A hemodialysis coagulation-inhibiting device based on a porous modified material

Abstract

This invention discloses a hemodialysis coagulation inhibition device based on porous modified materials, relating to the field of dialysis technology. It includes a housing with an upper cover and a lower cover fixedly installed at its upper and lower ends, respectively. An exchange chamber and an expansion chamber are interconnected within the housing. A porous modified material filter element is installed within the exchange chamber, with its bottom fixed to the housing and its top floating within the exchange chamber. An overflow pipe extending into the expansion chamber is fixedly installed on the exchange chamber. A Venturi drain pipe is fixedly installed at the bottom of the expansion chamber. This invention achieves mainstream bubble separation of the dialysate through a spiral guide plate, and the micro-negative pressure formed by the Venturi drain pipe and the suction pipe continuously removes gas from the expansion chamber. The porous filter membrane filaments oscillate, disturbing the flow field and peeling away microbubbles in dead corners of the membrane surface. These three elements work together to achieve deep degassing throughout the entire area. Furthermore, the reduction in bubbles reduces membrane surface deposits, further assisting in anticoagulation.

Description

Technical Field

[0001] This invention belongs to the field of dialysis technology, specifically, it relates to a hemodialysis coagulation inhibition device based on porous modified materials. Background Technology

[0002] Hemodialysis is an important renal replacement therapy for patients with end-stage renal disease. During dialysis, protein adsorption, platelet activation, and coagulation reactions can easily occur at the interface between blood and dialysis membrane, which seriously affect the safety and efficacy of dialysis.

[0003] To inhibit blood clotting, patent application number 201580052925.3 was published on August 9, 2019, as a hollow fiber membrane blood purification device. This device is a hollow fiber membrane blood purification device formed by filling a container with a hollow fiber membrane. The hollow fiber membrane contains hydrophobic polymers, hydrophilic polymers, and lipid-soluble substances. The amount of lipid-soluble substances on the inner surface of the hollow fiber membrane is more than 10 mg / m2 and less than 300 mg / m2, and the oxygen permeability coefficient of the container is less than 1.8 × 10-10 cm3·cm / (cm2·s·cmHg).

[0004] Although the aforementioned devices reduce the risk of coagulation through material modification, microbubbles still continuously precipitate from the dialysate during heating, depressurization, and solute exchange. Simultaneously, gas may be introduced or generated on the blood side due to insufficient tubing prefilling or blood flow disturbance. Once generated, the gas cannot be discharged in a timely and complete manner, easily accumulating and merging into large bubbles in the membrane fiber chambers and dead corners of the flow channels. These bubbles not only induce air embolism and increase the risk of coagulation, but also crowd out the effective membrane area and interfere with the flow distribution of dialysate, leading to a decrease in solute clearance rate and unstable dialysis efficiency. In severe cases, they may even interrupt treatment and threaten the patient's life. In view of the above problems, a hemodialysis coagulation inhibition device based on porous modified materials is proposed. Summary of the Invention

[0005] The technical problem to be solved by the present invention is to overcome the shortcomings of the prior art and provide a hemodialysis coagulation inhibition device based on porous modified materials that can overcome or at least partially solve the above problems.

[0006] To solve the above-mentioned technical problems, the basic concept of the technical solution adopted by the present invention is as follows: A hemodialysis coagulation inhibition device based on porous modified materials includes a housing, with an upper cover and a lower cover fixedly installed at the upper and lower ends of the housing, respectively. An exchange chamber and an expansion chamber are disposed within the housing and communicate with each other. A porous modified material filter element is disposed within the exchange chamber, with its bottom fixed to the housing and its top floating within the exchange chamber. An overflow pipe extending into the expansion chamber is fixedly installed on the exchange chamber. A Venturi drain pipe is fixedly installed at the bottom of the expansion chamber, and an air inlet pipe is fixedly installed on its side wall, with its inlet end connected to the top of the side wall of the expansion chamber. A gas-liquid separation section is disposed within the housing, with its exhaust end communicating with the expansion chamber.

