet on the pump housing for discharging blood; the current directions of the electromagnetic coils of the two armature drivers are the same and the switching of the current directions is synchronously controlled.

4. The flexible membrane armature-driven blood pump according to any one of claims 1 to 3, characterized in that: The flow channel component is in the shape of a rectangular body. The wave transmission flow channel is composed of a rectangular body-shaped inlet flow channel, a transition flow channel with a lying trapezoidal longitudinal section, a flat plate-shaped main flow channel, and a lying frustum-shaped outlet flow channel connected in sequence. Wherein: the outlet of the inlet flow channel contracts into the inlet of the main flow channel via the transition flow channel, and the outlet of the outlet flow channel is larger than its own inlet; the suspended end of the armature sheet extends into the inlet flow channel and is connected to the connecting end of the flexible membrane, and the fluctuating end of the flexible membrane is in the main flow channel.

5. The flexible membrane armature-driven blood pump according to claim 4, characterized in that: The swing amplitude of the suspended end of the armature assembly is set to 1.2 mm, and the swing frequency of the suspended end is set to 60 Hz. Wherein, the average blood flow rate flowing through the wave transmission flow channel is between 2.3 L / min and 3.8 L / min to meet the blood pressure difference between the blood entering and leaving the pump housing of 60 mmHg.

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