An in vivo fluid flow assist device

Abstract

The application discloses an in-vivo liquid flow assisting device, which comprises a support body with a shape suitable for being placed in a cavity to make liquid flow on the outer surface or the inner surface of the support body, and is provided with a plurality of fluid through holes penetrating the outer surface and the inner surface of the support body; a plurality of paddles fixed on the outer surface and / or the inner surface of the support body and capable of repeatedly moving in a direction perpendicular to the outer surface or the inner surface relative to the support body to change the flow rate or the flow direction of the liquid; and a plurality of control wires respectively controlling the paddles to enter a working state or a stop state, in the working state, the liquid is allowed to flow through the fluid through holes, and in the stop state, the fluid through holes are closed by the paddles to prohibit the liquid from flowing through the fluid through holes. The application utilizes the vibration of the tiny fins to change the flow direction or the flow rate of the liquid in the body, and realizes the blood pumping quickly without damaging the cells in the blood.

Description

Technical Field

[0001] This invention relates to an assistive device for the flow of fluids within the body, belonging to the field of medical device technology. Background Technology

[0002] With the continuous aging of the population, the number of patients with end-stage heart disease is constantly rising, while drug treatment has limited effectiveness. Therefore, heart transplantation and artificial hearts have become the main means of treating severe heart failure. Although heart transplantation is the ideal option, the shortage of donors limits its application, which has spurred the rapid development of artificial heart technology. Currently, the main artificial heart system used in my country is the left ventricular assist device (LVAD). Studies have shown that the latest products have a 3-year survival rate of up to 80%, approaching the effect of heart transplantation, and are widely used in Europe and the United States.

[0003] An artificial heart system consists of four parts: a blood pump, a drive unit, a monitoring system, and a power source, with the blood pump being the core component. Blood pumps can be classified into pulsatile pumps, axial flow pumps, and centrifugal pumps based on their working principles. Early pulsatile artificial hearts mimicked the contraction and relaxation of the heart, but due to significant damage to the blood, they were prone to complications such as thrombosis and stroke, and were mainly used as a transitional measure before heart transplantation.

[0004] With technological advancements, axial flow pumps and centrifugal pumps have become the mainstream in artificial hearts. Axial flow pumps pump blood using a high-speed rotating impeller, but the high speed can damage blood cells, increasing the risk of thrombosis and stroke. To address this issue, third-generation centrifugal pumps employ technologies such as magnetic fluid suspension, magnetic levitation, and pure water suspension, avoiding direct contact between blood and the bearings and reducing thrombus formation. However, stroke problems still exist in the clinical application of magnetic fluid-suspended artificial hearts, which may be related to the shear stress of blood in the secondary flow channel. This shear stress exceeds physiological conditions, causing mechanical damage to the formed elements in the blood.

[0005] Given the limitations of current technology, researchers are seeking to develop a novel interventional intravascular fluid flow assist device. This device should be able to effectively assist blood flow without damaging cells in the blood, in order 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 an auxiliary device for the flow of fluid in the body.

[0007] To achieve the above-mentioned technical objectives, the present invention adopts the following technical solution:

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

[0009] A support body has a shape suitable for insertion into a cavity to allow liquid to flow on the outer or inner surface of the support body, and is provided with a plurality of fluid through holes that penetrate the outer and inner surfaces of the support body;

[0010] Multiple blades are fixed to the outer and / or inner surfaces of the support body, and can move repeatedly relative to the support body in a direction perpendicular to the outer or inner surfaces, so as to change the flow rate or direction of the liquid.

[0011] Multiple control wires control the blades to enter either a working state or a stopped state. In the working state, the liquid is allowed to flow through the fluid passage; in the stopped state, the fluid passage is closed by the blades, preventing the liquid from flowing through the fluid passage.

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

[0013] The one-way valve diaphragm and the impeller are located on opposite sides of the liquid passage.

[0014] The one-way valve diaphragm is designed to allow the liquid to flow from the blade through the fluid through-hole, and to prevent the liquid from flowing from the fluid through-hole to the blade.

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

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

[0017] A support having a shape suitable for insertion into a cavity to allow liquid to flow on the surface of the support;

[0018] Multiple blades are fixed to one side of the support and can move repeatedly relative to the support in a direction perpendicular to the surface of the support, so as to change the flow rate or direction of the liquid.