[0007] Preferably, the gas-liquid separation unit includes a gas-liquid separation chamber disposed within the housing, and a gas guiding chamber with a high periphery and a low center is disposed at the top of the gas-liquid separation chamber; an exhaust hose is fixedly installed on the inner wall of the housing, the top of the exhaust hose extends into the expansion chamber, and the exhaust port of the exhaust hose is higher than the liquid outlet of the overflow pipe, and the air inlet end of the exhaust hose is connected to the top of the gas guiding chamber; a spiral guide plate is fixedly installed inside the gas-liquid separation chamber, and a liquid inlet communicating with the exchange chamber is disposed at the top of the side wall of the gas-liquid separation chamber, the position of the liquid inlet being higher than the spiral guide plate and lower than the gas guiding chamber.

[0008] Preferably, the spiral blades of the spiral guide plate are inclined at an angle of 10°-15° relative to the horizontal plane, forming a sloping structure that is high around the edges and low in the middle. The bubbles separated from the dialysate gather along the sloping surface towards the cylinder wall and enter the gas guiding chamber. The gas guiding chamber is discharged into the expansion chamber through the exhaust hose.

[0009] Preferably, an inlet pipe is fixedly installed on the side wall of the shell. The inlet pipe is connected to the gas-liquid separation chamber. The dialysate entering the gas-liquid separation chamber through the inlet pipe flows spirally upward along the spiral guide plate to achieve preliminary separation of the gas and liquid phases.

[0010] Preferably, the porous modified material filter element includes a porous filter membrane bundle, a floating connector fixedly installed on the top of the porous filter membrane bundle, and a fixed connector fixedly installed on the bottom of the porous filter membrane bundle; a float is fixedly installed at the bottom of the floating connector, an inlet blood vessel is fixedly installed at the top of the floating connector, and an outlet blood vessel is fixedly installed at the bottom of the fixed connector.

[0011] Preferably, the inlet tube is fixedly connected to and sealed with the upper shell cover, and the outlet tube is fixedly connected to and sealed with the lower shell cover. The inlet tube is a flexible tube. When the dialysate is discharged through the overflow tube, the floating connector is offset by 1mm to 3mm in any direction within the horizontal plane of the overflow tube outlet under the drive of the flowing dialysate. The inlet tube swings with the floating connector.

[0012] Preferably, when the floating joint swings, it drives the porous filter membrane filament bundle to swing synchronously to eliminate the static boundary layer on the membrane surface. At the same time, the exhaust hose serves as a limiting structure and a rebound structure, constraining the movement stroke of the floating joint while driving the floating joint to rebound.

[0013] Preferably, the housing is provided with a snap-fit ​​groove, the fixed connector is snapped into the snap-fit ​​groove, and a locking block is threaded into the snap-fit ​​groove, the locking block abutting against the bottom of the fixed connector for fixation.

[0014] Preferably, the fixed connector is provided with a first drain hole that runs vertically through the joint, and the locking block is provided with a second drain hole that runs vertically through the joint. When the locking block is fixed to the fixed connector, the first drain hole and the second drain hole coincide. A bottom drain pipe is fixedly installed at the bottom of the lower cover, and a flow regulating valve is provided on the bottom drain pipe.

[0015] Preferably, a connecting shaft is fixedly installed on the outer wall of the expansion cavity, and a connecting plate is fixedly installed on the connecting shaft; before pumping blood into the porous modified material filter element, the housing is rotated 180° so that the upper shell cover faces downwards before pumping blood. After the blood enters the porous filter membrane bundle or draining blood vessel, the housing is driven to rotate 180° so that the upper shell cover faces upwards. Under the action of the dialysate, blood, and the gravity of the device itself, the end face of the overflow tube is parallel to the ground.

[0016] The present invention has at least the following beneficial effects: This invention achieves the separation of mainstream bubbles in the dialysate through a spiral guide plate, while the micro-negative pressure formed by the Venturi drain tube and the suction tube continuously removes gas from the extended cavity. The porous filter membrane filament bundle oscillates to disturb the flow field and peel off microbubbles in dead corners of the membrane surface. The three work together to achieve deep degassing throughout the entire area. Furthermore, the reduction of bubbles can reduce the amount of deposits on the membrane surface, further assisting in preventing coagulation.

[0017] This invention reduces the probability of blood cell and protein adhesion at the source by modifying the porous filter membrane bundles, which is a passive protection. The floating connector drives the porous filter membrane bundles to swing, actively flushing away the deposits on the membrane surface and breaking down the static boundary layer. The combination of the two constructs a dual anticoagulation system, which significantly reduces the risk of thrombosis.

