In-vivo liquid flow auxiliary device

Abstract

The invention discloses an in-vivo liquid flow assisting device, which comprises a support body, which has a shape suitable for being placed in a cavity so as to enable liquid to flow on the outer surface or the inner surface of the support body, and is provided with a plurality of fluid through holes, and the fluid through holes penetrate through the outer surface and the inner surface of the support body; the plurality of paddles are fixed on the outer surface and / or the inner surface of the support body and can move repeatedly in the direction perpendicular to the outer surface or the inner surface relative to the support body, so that the flow speed or the flow direction of the liquid is changed; the control wires are used for respectively controlling the paddles to enter a working state or a stopping state, and in the working state, the liquid is allowed to flow through the fluid through holes; in the stopped state, the fluid through hole is closed by the paddle, and liquid is prevented from flowing through the fluid through hole. The flow direction or the flow speed of liquid in the body is changed through tiny fin vibration, and blood pumping is rapidly achieved on the premise that cells in blood are not damaged.

Description

Technical Field

[0001] The invention relates to an in vivo liquid flow auxiliary device, belonging to the technical field of medical devices. Background Art

[0002] With the continuous development of the aging population, the number of patients with end-stage heart disease continues to rise, and the effect of drug treatment is limited. Therefore, heart transplantation and artificial hearts have become the main means of treating severe heart failure. Although heart transplantation is an ideal choice, the problem of insufficient donors limits its application, which has prompted the rapid development of artificial heart technology. At present, the main artificial heart system used in my country is the left ventricular assist device (LVAD). Relevant studies have shown that the 3-year survival rate of its latest product has reached 80%, which is close to the effect of heart transplantation and has been widely used in Europe and the United States.

[0003] The artificial heart system consists of four parts: blood pump, drive device, monitoring system and energy source, among which the blood pump is the core component. Blood pumps can be divided into pulsatile pumps, axial flow pumps and centrifugal pumps according to different working principles. Early pulsatile artificial hearts imitated the contraction and relaxation of the heart, but due to the greater damage to the blood, they were prone to complications such as thrombosis and stroke, and were mainly used as a transitional means before heart transplantation.

[0004] With the advancement of technology, axial flow pumps and centrifugal pumps have become the mainstream of artificial hearts. Axial flow pumps pump blood through high-speed rotating impellers, but high speeds may cause damage to cells in the blood, increasing the risk of thrombosis and stroke. To solve this problem, the third-generation centrifugal pumps use technologies such as magnetic fluid suspension, magnetic suspension, and pure water suspension to avoid direct contact between blood and bearings and reduce the formation of thrombi. However, magnetic fluid suspension artificial hearts still have the problem of cerebral stroke in clinical applications, which may be related to the shear stress of blood in the secondary flow channel, which exceeds the physiological conditions and causes mechanical damage to the formed components in the blood.

[0005] Given the limitations of existing technologies, researchers are seeking to develop a new type of invasive in vivo fluid flow assist device that should be able to effectively assist blood flow without damaging blood cells to meet the treatment needs of patients with severe heart failure. Summary of the invention

[0006] The technical problem to be solved by the present invention is to provide a device for assisting the flow of in vivo liquid.

[0007] In order to achieve the above technical objectives, the present invention adopts the following technical solutions:

[0008] According to a first aspect of an embodiment of the present invention, there is provided an in vivo fluid flow assisting device, comprising:

[0009] A support body having a shape suitable for being placed in the cavity so that liquid flows on the outer surface or the inner surface of the support body, and having a plurality of fluid through holes, the fluid through holes penetrating the outer surface and the inner surface of the support body;

[0010] A plurality of paddles are fixed to the outer surface and / or the inner surface of the support body and can repeatedly move relative to the support body in a direction perpendicular to the outer surface or the inner surface to change the flow rate or flow direction of the liquid;

[0011] A plurality of control wires respectively control the paddles to enter a working state or a stopping state. In the working state, the liquid is allowed to flow through the fluid through hole; in the stopping state, the fluid through hole is closed by the paddles and the liquid is prohibited from flowing through the fluid through hole.

[0012] Preferably, the in vivo fluid flow assisting device further comprises a one-way valve diaphragm.

[0013] The one-way valve diaphragm and the paddle are respectively located on both sides of the liquid through hole.

[0014] The one-way valve membrane is designed to allow the liquid to flow from the paddle through the fluid through hole; and to prohibit the liquid from flowing from the fluid through hole to the paddle.

[0015] Preferably, the paddles, the fluid through holes and the one-way valve diaphragm are arranged in one-to-one correspondence.