[0019] Multiple control wires control the blades to enter a working state or a stopped state. In the working state, the liquid is driven by the movement of the blades to change its flow rate. In the stopped state, the blades are stationary so that the liquid flows over the surface of the support body at a constant flow rate.

[0020] Preferably, each of the blades includes a fixed base, an oscillator generator, and fins;

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

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

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

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

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

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

[0027] The predetermined distance is determined based on the vibration amplitude of the fins to ensure that the fins do not come into contact with the support body when they vibrate.

[0028] Preferably, the support body includes multiple segments, and each segment is provided with multiple blades.

[0029] Preferably, 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.

[0030] Preferably, each segment has multiple connecting holes at one end along its longitudinal direction, and connecting rods are spaced apart at the other end corresponding to the connecting holes, for insertion into the connecting holes of adjacent segments.

[0031] Preferably, 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. Alternatively, the fin is provided with a coated area, so that the thickness of different areas of the fin is different. Alternatively, the fin is provided with grooves, so that the strength or thickness of different areas of the fin is different.

[0032] Compared with the prior art, the in vivo fluid flow assist device provided in this embodiment of the invention adopts multiple distributed liquid extrusion structures. Since the extrusion force of each blade is very small, but the number is large, the small extrusion force will not affect the cells, and the cells are avoided from being damaged while changing the flow rate or direction. Moreover, each blade can be controlled by conducting or de-energizing, so the number of blades entering the working state can be precisely controlled according to the required flow rate, thereby accurately controlling the flow rate or direction. Since the support body can be pre-formed into various shapes, it can be adapted to cavities of different shapes such as blood vessels, heart, gallbladder, and bladder. Support bodies of different lengths can also be realized by using connecting rods to adapt to cavities of different lengths. Attached Figure Description

[0033] Figure 1 This is a partial structural schematic diagram of the in vivo fluid flow assist device provided in an embodiment of the present invention;

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

[0035] Figure 3 for Figure 2 A side view of the internal fluid flow assist device shown.

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

[0037] Figure 5 for Figure 4 A top view schematic diagram of the internal fluid flow assist device shown;

[0038] Figure 6 for Figure 1 The diagram shows an application scenario where liquids are present both inside and outside the body in the internal fluid flow assist device.

[0039] Figure 7 for Figure 1 The diagram shows an application scenario of diverting internal fluid in an in vivo fluid flow assist device.

[0040] Figure 8A for Figure 1 The diagram shows an application scenario where a liquid on one side is accelerated in an in vivo fluid flow assist device.

[0041] Figure 8B for Figure 1 The diagram shows an application scenario where the fluid on one side is slowed down in the in vivo fluid flow assist device.

[0042] Figure 9 for Figure 1 The diagram shows an application scenario where the support structure of the in vivo fluid flow assist device is a solid structure.

[0043] Figure 10 for Figure 1 The diagram shown illustrates an application scenario for an in vivo fluid flow assist device, which only contains internal fluid.

[0044] Figure 11 for Figure 1 The diagram shows an application scenario of accelerating the liquid on both sides in the in vivo fluid flow assist device.

[0045] Figure 12This is a partial structural schematic diagram of the in vivo fluid flow assist device provided in an embodiment of the present invention;

[0046] Figure 13 for Figure 12 The diagram shows another angle of the internal fluid flow assist device. Detailed Implementation

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

[0048] The in vivo fluid flow assist device provided in this invention is used to deliver fluid to a target location via the femoral or radial artery, and then change the flow rate or direction of the fluid at that location. One application scenario is implantation into the heart (e.g., the left ventricle). Multiple blades on the in vivo fluid flow assist device work together to squeeze blood, pumping it out of the aorta and achieving cardiac contraction; the blades then close to achieve cardiac diastole. A second application scenario is implantation into a blood vessel with minor vascular embolism. The alternating operation of the multiple blades accelerates blood flow, helps flush the vessel wall, reduces thrombus formation, relieves discomfort, and promotes collateral circulation. A third application scenario is implantation into the gallbladder to promote bile excretion. A fourth application scenario is the treatment of varicose veins, acting as venous valves to prevent blood backflow. These are just examples; other applications are also possible.

[0049] The following explanation will take the intervention of blood flow velocity within blood vessels as an example.