[0018] This invention utilizes a Venturi drain tube and a suction tube to both extract gas and prevent cavitation, while simultaneously reducing the oscillation resistance of the floating connector and the porous membrane bundle, making dynamic rinsing more flexible and stable. The oscillation of the porous membrane bundle disturbs the flow field, disrupts liquid surface tension, and promotes the full release of dissolved gas from the liquid phase. The released gas is then rapidly discharged with the aid of a slight negative pressure, further enhancing the overall gas-liquid separation effect. This achieves bidirectional and synergistic enhancement of negative pressure degassing and membrane bundle oscillation. Furthermore, the negative pressure extraction of gas drives gas flow within the extended chamber. The flowing gas, along with the venting hose and the liquid flow disturbance during dialysate discharge, continuously exerts multidirectional thrust on the floating connector, making its reciprocating oscillation more continuous and uniform, strengthening the membrane surface rinsing effect, continuously inhibiting protein and platelet adhesion and aggregation, and further enhancing coagulation inhibition capacity.

[0019] This invention allows for the online discharge of impurities from the flow channel by opening the flow regulating valve, preventing impurities from clogging the porous filter membrane filament bundles and inducing local coagulation. The filter element's excellent coagulation inhibition ability also reduces the generation of impurities such as protein debris and microthrombi, reducing the frequency of sewage discharge. This two-way cooperation ensures the long-term efficient operation of the device.

[0020] In this invention, the protein debris, microthrombi, and other impurities produced by dialysis that settle at the bottom of the device can be discharged online using the flow regulating valve on the bottom drain pipe. Simply opening the valve briefly will remove the deposited impurities, eliminating the need to stop the dialysis process and ensuring continuous operation. This avoids the impact on work efficiency caused by downtime for cleaning.

[0021] This invention achieves inverted blood pumping by flipping the housing through a connecting shaft and connecting plate. At this time, the blood flows from bottom to top, gradually filling the porous filter membrane filament bundle and the entire flow path, and fully expelling the internal air. After the blood is full, the housing is reset, and the blood flows from top to bottom. The overall liquid flow impact is small, which can reduce the friction and impact between blood cells and tubes and membranes, and effectively reduce the risk of hemolysis and coagulation.

[0022] The specific embodiments of the present invention will now be described in further detail with reference to the accompanying drawings. Attached Figure Description

[0023] In the attached diagram: Figure 1 This is a three-dimensional structural schematic diagram of a hemodialysis coagulation inhibition device based on porous modified materials proposed in this invention; Figure 2 This is a three-dimensional sectional view of a hemodialysis coagulation inhibition device based on porous modified materials proposed in this invention; Figure 3 for Figure 2 Schematic diagram of the structure at point A; Figure 4 This is a main cross-sectional view of a hemodialysis coagulation inhibition device based on porous modified materials proposed in this invention; Figure 5 for Figure 4 Schematic diagram of the structure at point B; Figure 6 for Figure 4 Schematic diagram of the structure at point C; Figure 7 This is a cross-sectional view of the housing of a hemodialysis coagulation inhibition device based on porous modified materials proposed in this invention; Figure 8 for Figure 7 Schematic diagram of the structure at point D; Figure 9 This is a schematic diagram of the structure of a porous modified material filter element for a hemodialysis coagulation inhibition device based on porous modified materials proposed in this invention; Figure 10 for Figure 9 Schematic diagram of the structure at point E; Figure 11 This is a schematic diagram of the locking block of a hemodialysis coagulation inhibition device based on porous modified materials proposed in this invention.

[0024] In the diagram: 1. Shell; 11. Expansion cavity; 111. Overflow pipe; 12. Gas-liquid separation cavity; 13. Spiral guide plate; 14. Snap-fit ​​groove; 15. Liquid inlet; 16. Air guide cavity; 17. Exhaust hose; 18. Exchange cavity; 2. Upper shell cover; 21. Lower shell cover; 22. Bottom drain pipe; 23. Flow regulating valve; 3. Porous modified material filter element; 31. Inlet tube; 32. Floating connector; 33. Porous filter membrane bundle; 34. Fixed connector; 341. First drain hole; 35. Drain tube; 36. Float; 4. Inlet pipe; 5. Locking block; 51. Second drain hole; 6. Venturi drain pipe; 61. Suction pipe; 7. Connecting shaft; 71. Connecting plate. Detailed Implementation

[0025] To make the objectives, technical solutions, and advantages of the embodiments of the present invention clearer, the technical solutions in the embodiments will be clearly and completely described below with reference to the accompanying drawings. The following embodiments are used to illustrate the present invention, but are not intended to limit the scope of the present invention.