[0016] According to a second aspect of an embodiment of the present invention, another in vivo fluid flow assisting device is provided, comprising:

[0017] A support having a shape suitable for placement in the cavity so that the liquid flows on the surface of the support;

[0018] A plurality of paddles are fixed on one side of the support body and are capable of repeatedly moving relative to the support body in a direction perpendicular to the surface of the support body so as to change the flow rate or flow direction of the liquid;

[0019] A plurality of control wires respectively control the paddles to enter a working state or a stopping state. In the working state, the liquid is driven by the movement of the paddles to change the flow rate; in the stopping state, the paddles are stationary so that the liquid flows through the surface of the support body at a constant flow rate.

[0020] Preferably, each of the blades comprises a fixed base, a vibrator generator and a fin;

[0021] The fixed base is mounted on the outer surface or the inner surface of the support body;

[0022] One end of the vibrator generator is connected to the fixed base, and the other end is connected to the fin;

[0023] The fins vibrate under the drive of the vibrator generator to change the flow rate or flow direction of the liquid.

[0024] Preferably, each of the fins is arranged along the longitudinal direction of the support body, and the directions of the fins are consistent or opposite.

[0025] Preferably, the fins are made of any one or more of piezoelectric materials, alloy materials or fiber materials.

[0026] Preferably, a predetermined distance is provided between the fin and the support body;

[0027] The predetermined distance is determined according to the vibration amplitude of the fin to ensure that the fin does not contact the support body when vibrating.

[0028] Preferably, the support body includes a plurality of sections, and each section is provided with a plurality of blades.

[0029] Preferably, the segments are designed to be separable from each other or connected as a whole; and the blades are evenly distributed on the surface of the segments.

[0030] Preferably, at both ends of the longitudinal direction of each segment, one end is provided with a plurality of connection holes, and at the other end, connection rods are spaced apart at positions corresponding to the connection holes for insertion into the connection holes of adjacent segments.

[0031] Preferably, the fin is provided with primary reinforcing ribs and secondary reinforcing ribs, so that different regions of the fin have different strengths, and the secondary reinforcing ribs are used to adjust the vibration direction of the fin. Alternatively, the fin is provided with a coating area, so that different regions of the fin have different thicknesses. Alternatively, the fin is provided with a groove, so that different regions of the fin have different strengths or thicknesses.

[0032] Compared with the prior art, the in vivo liquid flow assist device provided in the embodiment of the present invention adopts multiple distributed liquid extrusion structures. Since the extrusion force of each paddle is very small, but the number is large, the small extrusion force will not affect the cells, and the flow rate or flow direction will not be damaged while changing the flow rate; moreover, each paddle can be controlled separately by conducting or disconnecting the power, so the number of fins entering the working state can be accurately controlled according to the required flow rate, thereby accurately controlling the flow rate or flow direction; since the shape of the support body can be pre-formed into various shapes, it can be suitable for cavities of different shapes such as blood vessels, heart, gallbladder, bladder, etc.; connecting rods can also be used to achieve support bodies of different lengths to suit cavities of different lengths. BRIEF DESCRIPTION OF THE DRAWINGS

[0033] Figure 1 A schematic diagram of a partial structure of a device for assisting in vivo fluid flow provided by an embodiment of the present invention;

[0034] Figure 2 for Figure 1 , a schematic diagram of a segmented three-dimensional structure;

[0035] Figure 3 for Figure 2 A schematic side view of the structure of the in vivo liquid flow assisting device shown;

[0036] Figure 4 for Figure 2 A perspective structural diagram of the in vivo fluid flow assisting device shown;

[0037] Figure 5 for Figure 4 A schematic top view of the structure of the in vivo liquid flow assisting device shown;

[0038] Figure 6 for Figure 1 A schematic diagram of an application scenario in which there is liquid both inside and outside the in vivo liquid flow assisting device shown;

[0039] Figure 7 for Figure 1 A schematic diagram of an application scenario of diverting internal liquid in the in vivo liquid flow assisting device shown;

[0040] Fig. 8A for Figure 1 A schematic diagram of an application scenario of accelerating liquid on one side in the in vivo liquid flow assisting device shown;

[0041] Figure 8B for Figure 1 A schematic diagram of an application scenario of slowing down the liquid on one side in the in vivo liquid flow assisting device shown;

[0042] Fig. 9 for Figure 1 A schematic diagram of an application scenario in which the support body of the in vivo liquid flow assisting device is a solid structure;

[0043] Fig.10 for Figure 1 A schematic diagram of an application scenario in which only internal fluid is present in the in vivo fluid flow assisting device shown;

[0044] Fig.11 for Figure 1 A schematic diagram of an application scenario of accelerating liquid on both sides in the in vivo liquid flow assisting device shown;

[0045] Fig.12A schematic diagram of a partial structure of a device for assisting in vivo fluid flow provided by an embodiment of the present invention;

[0046] Fig.13 for Fig.12 A schematic structural diagram of the in vivo liquid flow assisting device from another angle is shown. DETAILED DESCRIPTION

[0047] The technical content of the present invention is described in detail below with reference to the accompanying drawings and specific embodiments.