[0050] like Figure 1 and Figure 2 As shown, this embodiment of the invention discloses an in vivo fluid flow assist device, which includes a support body 1, multiple blades 2, a one-way valve diaphragm 3, and a control wire 4. In this embodiment, the control wire 4 is a conductive wire that extends along the longitudinal direction of the support body 1, with one end connected to a power source inside the handle to supply power to each blade 2, thereby causing each blade 2 to enter a working state (when energized) or a closed state (when de-energized). It should be noted that because this is a temporary auxiliary intervention for fluids such as blood (not a long-term implantation), the materials and shape of the in vivo fluid flow assist device will not cause embolism or other problems.

[0051] The support 1 is made of implantable polymer, ceramic, silicon, or metal materials. The support 1 can be tubular, strip-shaped, plate-shaped, or other shapes suitable for insertion into cavities, determined by its implantation location within the body. Furthermore, the support 1 can be composed of any combination of hollow tubes, multi-cavity tubes, or other types of conduits. The support 1 is manufactured using techniques such as cutting, carving, and splicing to alter its structure, achieving a balance between flexibility and rigidity. In this embodiment, an octagonal tubular structure of the support 1 is used as an example, but this does not constitute a limitation of the invention.

[0052] Optionally, the support body 1 includes a flexible segment, a working segment, and a connecting segment connected in sequence. The flexible segment is located at the distal end of the support body 1 and extends along the length of the support body 1 to reduce damage to surrounding tissues. The connecting segment connects to the working segment and is also connected to the handle / connector. The working segment is located between the flexible segment and the connecting segment. The support body 1 has a shape suitable for insertion into the cavity, and the anatomical structure of the implantation site is the same. Due to the conformal material of the support body 1, the paddle 2 can be fixed in the target position. Another alternative is to have only the working segment, without the flexible segment and connecting segment.

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

[0054] It should be noted that the working section is equipped with multiple blades 2, which are evenly distributed throughout the working section and can be arranged in a matrix, staggered, or spiral pattern. Figure 1 (As shown). Furthermore, the blade 2 can be disposed on the outer surface or the inner surface of the support 1, or it can be disposed on both the outer surface and the inner surface of the support 1.

[0055] like Figure 3 and Figure 4As shown, the blade 2 includes a fixed base 21, an oscillator generator 22, and fins 23. By operating the handle, the control wire 4 energizes or de-energizes each blade 2, causing the energized blade 2 to enter the working state (in this embodiment, the open state, allowing liquid to flow through the fluid passage 12), and the de-energized blade 2 to stop working (in this embodiment, the closed state). However, it is also possible to close when energized and open when de-energized. In this way, all blades 2 can work simultaneously or sequentially, thereby accelerating or decelerating the blood, or changing the direction of liquid flow.

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

[0057] The number (N) of the fixed base 21, the oscillator generator 22, and the fins 23 are in one-to-one correspondence and are less than or equal to the number (M) of the fluid through holes 12, that is, N≤M.

[0058] One end of the oscillator 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 oscillator generator 22 and the support body 1. When energized, the oscillator generator 22 vibrates to drive the fin 23 to vibrate. It should be noted that after the oscillator generator 22 is energized, the vibration frequency of the oscillator generator 22 is 10Hz to 1000KHz, preferably 10KHz to 100KHz. This vibration frequency is determined according to the fin material and the expected liquid flow rate.

[0059] The fins 23 can be made of any one or more of piezoelectric materials, alloy materials, or fiber materials, and their shape can be sheet-like or biomimetic wing-like, conforming to fluid dynamics. The fins 23 cover the outer or inner side of the fluid passage 12 on the support 1, and their shape and size are sufficient to completely cover the fluid passage 12. The outer side of one end of the fin 23 (the side away from the support) is connected or bonded to the inner side of one end of the oscillator generator 22 (the side closer to the support). That is, the fins 23 are located between the support 1 and the oscillator generator 22. Furthermore, a predetermined distance is provided between the fins 23 and the support 1. This predetermined distance is determined according to the vibration amplitude of the fins 23 to ensure that the fins 23 do not contact the support 1 when vibrating.