[0026] Example: Refer to Figures 1-11A hemodialysis coagulation inhibition device based on porous modified materials includes a housing 1, with an upper cover 2 and a lower cover 21 fixedly installed at the upper and lower ends of the housing 1, respectively. An exchange chamber 18 and an expansion chamber 11 are provided inside the housing 1, communicating with each other. A porous modified material filter element 3 is installed inside the exchange chamber 18, with the bottom of the filter element 3 fixed to the housing 1 and the top of the filter element 3 floating within the exchange chamber 18. An overflow pipe 111 extending into the expansion chamber 11 is fixedly installed on the exchange chamber 18. A Venturi drain pipe 6 is fixedly installed at the bottom of the expansion chamber 11, and an air inlet pipe 61 is fixedly installed on the side wall of the Venturi drain pipe 6, with the air inlet end of the air inlet pipe 61 connected to the top of the side wall of the expansion chamber 11. A gas-liquid separation section is provided inside the housing 1, including a gas-liquid separation chamber 12 located within the housing 1, with a gas guide chamber 16 at the top of the gas-liquid separation chamber 12 that is higher around the edges and lower in the middle. A drain pipe is fixedly installed on the inner wall of the housing 1. The exhaust hose 17 extends to the expansion chamber 11 at its top, and the exhaust port of the exhaust hose 17 is higher than the drain port of the overflow pipe 111. The air inlet of the exhaust hose 17 is connected to the top of the air guiding chamber 16. A spiral guide plate 13 is fixedly installed inside the gas-liquid separation chamber 12. An inlet 15 communicating with the exchange chamber 18 is provided on the top of the side wall of the gas-liquid separation chamber 12. The position of the inlet 15 is higher than the spiral guide plate 13 and lower than the air guiding chamber 16. The spiral blades are inclined at an angle of 10°-15° relative to the horizontal plane, forming a sloping structure that is high around the edges and low in the middle. The bubbles separated from the dialysate gather along the sloping side of the cylinder wall and enter the gas guiding chamber 16. The gas guiding chamber 16 discharges into the expansion chamber 11 through the exhaust hose 17. The liquid inlet pipe 4 is fixedly installed on the side wall of the shell 1. The liquid inlet pipe 4 is connected to the gas-liquid separation chamber 12. The dialysate entering the gas-liquid separation chamber 12 through the liquid inlet pipe 4 flows spirally upward along the spiral guide plate 13.

[0027] In this embodiment, the dialysate to be treated is fed into the gas-liquid separation chamber 12 through the inlet pipe 4. Under the guidance of the spiral guide plate 13, a spiral upward flow field is formed. Relying on the 10°-15° tilt angle of the blades and the structure of high around the edges and low in the middle, the bubbles encased in the dialysate gather towards the outer cavity wall under the combined action of centrifugal force and buoyancy, and flow upward into the gas guiding chamber 16 to complete the gas-liquid separation of the dialysate. The gas collected in the gas guiding chamber 16 is transported to the expansion chamber 11 through the exhaust hose 17. After gas-liquid separation, the dialysate flows smoothly into the exchange chamber 18 through the inlet 15, and comes into full countercurrent contact with the blood in the porous modified material filter element 3, realizing the dialysis exchange process of solute dispersion and water ultrafiltration. The porous modified material filter element 3 itself has excellent anti-adhesion and blood compatibility properties, which can effectively inhibit the adhesion and activation aggregation of proteins and platelets in the blood on the membrane fiber surface, thereby reducing the probability of coagulation during dialysis from the material level.