[0048] The in vivo liquid flow assist device provided by the embodiment of the present invention is used to be delivered to the target position through the femoral artery or radial artery access, and then change the flow rate or flow direction of the fluid at this position. Among them, the first application scenario is: implanted in the heart (such as the left ventricle), using multiple blades on the in vivo liquid flow assist device to work and squeeze the blood together, so that the blood is pumped out of the aorta to reach the heart contraction state; multiple blades enter the closed state to reach the heart diastole state. The second application scenario is: implanted in the blood vessel position where mild vascular embolism occurs. Using multiple blades on the in vivo liquid flow assist device to alternately enter the working state, accelerate blood flow, help flush the blood vessel wall, reduce the formation of thrombus; relieve discomfort symptoms, and promote the establishment of collateral circulation. The third application scenario is: implanted in the gallbladder to promote bile excretion; the fourth application scenario is: used in the treatment of varicose veins, play the role of venous valves, and avoid blood reflux. The above is just an example, and it can also be used in other application scenarios.

[0049] The following description will be made by taking the intervention of the blood flow rate in the blood vessels as an example.

[0050] like Figure 1 and Figure 2 As shown, an embodiment of the present invention discloses an in vivo liquid flow assist device, which includes a support body 1, a plurality of paddles 2, a one-way valve diaphragm 3 and a control wire 4. In this embodiment, the control wire 4 is a conductive wire, extending along the longitudinal direction of the support body 1, and one end of the control wire 4 is connected to the power supply in the handle to supply power to each paddle 2, so that each paddle 2 enters a working state (when powered on) or enters a closed state (when powered off). It should be noted that because it is a temporary auxiliary intervention for liquids such as blood (not long-term implantation in the body), the material and shape of the in vivo liquid flow assist device will not cause embolism, etc.

[0051] The support body 1 is made of a polymer material, ceramic, silicon material or metal material that can be implanted in the body. The support body 1 can be in a tubular, strip, plate or other shape suitable for placement in a cavity, which is determined by the shape of the body position where it is implanted. Moreover, the support body 1 can be a combination of any one or more catheters in a hollow tube or a multi-cavity tube. The support body 1 is prepared by a process technology that changes its own structure, such as cutting, carving, and splicing, so that it has a certain hardness while maintaining a certain softness. In this embodiment, the support body 1 is an octagonal tubular structure as an example for illustration, but this does not constitute a limitation of the present invention.

[0052] Optionally, the support body 1 includes a flexible section, a working section, and a connecting section which are connected in sequence. The flexible section is arranged at the distal end of the support body 1 and extends along the length direction of the support body 1 to reduce damage to the tissues around the cavity. The connecting section is connected to the working section, and the connecting section is connected to the handle / connector. The working section is located between the flexible section and the connecting section. The support body 1 has a shape suitable for being placed in the cavity, and the anatomical structure of the position to be implanted is the same. Due to the conformability of the material of the support body 1, the paddle 2 can be fixed at the target position. Another optional scheme is that there is no flexible section and connecting section, only a working section.

[0053] like Figure 3 and Figure 4 As shown, the support body 1 includes a plurality of segments 10, and each segment 10 is arranged along the longitudinal direction. A plurality of auxiliary fixing holes 11 and fluid through holes 12 are provided on each segment 10. The centers of the auxiliary fixing holes 11 and the fluid through holes 12 correspond one to one in the longitudinal direction (the two have the same number, M in each segment), and the line connecting the centers of the circles is parallel to the longitudinal axis of the support body 1. In other words, on a segment, a plurality of auxiliary fixing holes 11 are arranged radially symmetrically in the radial direction; and a plurality of fluid through holes 12 are arranged radially symmetrically in the radial direction. The diameter of the fluid through hole 12 is larger than the auxiliary fixing hole 11. The diameter of the fluid through hole 12 is determined according to the vibration frequency, size and required flow rate of the fin 23. The fluid through hole 12 runs through the thickness direction of the support body 1 to allow liquid to enter from one surface of the support body 1 to another surface, for example, from the outer surface of the support body 1 through the fluid through hole 12 to the inner surface.