[0060] The fins 23 are made of thin, biocompatible membrane or sheet materials, such as polymers (e.g., polylactic acid, chitosan), metals (e.g., titanium and its alloys), ceramics, etc. Driven by the oscillator generator 22, the fins 23 reciprocate in the radial direction of the support 1, thereby applying a radial force to the liquid. The specific structure of the fins 23 is designed based on the material of the fins 23 and the magnitude of the force required to compress the liquid. The specific structure of the fins 23 mainly includes the fin shape, fin angle of attack, and fin weight distribution.

[0061] In a preferred embodiment of the invention, the fins employ a streamlined, sheet-like structure along their length, which mimics the cross-sectional shape of an aircraft wing, i.e., a teardrop-shaped profile. This fin shape helps improve hydrodynamic performance and optimize fluid flow characteristics. Of course, the fins can also adopt other shapes, such as rectangular, elliptical, or circular sheets as shown in the figure.

[0062] The angle of attack design of the fins affects the direction of blood flow. When the fins are placed at a certain angle of attack, the originally straight flow of blood is deflected, forming a curved flow. This change in flow direction increases the contact area between the blood and the fin surface, making it easier to form small-scale transverse vortices and longitudinal vortices along the flow direction, thereby changing the flow velocity. By changing the size and direction of the fin angle of attack, uneven flow velocity distribution occurs at different locations within the flow channel. This causes liquid to be forced into the fluid through-hole 12, or its flow velocity to change even if it does not enter the fluid through-hole 12, thus achieving precise control of blood flow velocity to meet medical needs.

[0063] This invention utilizes minute fin vibrations to alter the flow direction or velocity of bodily fluids. It can rapidly pump blood without damaging cells in the blood, improve the local microenvironment, and is convenient to deliver, low in cost, fast-acting, and suitable for different cavity shapes.

[0064] More preferably, delivery is performed via interventional surgery, so each fin is less than 0.8 mm in size, which can meet the delivery requirements, avoid damage to blood cells, and generate a sufficiently large force to increase or decrease the flow rate or direction of the liquid.

[0065] As the first fin weight distribution scheme, fin 23 is provided with main reinforcing ribs and secondary reinforcing ribs, with the main reinforcing ribs being larger than the secondary reinforcing ribs. The main reinforcing ribs are arranged along the edge of fin 23, and by increasing the strength of the main reinforcing ribs, bending of fin 23 under high-frequency vibration can be prevented. The secondary reinforcing ribs are arranged on the upper or lower surface (near the surface of support 1), or both surfaces of fin 23. The secondary reinforcing ribs can be regularly distributed or irregularly distributed. When blood passes over the surface of fin 23, the vibration direction of fin 23 changes slightly due to the action of the secondary reinforcing ribs, thereby affecting the flow of liquid.

[0066] The reinforcing ribs are designed to: 1) be arranged along the length of the fin (i.e., the main axis of the fin). This arrangement ensures that the reinforcing ribs function along the entire length of the fin, providing a continuous and uniform effect on blood flow. 2) employ a non-uniformly distributed structure. This design introduces non-uniformity and directional changes during blood flow, thereby generating vortices. The formation of vortices helps disrupt the laminar flow state of the blood, increasing blood mixing and turbulence, thus altering the velocity distribution. This design also helps reduce blood stagnation on the fin surface, thereby reducing the risk of thrombosis.

[0067] As a second fin weight distribution scheme, multiple coated areas (replacing reinforcing ribs) on fin 23 result in different thicknesses in different areas of the fin, thus altering the fin's weight distribution to a non-uniform one. The principle is similar to the aforementioned reinforcing rib design, both resulting in different strengths / thicknesses in different areas of the fin, and will not be elaborated upon here.

[0068] As a third fin weight distribution scheme, fin 23 is provided with multiple grooves, and the weight distribution of fin 23 is changed by the density or thickness of the grooves. Its principle is similar to that of the aforementioned reinforcing rib design, and will not be elaborated here.

[0069] like Figure 4 and Figure 5 As shown, the one-way valve diaphragm 3 is made of a flexible thin film material of metal or polymer, and is bonded, welded, or thermally fused to the tube body of the conduit 1. The one-way valve diaphragm 3 is located on the side of the liquid passage 12 away from the fin 23, corresponding to the fin 23, and its shape and size are adapted to the fluid passage 12, completely covering the fluid passage 12. That is, the one-way valve diaphragm 3 and the fin 23 are located on both sides of the liquid passage 12, respectively, and cover both sides of the liquid passage 12 on the conduit 1.