[0028] As the amount of dialysate in the exchange chamber 18 increases, the waste liquid after exchange is discharged into the expansion chamber 11 through the drain port at the top of the overflow pipe 111, and then flows out through the Venturi drain pipe 6. According to Bernoulli's principle, the flow velocity inside the Venturi drain pipe 6 increases and the static pressure decreases. The gas accumulated at the top of the expansion chamber 11 is continuously extracted through the suction pipe 61, so that a stable micro-negative pressure environment is formed inside the expansion chamber 11. The gas trapped in the chamber is quickly removed, further reducing the gas content of the dialysate and reducing gas-liquid contact. At the same time, the swing resistance at the top of the porous modified material filter element 3 is reduced. Combined with the swing of the membrane fibers, the synergistic effect of continuous degassing and dynamic anticoagulation is achieved. At the same time, the negative pressure formed at the top of the liquid surface can promote the gas in the blood-dialysis process to be released from the liquid phase and quickly discharged with the air flow, effectively avoiding the adhesion of bubbles to the surface of the membrane fibers, and further reducing the risk of coagulation and hemolysis caused by bubbles.

[0029] Meanwhile, the stable micro-negative pressure environment inside the expansion cavity 11 can balance the pressure distribution throughout the cavity, avoid sudden drops in local pressure that cause concentrated bubble collapse, and significantly reduce the impact load generated by bubble collapse, thereby effectively preventing cavitation damage to the inner walls of the cavity and pipelines and extending the overall service life of the device.

[0030] Reference Figure 2 , Figures 4-6 , Figures 9-11 The porous modified material filter element 3 includes a porous filter membrane bundle 33, a floating connector 32 fixedly installed on the top of the porous filter membrane bundle 33, and a fixed connector 34 fixedly installed on the bottom of the porous filter membrane bundle 33. A float 36 is fixedly installed at the bottom of the floating connector 32, an inlet tube 31 is fixedly installed at the top of the floating connector 32, and an outlet tube 35 is fixedly installed at the bottom of the fixed connector 34. The inlet tube 31 is fixedly connected and sealed to the upper shell cover 2, and the outlet tube 35 is fixedly connected and sealed to the lower shell cover 21. The inlet tube 31 is a flexible tube. When the dialysate is discharged through the overflow tube 111, the floating connector 32 moves in the flowing dialysis fluid. Driven by the liquid, the inlet tube 31 deviates 1mm to 3mm in any direction within the horizontal plane of the overflow outlet of the overflow tube 111. The inlet tube 31 swings with the floating connector 32. When the floating connector 32 swings, it drives the porous filter membrane bundle 33 to swing synchronously to eliminate the static boundary layer on the membrane surface. At the same time, the exhaust hose 17 acts as a limiting structure and a rebound structure, constraining the movement stroke of the floating connector 32 while driving the floating connector 32 to rebound. A snap-fit ​​groove 14 is provided inside the housing 1. The fixed connector 34 is snapped into the snap-fit ​​groove 14. A locking block 5 is threaded into the snap-fit ​​groove 14. The locking block 5 abuts against the bottom of the fixed connector 34 and is fixed.

[0031] In this embodiment, blood enters the floating connector 32 through the inlet tube 31 and is divided. It then exchanges fluid with the dialysate through the porous membrane bundle 33 before converging in the fixed connector 34 and finally flowing out through the outlet tube 35. When the dialysate flows out from the overflow tube 111, the flowing fluid generates thrust, causing the floating connector 32 to shift by 1mm to 3mm in the corresponding horizontal plane, thereby causing the porous membrane bundle 33 to oscillate slightly. The exhaust hose 17, relying on its structure and elasticity, limits the maximum range of motion of the floating connector 32, controlling the oscillation amplitude. Furthermore, it provides a rebound force after the connector shifts, driving it to reset, thus causing the floating connector 32 to form a continuous reciprocating oscillation motion. The fixed connector 34 at the bottom of the filter element is engaged in the locking groove 14 of the housing 1 and then tightened by the locking block 5, achieving complete bottom fixation. This ensures that only the top of the porous membrane bundle 33 oscillates flexibly, resulting in a stable overall assembly structure.

[0032] In this embodiment, the continuous oscillation of the porous membrane fiber bundle 33 can disrupt the static boundary layer formed on the surface of the membrane fibers, preventing the adhesion and accumulation of substances such as proteins and platelets. This compensates for the shortcomings of single material modification, providing dual inhibition of thrombus formation and improving the coagulation inhibition effect. Furthermore, the exhaust hose 17 acts as a limiter, controlling the offset within the range of 1mm to 3mm, preventing the porous membrane fiber bundle 33 from being stretched or twisted significantly, effectively preventing membrane fiber breakage and damage, and extending the service life of the filter element. Moreover, the oscillation is driven by the flow of dialysate, and the exhaust hose 17 simultaneously achieves limiter and rebound functions. There is no need to add external components such as motors and transmission mechanisms, resulting in a simplified overall structure, low energy consumption, and low failure rate. In addition, the oscillation of the porous membrane fiber bundle 33 can disturb the surrounding flow field and peel off the tiny air bubbles attached to the membrane surface. Combined with the overall negative pressure degassing system, this further improves the gas-liquid separation efficiency and reduces the adverse effects of air bubbles.