[0054] It should be noted that a plurality of blades 2 are provided in the working section, and the blades 2 are evenly distributed in the entire working section, and can be arranged in a matrix, staggered or spiral arrangement ( Figure 1 In addition, the blades 2 may be arranged on the outer surface or the inner surface of the support body 1, or may be arranged on the outer surface and the inner surface of the support body 1 at the same time.

[0055] like Figure 3 and Figure 4As shown, the paddle 2 includes a fixed base 21, a vibrator generator 22 and a fin 23. By operating the handle, the control wire 4 is used to energize or de-energize each paddle 2, so that the energized paddle 2 enters the working state (in the present embodiment, it is an open state, allowing liquid to flow through the fluid through hole 12), and the de-energized paddle 2 stops working (in the present embodiment, it is a closed state). However, it can also be closed when powered on and open when powered off. In this way, all the paddles 2 can work simultaneously or one by one, thereby accelerating or decelerating the blood, or changing the flow direction of the liquid.

[0056] The fixing base 21 is fixedly mounted on the outer surface or the inner surface of the supporting body 1 through the auxiliary fixing hole 11 .

[0057] The number (N) of the fixed base 21 , the vibrator generator 22 , and the fins 23 corresponds to each other, and is less than or equal to the number (M) of the fluid through holes 12 , that is, N≤M.

[0058] One end of the vibrator generator 22 is fixedly connected to the fixed base 21, and the other end is fixedly connected to the fin 23. That is, the fixed base 21 is sandwiched between the vibrator generator 22 and the support body 1. When powered on, the vibrator generator 22 vibrates to drive the fin 23 to vibrate. It should be noted that after the vibrator generator 22 is powered on, the vibration frequency of the vibrator generator 22 is 10Hz to 1000KHz, preferably 10KHz to 100KHz. The vibration frequency is determined according to the fin material and the expected liquid flow rate.

[0059] The fin 23 can be made of any one or more of piezoelectric material, alloy material or fiber material, and the shape can be a sheet or bionic wing shape or other shapes that conform to fluid mechanics. The fin 23 covers the outside or inside of the fluid through hole 12 on the support body 1, and the shape and size are sufficient to completely cover the fluid through hole 12. The outside of one end of the fin 23 (the side away from the support body) is connected or bonded to the inside of one end of the vibrator generator 22 (the side close to the support body). That is, the fin 23 is located between the support body 1 and the vibrator generator 22. In addition, a predetermined distance is set between the fin 23 and the support body 1. The predetermined distance is determined according to the vibration amplitude of the fin 23 to ensure that the fin 23 does not contact the support body 1 when vibrating.

[0060] The fin 23 is a thin film or sheet material that meets biocompatibility, such as a polymer material (such as polylactic acid, chitosan), a metal material (such as titanium and its alloys), a ceramic material, etc. The fin 23 can reciprocate in the radial direction of the support body 1 driven by the vibrator generator 22, thereby exerting a radial force on the liquid. The specific structure of the fin 23 is designed according to the material of the fin 23 and the force required to squeeze the liquid. The specific structure of the fin 23 mainly includes the fin shape, the fin angle of attack and the fin weight distribution.

[0061] In a preferred embodiment of the present invention, the fin adopts a streamlined sheet structure along its length direction, and the streamlined sheet structure imitates the cross-sectional shape of an aircraft wing, that is, a teardrop-shaped profile. This fin shape helps to improve fluid dynamics performance and optimize fluid flow characteristics. Of course, the fin can also adopt other shapes, such as rectangular, elliptical or circular sheets as shown in the figure.

[0062] Among them, the angle of attack design of the fins will affect the flow direction of the blood. When the fins are placed at a certain angle of attack, the blood that originally flows in a straight line will be deflected to form a curved flow. This change in flow direction will increase the contact area between the blood and the surface of the fins, easily forming smaller-scale lateral vortices and longitudinal vortices generated along the flow direction, thereby changing the flow rate. By changing the size and direction of the angle of attack of the fins, the flow velocity distribution at different positions inside the flow channel will be uneven, causing the liquid to be squeezed into the fluid through hole 12, or not enter the fluid through hole 12 but the flow velocity changes, thereby achieving precise control of the blood flow rate to meet medical needs.

[0063] The present invention utilizes tiny fin vibrations to change the flow direction or velocity of the fluid in the body, which can not only quickly pump blood without damaging cells in the blood, but also improve the local microenvironment. It is also easy to deliver, low in cost, and quick to take effect, and is suitable for different cavity shapes.