[0070] The thickness of the one-way valve diaphragm 3 can be uniform or non-uniform. Reinforcing ribs can be added to the one-way valve diaphragm 3, or they can be glued or welded to it. The reinforcing ribs can be completely or partially attached to the one-way valve diaphragm 3. There can be one or multiple reinforcing ribs. The thickness of the reinforcing ribs can be uniform, gradually changing, or non-uniform. Secondary reinforcing ribs can connect the reinforcing ribs; the thickness of these secondary reinforcing ribs can be uniform, gradually changing, or non-uniform. The structure formed by the reinforcing ribs can be fan-shaped, circular, elliptical, or polygonal. The reinforcing ribs can be located on the same plane or on different planes of the one-way valve diaphragm 3. The reinforcing ribs can be on the same plane or on different planes. By adjusting the thickness of the one-way valve diaphragm 3 at different positions, the gradually changing 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 in a preset direction. Alternatively, a counterweight membrane can be provided on the one-way valve diaphragm 3 to adjust the motion of the one-way valve diaphragm 3; a guide vane can be provided on the one-way valve diaphragm 3 to adjust the fluid direction.

[0071] The working principle and application scenarios of the in vivo fluid flow assist device provided in the embodiments of the present invention will be explained in detail below with reference to the aforementioned structural design.

[0072] Example 1

[0073] like Figure 6 As shown, in this embodiment, the support 1 is a hollow tube, which is inserted into cavities such as blood vessels, the heart, or the middle of the gallbladder. Liquids such as blood or bile (indicated by arrows in the figure) flow unidirectionally inside and outside the support 1. The blades 2 are disposed on the outer wall of the support 1, and the one-way valve diaphragm 3 is disposed on the inner wall of the support 1. That is, the fins 23 are located outside the fluid passage 12 of the support 1, and the one-way valve diaphragm 3 is located inside the fluid passage 12.

[0074] Specifically, when energized, the piezoelectric oscillator 22 begins to vibrate, transferring vibrational energy to the fins 23 connected to it. The fins 23 then vibrate in a direction perpendicular or approximately perpendicular to the plane of the fluid passage 12 corresponding to them, amplifying the vibrational energy. When the suspended end 231 of the fin 23 moves upward (shown by the dotted line in the figure), the fin 23 moves away from the fluid passage 12. At this time, due to the one-way valve diaphragm 3, some blood from the outside of the support 1 is drawn into the space between the fins 23 and the one-way valve diaphragm 3, blocked by the fin design. Then, the suspended end 231 of the fin 23 begins to move downward, generating downward pressure. The blood drawn into the space between the fins 23 and the one-way valve diaphragm 3 is pushed open by this pressure. That is, the one-way valve diaphragm 3 moves away from the fin 23. At this time, the liquid outside the support body 1 flows into the support body 1, forming a certain acceleration, which causes the liquid inside the support body 1 to move forward.

[0075] In different embodiments of the invention, the orientation of each fin is the same or opposite. If the orientation of each fin is the same and consistent with the flow direction of the liquid, the numerous fins together accelerate the flow of the liquid; if the orientation of each fin is the same and opposite to the flow direction of the liquid, the numerous fins together slow down the flow of the liquid; if the orientation of each fin is opposite, turbulence can be generated in a local area of ​​the liquid, so that small solids (such as small blood clots) carried in the liquid will not deposit in that local area, reducing the risk of blood clot deposition leading to blood vessel blockage.

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

[0077] Example 2

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

[0079] The blade 2 is located inside the support 1 (on the side closest to the axis of the hollow tube), and the one-way valve diaphragm 3 is located outside the conduit 1. Unlike Embodiment 1, the fin 23 is located inside the fluid passage 12 of the conduit 1, and the one-way valve diaphragm 3 is located outside the fluid passage 12.

[0080] Specifically, after conduction, the oscillator generator 22 begins to vibrate, transferring vibrational energy to the fins 23 connected to it. The fins 23 then vibrate, amplifying the vibrational energy. When the suspended end 231 of the fin 23 vibrates away from the fluid passage 12 (i.e., deforms towards the interior of the hollow tube, as shown by the dotted line in the figure), some blood inside the support 1 is drawn into the space between the fins 23 and the one-way valve diaphragm 3. Then, the suspended end 231 of the fin 23 begins to vibrate towards the fluid passage 12 (as shown by the solid line in the figure), causing the blood drawn into the space between the fins 23 and the one-way valve diaphragm 3 to be compressed by the one-way valve diaphragm 3, thus pushing the one-way valve diaphragm 3 open. That is, the one-way valve diaphragm 3 moves away from the fins 23, at which point the blood inside the support 1 flows out to the outside of the support 1, changing its direction and velocity.