[0033] Reference Figure 5 , Figure 10 and Figure 11 The fixed connector 34 is provided with a first drain hole 341 that runs vertically through the joint, and the locking block 5 is provided with a second drain hole 51 that runs vertically through the joint. When the locking block 5 is fixed to the fixed connector 34, the first drain hole 341 and the second drain hole 51 coincide. The bottom of the lower cover 21 is fixedly installed with a bottom drain pipe 22, and a flow regulating valve 23 is provided on the bottom drain pipe 22.

[0034] After dialysis, the waste liquid flows through the first drain hole 341 and the second drain hole 51 in sequence, and is finally discharged outward from the bottom drain pipe 22. The flow regulating valve 23 can be used to change the flow cross-sectional area of ​​the pipeline, thereby controlling the overall discharge flow rate to adapt to different dialysis conditions.

[0035] The first drain hole 341 and the second drain hole 51 are aligned and connected to ensure smooth flow of waste liquid; while the locking block 5 tightens the fixed joint 34, it does not affect the normal transport of fluid, realizing the integration of locking positioning and media flow.

[0036] Furthermore, during dialysis, when impurities accumulate at the bottom of the device, the flow regulating valve 23 can be briefly opened to quickly remove the deposited impurities from the body via the bottom drainage channel, achieving online waste removal during dialysis. After the impurities are removed, the flow regulating valve 23 is closed to restore the device to normal dialysis drainage conditions, preventing long-term accumulation of impurities that clog the membrane pores and flow channels, preventing the accumulation of dirt on the membrane surface that could lead to coagulation, and continuously ensuring the dialysis flux and coagulation inhibition performance of the porous modified material filter element 3.

[0037] Reference Figure 1 A connecting shaft 7 is fixedly installed on the outer wall of the expansion cavity 11, and a connecting plate 71 is fixedly installed on the connecting shaft 7. Before pumping blood into the porous modified material filter element 3, the housing 1 is rotated 180° so that the upper cover 2 faces downwards before pumping blood. When the blood enters the porous filter membrane bundle 33 or the drain tube 35, the housing 1 is driven to rotate 180° so that the upper cover 2 faces upwards. Under the action of the dialysate, blood and the gravity of the device itself, the end face of the overflow tube 111 of the housing 1 is parallel to the ground.

[0038] Before operation, the housing 1 is flipped and inverted via the connecting plate 71 and connecting shaft 7, allowing blood to flow smoothly from top to bottom into the porous filter membrane bundle 33. Gravity is used to pre-fill the pipeline and membrane fibers or the entire blood flow path, which can quickly purge the internal air. After the blood flows normally, the housing 1 is reset, and the overflow pipe 111 is leveled using the weight of the medium and the equipment to ensure uniform liquid level and stable liquid flow, providing a stable operating condition for subsequent gas-liquid separation, membrane fiber oscillation and dialysis exchange.

[0039] In this embodiment, the housing 1 can be easily flipped over by connecting shaft 7 and connecting plate 71. The inverted blood pump allows the blood to be pre-filled smoothly by gravity, effectively removing internal air, reducing liquid flow impact, and avoiding damage to blood cells. After resetting, the overflow pipe 111 is kept horizontal by the medium and the weight of the equipment, ensuring stable liquid level and flow, creating good operating conditions for gas-liquid separation, membrane fiber oscillation, and dialysis exchange, and improving the overall operational stability and safety.

[0040] In summary, during dialysis, this device, on the one hand, relies on the excellent biocompatibility and anti-adhesion properties of the porous modified material itself to inhibit the adhesion and aggregation of proteins and platelets at the material level; on the other hand, it utilizes the liquid flow to drive the membrane fibers to oscillate slightly, breaking the static boundary layer on the membrane surface and dynamically flushing away impurities, forming a dual coagulation inhibition system of material protection and dynamic flushing, which significantly reduces the probability of thrombosis.