[0064] More preferably, the delivery is performed through interventional surgery, so the size of each fin is less than 0.8 mm, which can not only meet the delivery requirements, but also avoid damage to blood cells, and can also form a sufficiently large force to increase or decrease the flow rate or direction of the liquid.

[0065] As a first fin weight distribution scheme, the fin 23 is provided with main reinforcement ribs and secondary reinforcement ribs, and the size of the main reinforcement ribs is larger than the secondary reinforcement ribs. The main reinforcement ribs are arranged along the edges of the fins 23, and the strength of the main reinforcement ribs can be increased to prevent the fins 23 from bending under high-frequency vibration. The secondary reinforcement ribs are arranged on the upper surface or lower surface of the fin 23 (the surface close to the support body 1), or the upper and lower surfaces. The secondary reinforcement ribs can be regularly distributed or irregularly distributed. When blood passes through the surface of the fin 23, the vibration direction of the fin 23 changes slightly due to the action of the secondary reinforcement ribs, thereby affecting the flow of the liquid.

[0066] The ribs are designed to: 1) be arranged along the length of the fin (i.e. the main axis of the fin). This layout ensures that the ribs work along the entire length of the fin, having a continuous and uniform effect on the flow of blood. 2) Use a non-uniformly distributed structure. This design can introduce non-uniformity and directional changes in the blood flow process, thereby generating vortices. The formation of vortices helps to disrupt the laminar state of blood, increase the mixing and disturbance of blood, and thus change the flow velocity distribution. This design also helps to reduce the stagnation of blood on the fin surface, thereby reducing the risk of thrombosis.

[0067] As a second fin weight distribution scheme, multiple film-coated areas (instead of reinforcing ribs) on the fin 23 make different thicknesses in different areas of the fin, thus changing the weight distribution of the fin to a non-uniform distribution. The principle is similar to the aforementioned reinforcing rib design, both of which make different strengths / thicknesses in different areas of the fin, which will not be repeated here.

[0068] As a third fin weight distribution solution, a plurality of grooves are provided on the fin 23, and the weight distribution of the fin 23 is changed by the density or thickness of the grooves. The principle is similar to the aforementioned rib design and will not be described in detail here.

[0069] like Figure 4 and Figure 5 As shown, the one-way valve diaphragm 3 is made of a flexible film material made of metal or polymer material, and is bonded, welded, or hot-melted on the tube body of the catheter 1. The one-way valve diaphragm 3 is arranged on the side of the liquid through hole 12 away from the fin 23, corresponding to the fin 23, and has a shape and size that matches the fluid through hole 12, and can completely cover the fluid through hole 12. That is, the one-way valve diaphragm 3 and the fin 23 are respectively located on both sides of the liquid through hole 12, and cover both sides of the liquid through hole 12 on the catheter 1.

[0070] The thickness of the one-way valve diaphragm 3 can be uniform or uneven. Reinforcing ribs can be added to the one-way valve diaphragm 3, or they may not be provided. The reinforcing ribs can be integrally formed with the one-way valve diaphragm 3, or they can be bonded or welded; the reinforcing ribs can be completely fitted with the one-way valve diaphragm 3, or they can be partially fitted; there can be one reinforcing rib or multiple reinforcing ribs; the thickness of the reinforcing ribs can be uniform, gradual, or uneven; there can be secondary reinforcing ribs connecting the reinforcing ribs, and the thickness of the secondary reinforcing ribs can be uniform, gradual, or uneven; the structure formed by the reinforcing ribs can be fan-shaped, circular, elliptical, or polygonal; the reinforcing ribs can be located in the same plane of the one-way valve diaphragm 3, or in different planes; the reinforcing ribs can be in the same plane or in different planes. By adjusting the thickness of the one-way valve diaphragm 3 at different positions, the gradual thickness of the reinforcing ribs, the hardness of the one-way valve diaphragm 3 and the reinforcing ribs, and the distribution density of the reinforcing ribs, the fluid can be discharged from a preset direction. Alternatively, a weighted membrane may be provided on the one-way valve membrane 3 to adjust the movement form of the one-way valve membrane 3; a guide plate may be provided on the one-way valve membrane 3 to adjust the direction of the fluid.

[0071] In combination with the aforementioned structural design, the working principle and application scenarios of the in vivo liquid flow assisting device provided by the embodiment of the present invention are specifically described below.