[0081] Example 3

[0082] like Figure 8A and Figure 8B As shown, in this embodiment, the support 1 is a sheet material, delivered to a position where one side of the support 1 (the right side of the support 1 in the figure) is in close contact with the endocardium, vascular endothelium, and gallbladder endothelium 100 of the heart. The paddle 2 is disposed on the other side of the support 1, on the same side as the liquid. The paddle 2 can move repeatedly relative to the support 1 in a direction perpendicular to the surface of the support 1, thereby changing the flow rate or direction of the liquid. Unlike Embodiment 1, the support 1 does not have a one-way valve diaphragm 3, nor does it have a fluid passage 12.

[0083] Since the support body 1 does not have fluid passage holes 12, when the fin 23 vibrates, the liquid is squeezed into the space between the fin 23 and the support body 1, but the liquid still flows through the outside of the support body 1, that is, the flow direction remains unchanged, only the flow rate changes.

[0084] It should be noted that the extension direction of fin 23 and the liquid flow direction can not only be the same direction ( Figure 8A As shown), it can also be in the opposite direction (as shown). Figure 8B (As shown). When the two are in the same direction, fin 23 is used to accelerate the flow rate of the liquid; when the two are in opposite directions, 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 stop 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 stop state, the blades are stationary so that the liquid flows over the surface of the support body at a constant flow rate.

[0086] Example 4

[0087] like Figure 9As shown, unlike Embodiment 3, the support 1 in this embodiment is made of solid material (e.g., sheet or solid tube) and is placed in a position where one side of the support 1 (the right side of the support 1 in the figure) is in close contact with the endocardium, vascular endothelium and gallbladder endothelium 100 of the heart.

[0088] Similar to Embodiment 3, the blade 2 is located on the other side of the support 1, on the same side as the liquid. No one-way valve diaphragm 3 or fluid passage 12 is provided on the support 1; therefore, the change only alters the flow rate of the liquid on one side of the support 1.

[0089] Example 5

[0090] like Figure 10 As shown, the support 1 in this embodiment is a hollow tube. The blade 2 is disposed inside the support 1. The support 1 does not have a one-way valve diaphragm 3 or a fluid passage 12, so it only changes the flow rate of the liquid inside the support 1.

[0091] Example 6

[0092] like Figure 11 As shown, the in vivo fluid flow assist device in this embodiment, for example, delivers bile into the gallbladder, with bile flowing on both sides of the support. Each segment includes at least one pair of blades 2, located on both sides of the support 1. The two blades 2 in each pair have identical structures and are staggered along the longitudinal direction of the support 1 (i.e., one-to-one correspondence in the figure). Specifically, each segment of the support 1 has at least two fluid through-holes 12, arranged one-to-one along the longitudinal direction of the support 1. One blade 2 is configured such that its fins correspond to one of the fluid through-holes 12; the other blade 2 is configured such that its fins correspond to the other fluid through-hole 12. This design ensures that the number of blades on both sides of the support 1 in each segment is equal, resulting in the same flow rate of fluid on both sides of the support 1, for example, to promote bile drainage.

[0093] Example 7

[0094] like Figure 12 and Figure 13 As shown, in this embodiment, the in vivo fluid flow assist device includes a support body 1 comprising at least two detachable segments 10. That is, each segment 10 can be separated from the others or connected as a single unit.

[0095] Each segment 10 of the support body 1 has multiple connecting holes 101 at one end along its longitudinal direction, and connecting rods 102 are spaced apart at the other end corresponding to the connecting holes 11. In this embodiment, the support body 1 is an octagonal tubular structure, therefore, the support body 1 has 8 connecting holes 101 and 4 connecting rods 102. It can be understood that the number of connecting holes can be the same as or more than the number of connecting rods. Specifically, by inserting the 4 connecting rods 102 on one segment 10 of the support body 1 into the connecting holes 101 of another segment 10, two or more segments 10 can be connected to obtain support bodies 1 of different lengths to suit cavities of different lengths.