[0072] Embodiment 1

[0073] like Figure 6 As shown, the support body 1 in this embodiment is a hollow tube, which is delivered into a cavity such as a blood vessel, a heart or a gallbladder. Liquids such as blood or bile (indicated by arrows in the figure) flow unidirectionally inside and outside the support body 1. The paddle 2 is arranged on the outer wall of the support body 1, and the one-way valve diaphragm 3 is arranged on the inner wall of the support body 1. That is, the fin 23 is located outside the fluid through hole 12 of the support body 1, and the one-way valve diaphragm 3 is located inside the fluid through hole 12.

[0074] Specifically, when powered on, the vibrator generator 22 made of piezoelectric material begins to vibrate and transfers the vibration energy to the fin 23 connected to the vibrator generator 22. As a result, the fin 23 vibrates in a direction perpendicular to or approximately perpendicular to the plane where the fluid through hole 12 corresponding to the fin 23 is located, and amplifies the vibration energy. When the suspended end 231 of the fin 23 moves upward (as shown by the dotted line in the figure), the fin 23 moves away from the fluid through hole 12. At this time, blocked by the one-way valve diaphragm 3, due to the design of the fin, part of the blood on the outside of the support body 1 is sucked between the fin 23 and the one-way valve diaphragm 3. At this time, the suspended end 231 of the fin 23 begins to move downward, generating a downward pressure. The blood sucked between the fin 23 and the one-way valve diaphragm 3 pushes open the one-way valve diaphragm 3 under the action of pressure. That is, the one-way valve diaphragm 3 moves in a direction away from the fin 23 , and at this time, the liquid outside the support body 1 flows into the support body 1 , forming a certain acceleration, which causes the liquid in the support body 1 to move forward.

[0075] In different embodiments of the present invention, the directions of the fins are consistent or opposite. If the directions of the fins are consistent and consistent with the flow direction of the liquid, the fins together accelerate the flow of the liquid; if the directions of the fins are consistent and opposite to the flow direction of the liquid, the fins together slow down the flow of the liquid; if the directions of the fins are opposite, turbulence can be caused in a local area of ​​the liquid, so that tiny solids (such as small thrombi) carried in the liquid will not be deposited in the local area, reducing the risk of thrombus deposition and blockage of blood vessels.

[0076] Since there are many fins 23 on the support body 1, even if each fin 23 only changes the flow rate or flow direction of a small amount of liquid, the total amount of liquid changed by all these fins 23 is sufficient to affect the flow rate of the entire liquid.

[0077] Embodiment 2

[0078] like Figure 7 As shown, the support body 1 in this embodiment is a hollow tube and is arranged in a position close to the vascular endothelium (not shown) (i.e., the right side of the support body in the figure is close to the vascular endothelium). This embodiment is only described by taking the intravascular space as an example, but this does not constitute a limitation of the present invention.

[0079] The blade 2 is arranged on the inner side of the support body 1 (the side close to the axis of the hollow tube), and the one-way valve diaphragm 3 is arranged on the outer side of the conduit 1. Different from the first embodiment, the fin 23 is located on the inner side of the fluid through hole 12 of the conduit 1, and the one-way valve diaphragm 3 is located on the outer side of the fluid through hole 12.

[0080] Specifically, after conducting electricity, the vibrator generator 22 starts to vibrate and transfers the vibration energy to the fin 23 connected to the vibrator generator 22. The fin 23 starts to vibrate and amplifies the vibration energy. When the suspended end 231 of the fin 23 vibrates in a direction away from the fluid through hole 12 (i.e., deforms toward the inside of the hollow tube, as shown by the dotted line in the figure). At this time, part of the blood in the support body 1 is sucked between the fin 23 and the one-way valve diaphragm 3. Then, the suspended end 231 of the fin 23 starts to vibrate toward the fluid through hole 12 (as shown by the solid line in the figure), so that the blood sucked between the fin 23 and the one-way valve diaphragm 3 is blocked by the one-way valve diaphragm 3 and squeezed, thereby pushing the one-way valve diaphragm 3 open. That is, the one-way valve diaphragm 3 moves in a direction away from the fin 23. At this time, the blood inside the support body 1 flows out to the outside of the support body 1, changing the flow direction and flow rate.

[0081] Embodiment 3

[0082] like Fig. 8A and Figure 8B As shown, the support body 1 in this embodiment is a sheet material, which is delivered to a position where one side of the support body 1 (the right side of the support body 1 in the figure) is in close contact with the endocardium, vascular endothelium and gallbladder endothelium 100 of the heart. The paddle 2 is arranged on the other side of the support body 1, and is located on the same side of the support body 1 as the liquid. The paddle 2 can repeatedly move relative to the support body 1 in a direction perpendicular to the surface of the support body 1 to change the flow rate or flow direction of the liquid. Different from the first embodiment, the support body 1 is not provided with a one-way valve diaphragm 3, nor is a fluid through hole 12.

[0083] Since the support body 1 has no fluid through hole 12, the fins 23 squeeze the liquid into between the fins 23 and the support body 1 when vibrating, but the liquid still flows through the outside of the support body 1, that is, the flow direction remains unchanged and only the flow rate changes.

[0084] It should be noted that the extension direction of the fin 23 and the liquid flow direction can not only be in the same direction ( Fig. 8A ), or the opposite direction (as shown Figure 8B When the two are in the same direction, the fin 23 is used to accelerate the flow rate of the liquid; when the two are in opposite directions, the fin 23 is used to reduce the flow rate of the liquid.

[0085] Multiple control wires 4 control the corresponding blades 2 to enter the working state or the stopping state respectively. In the working state, the liquid is driven by the movement of the fins 23 of the blades 2 to change the flow rate; in the stopping state, the blades are stationary so that the liquid flows through the surface of the support body at a constant flow rate.

[0086] Embodiment 4

[0087] like Fig. 9As shown, unlike the third embodiment, the support body 1 in this embodiment is a solid material (such as a sheet or a solid tube), which is placed so that one side of the support body 1 (the right side of the support body 1 in the figure) is in close contact with the endocardium, vascular endothelium and gallbladder endothelium 100 of the heart.

[0088] Similar to the third embodiment, the blade 2 is arranged on the other side of the support 1, and is located on the same side as the liquid. The support 1 is not provided with a one-way valve diaphragm 3, nor is a fluid through hole 12, so only the flow rate of the liquid on one side of the support 1 is changed.

[0089] Embodiment 5

[0090] like Fig.10 As shown, the support body 1 in this embodiment is a hollow tube. The paddle 2 is arranged on the inner side of the support body 1. The support body 1 is not provided with a one-way valve diaphragm 3, nor is a fluid through hole 12, so only the flow rate of the liquid inside the support body 1 is changed.

[0091] Embodiment 6

[0092] like Fig.11 As shown, the in vivo liquid flow assist device in this embodiment is delivered to the gallbladder, for example, and bile flows on both sides of the support body. Each segment includes at least one pair of blades 2, which are respectively located on both sides of the support body 1. The two blades 2 in each pair of blades 2 have the same structure and are staggered along the longitudinal direction of the support body 1 (that is, one-to-one correspondence in the figure). Specifically, in each segment of the support body 1, there are at least two fluid through holes 12, and the two are arranged one-to-one along the longitudinal direction of the support body 1. One blade 2 is configured so that its fin corresponds to one of the fluid through holes 12; the other blade 2 is configured so that its fin corresponds to the other fluid through hole 12. Such a design ensures that the number of blades on both sides of the support body 1 of each segment is equal, so that the flow rate of the liquid on both sides of the support body 1 is the same, for example, for promoting the discharge of bile.

[0093] Embodiment 7

[0094] like Fig.12 and Fig.13 As shown, in the in vivo fluid flow assisting device of this embodiment, the support body 1 includes at least two mutually detachable segments 10. That is, each segment 10 can be detached from each other or connected as one.

[0095] At both ends of the longitudinal direction of each segment 10 of the support body 1, one end is provided with a plurality of connecting holes 101, and at the other end, connecting rods 102 are arranged at intervals at positions corresponding to the connecting holes 11. In the present embodiment, the support body 1 is an octagonal tubular structure, and therefore, there are 8 connecting holes 101 and 4 connecting rods 102 corresponding to the support body 1. It can be understood that the number of connecting holes can be the same as the number of connecting rods, or can be more than the number of connecting rods. Specifically, by inserting the 4 connecting rods 102 on a segment 10 of the support body 1 into the connecting holes 101 of another segment 10, the connection of two or more segments 10 can be achieved, and support bodies 1 of different lengths can be obtained to be suitable for cavities of different lengths.

[0096] In summary, the in vivo liquid flow assist device provided by the embodiment of the present invention adopts multiple distributed liquid extrusion structures. Since the extrusion force of each paddle is very small, but the number is large, the small extrusion force will not affect the cells, and the flow rate or flow direction will not be damaged while changing the flow rate or flow direction; moreover, each paddle can be controlled separately by conducting or disconnecting the power, so the number of fins entering the working state can be accurately controlled according to the required flow rate, thereby accurately controlling the flow rate or flow direction; since the shape of the support body can be pre-formed into various shapes, it can be suitable for cavities of different shapes such as blood vessels, heart, gallbladder, bladder, etc.; connecting rods can also be used to achieve support bodies of different lengths to suit cavities of different lengths.