[0096] In summary, the in vivo fluid flow assist device provided in this embodiment of the invention employs multiple distributed fluid extrusion structures. Because the extrusion force of each blade is small, but the number is large, the small extrusion force will not affect the cells, thus avoiding cell damage while changing the flow rate or direction. Furthermore, each blade can be controlled independently by conducting or de-energizing the flow, allowing precise control of the number of blades entering the working state according to the required flow rate, thereby precisely controlling the flow rate or direction. Since the support body can be pre-formed into various shapes, it can be adapted to cavities of different shapes, such as blood vessels, the heart, gallbladder, and bladder. Connecting rods can also be used to achieve supports of different lengths to suit cavities of varying lengths.

[0097] The in vivo fluid flow assist device provided by the present invention has been described in detail above. Any obvious modifications made to this invention by those skilled in the art without departing from its essential content will constitute an infringement of the patent rights of this invention and will incur corresponding legal liability.

Claims

1. An in-vivo fluid flow assist device, characterized by It comprises: a support body with a shape suitable for being placed in a cavity to make liquid flow on the outer surface or inner surface of the support body, and provided with a plurality of fluid through holes penetrating the outer surface and the inner surface of the support body; a plurality of paddles fixed on the outer surface and / or the inner surface of the support body and capable of repeatedly moving in a direction perpendicular to the outer surface or the inner surface of the support body relative to the support body to change the flow rate or flow direction of the liquid; a plurality of control wires respectively controlling the paddles to enter a working state or a stop state, in the working state, the liquid is allowed to flow through the fluid through holes; in the stop state, the fluid through holes are closed by the paddles to prohibit the liquid from flowing through the fluid through holes; each of the paddles comprises 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 with the fixed base, and the other end is connected with the fin; the fin vibrates under the driving of the vibrator generator to change the flow rate or flow direction of the liquid; the fin has different fin weight distributions to change the flow direction and flow rate of the liquid, a one-way valve diaphragm is arranged on one side of the fluid through hole, and the paddle, the fluid through hole and the one-way valve diaphragm are arranged one by one.

2. The in-vivo liquid flow assisting device according to claim 1, wherein: the diameter of the fluid through hole is determined according to the vibration frequency, size of the fin and required flow rate.

3. The in vivo fluid flow assist device of claim 2, wherein further comprising a one-way valve diaphragm, the one-way valve diaphragm and the paddle are respectively located on both sides of the fluid through hole, the one-way valve diaphragm is designed to allow the liquid to flow from the paddle through the fluid through hole; and prohibit the liquid from flowing from the fluid through hole to the paddle.

4. The in-vivo liquid flow assisting device according to claim 1, wherein: each of the fins is arranged along the longitudinal direction of the support body, the respective orientations of the fins are consistent or opposite; the fin is a streamlined sheet structure along the length direction thereof.

5. The in-vivo liquid flow assisting device according to claim 1, wherein: the fin adopts any one or more of piezoelectric material, alloy material or fiber material.

6. The in-vivo liquid flow assisting device according to claim 1, wherein: 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.

7. The in-vivo liquid flow assisting device according to claim 1, wherein: the support body comprises a plurality of segments, each segment is provided with a plurality of paddles.

8. The in-vivo liquid flow assisting device according to claim 7, wherein: the segments are designed to be detachable and connectable as a whole; the paddles are uniformly distributed on the surface of the segments.

9. The in-vivo liquid flow assisting device according to claim 7, wherein: Two ends of each of the segments in the longitudinal direction, one of which is provided with a plurality of connecting holes, and the other of which is provided with connecting rods at positions corresponding to the connecting holes, for insertion into the connecting holes of adjacent segments.

10. The in vivo fluid flow assist device of claim 1, wherein: The fin is provided with a main reinforcing rib and a secondary reinforcing rib, so that the strength of different regions of the fin is different, and the secondary reinforcing rib is used to adjust the vibration direction of the fin.

11. The in vivo fluid flow assist device of claim 1, wherein: The fin is provided with a film-covered region, so that the thickness of different regions of the fin is different.

12. The in vivo fluid flow assist device of claim 1, wherein: The fin is provided with a groove, so that the strength or thickness of different regions of the fin is different.

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