[0097] The above is a detailed description of the in vivo fluid flow assisting device provided by the present invention. For those skilled in the art, any obvious changes made to it without departing from the essence of the present invention will constitute an infringement of the patent right of the present invention and will bear corresponding legal responsibilities.

Claims

1. A device for assisting the flow of fluid in the body, characterized in that include: A support body having a shape suitable for being placed in the cavity so that liquid flows on the outer surface or the inner surface of the support body, and having a plurality of fluid through holes, the fluid through holes penetrating the outer surface and the inner surface of the support body; A plurality of paddles are fixed to the outer surface and / or the inner surface of the support body and can repeatedly move relative to the support body in a direction perpendicular to the outer surface or the inner surface to change the flow rate or flow direction of the liquid; A plurality of control wires respectively control the paddles to enter a working state or a stopping state. In the working state, the liquid is allowed to flow through the fluid through hole; in the stopping state, the fluid through hole is closed by the paddles and the liquid is prohibited from flowing through the fluid through hole.

2. The in vivo fluid flow assisting device according to claim 1, characterized in that Also includes a one-way valve diaphragm, The one-way valve diaphragm and the paddle are respectively located on both sides of the liquid through hole. The one-way valve membrane is designed to allow the liquid to flow from the paddle through the fluid through hole; and to prohibit the liquid from flowing from the fluid through hole to the paddle.

3. The in vivo fluid flow assisting device according to claim 2, characterized in that: The paddles, the fluid through holes and the one-way valve diaphragm are arranged in one-to-one correspondence.

4. A device for assisting the flow of fluid in the body, characterized in that include: A support having a shape suitable for placement in the cavity so that the liquid flows on the surface of the support; A plurality of paddles are fixed on one side of the support body and are capable of repeatedly moving relative to the support body in a direction perpendicular to the surface of the support body so as to change the flow rate or flow direction of the liquid; A plurality of control wires respectively control the paddles to enter a working state or a stopping state. In the working state, the liquid is driven by the movement of the paddles to change the flow rate; in the stopping state, the paddles are stationary so that the liquid flows through the surface of the support body at a constant flow rate.

5. The in vivo fluid flow assisting device according to any one of claims 1 to 4, characterized in that: Each of the blades includes a fixed base, a vibrator generator and a fin; The fixed base is mounted on the outer surface or the inner surface of the support body; One end of the vibrator generator is connected to the fixed base, and the other end is connected to the fin; The fins vibrate under the drive of the vibrator generator to change the flow rate or flow direction of the liquid.

6. The in vivo fluid flow assisting device according to claim 5, characterized in that: Each of the fins is arranged along the longitudinal direction of the support body, and the directions of the fins are consistent or opposite; the fins are streamlined sheet structures along the length direction thereof.

7. The in vivo fluid flow assisting device according to claim 5, characterized in that: The fins are made of any one or more of piezoelectric material, alloy material or fiber material.

8. The in vivo fluid flow assisting device according to claim 5, characterized in that: A predetermined distance is provided between the fin and the support body; The predetermined distance is determined according to the vibration amplitude of the fin to ensure that the fin does not contact the support body when vibrating.

9. The in vivo fluid flow assisting device according to claim 5, characterized in that: The support body includes a plurality of sections, and each section is provided with a plurality of blades.

10. The in vivo fluid flow assisting device according to claim 9, characterized in that: The segments are designed to be separable from each other or connected as a whole; the blades are evenly distributed on the surface of the segments.

11. The in vivo fluid flow assisting device according to claim 9, characterized in that: At both ends of the longitudinal direction of each segment, one end is provided with a plurality of connection holes, and at the other end, connection rods are arranged at intervals at positions corresponding to the connection holes for inserting into the connection holes of adjacent segments.

12. The in vivo fluid flow assisting device according to claim 5, characterized in that: The fin is provided with main reinforcing ribs and secondary reinforcing ribs, so that the strength of different areas of the fin is different, and the secondary reinforcing ribs are used to adjust the vibration direction of the fin.

13. The in vivo fluid flow assisting device according to claim 5, characterized in that: The fin is provided with a coating area, so that different areas of the fin have different thicknesses.

14. The in vivo fluid flow assisting device according to claim 5, characterized in that: The fins are provided with grooves so that different areas of the fins have different strengths or thicknesses.

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