[0041] In summary, this device has the following advantages: The main gas bubbles in the dialysate are separated by the spiral guide plate 13. The micro negative pressure formed by the Venturi drain tube 6 and the suction tube 61 continuously removes the gas in the expansion chamber 11. The porous filter membrane fiber bundle 33 swings to disturb the flow field and peel off microbubbles in the dead corners of the membrane surface. The three work together to achieve deep degassing throughout the entire area. The reduction of bubbles can reduce the deposits on the membrane surface and further assist in preventing coagulation.

[0042] The modified material of the porous filter membrane bundle 33 reduces the probability of blood cell and protein adhesion from the source, which is a passive protection; the floating connector 32 drives the porous filter membrane bundle 33 to swing, actively flushing the deposits on the membrane surface and breaking the static boundary layer. The combination of the two constructs a dual anticoagulation system, which greatly reduces the risk of thrombosis.

[0043] A slight negative pressure is created in the expansion chamber 11 by using the Venturi drain tube 6 and the suction tube 61. This serves two purposes: firstly, it draws out gas and prevents cavitation; secondly, it reduces the oscillation resistance of the floating connector 32 and the porous membrane bundle 33, making dynamic rinsing more flexible and stable. The oscillation of the porous membrane bundle 33 disturbs the flow field, disrupts the liquid surface tension, and promotes the full release of dissolved gas in the liquid phase. The released gas is then quickly discharged with the help of the slight negative pressure, further improving the overall gas-liquid separation effect. This achieves bidirectional empowerment and synergistic effect of negative pressure degassing and membrane oscillation. Furthermore, the negative pressure draws out gas, driving the gas flow in the expansion chamber 11. The flowing gas, along with the discharge hose 17 and the liquid flow disturbance during dialysate discharge, continuously exerts a multi-directional thrust on the floating connector 32, making its reciprocating oscillation more continuous and uniform, enhancing the membrane surface rinsing effect, continuously inhibiting protein and platelet adhesion and aggregation, and further improving coagulation inhibition capacity.

[0044] Opening the flow regulating valve 23 allows for the online discharge of impurities from the flow channel, preventing impurities from clogging the pores of the porous filter membrane bundle 33 and inducing local coagulation. The filter element's excellent coagulation inhibition ability can also reduce the generation of impurities such as protein debris and microthrombi, reducing the frequency of sewage discharge. This two-way cooperation ensures the long-term efficient operation of the device.

[0045] Protein debris, microthrombi, and other impurities produced during dialysis can be discharged online using the flow regulating valve 23 on the bottom drain pipe 22. Simply opening the valve briefly will remove the deposited impurities, eliminating the need to stop the dialysis process and effectively ensuring its continuity, thus avoiding disruption to work efficiency due to downtime for cleaning.

[0046] The inverted blood pumping is completed by flipping the housing 1 through the connecting shaft 7 and connecting plate 71. At this time, the blood flows from bottom to top, gradually filling the porous filter membrane bundle 33 and the entire flow path, and fully expelling the internal air. After the blood is full, the housing 1 is reset, and the blood flows from top to bottom. The overall liquid flow impact is small, which can reduce the friction and impact between blood cells and the pipeline and membrane, and effectively reduce the risk of hemolysis and coagulation.

[0047] The above description is merely a preferred embodiment of the present invention and is not intended to limit the present invention in any way. Although the present invention has been disclosed above with reference to preferred embodiments, it is not intended to limit the present invention. Any person skilled in the art can make some modifications or alterations to the above-described technical content to create equivalent embodiments without departing from the scope of the present invention. Any simple modifications, equivalent changes, and alterations made to the above embodiments based on the technical essence of the present invention without departing from the scope of the present invention shall still fall within the scope of the present invention.

Claims

1. A hemodialysis coagulation inhibition device based on porous modified materials, comprising a housing (1), wherein an upper shell cover (2) and a lower shell cover (21) are respectively fixedly installed at the upper and lower ends of the housing (1), characterized in that, The housing (1) is provided with an exchange cavity (18) and an expansion cavity (11) that are interconnected. The exchange chamber (18) is provided with a porous modified material filter element (3). The bottom of the porous modified material filter element (3) is fixed to the shell (1), and the top of the porous modified material filter element (3) is floatingly disposed in the exchange chamber (18). An overflow pipe (111) extending into the expansion cavity (11) is fixedly installed on the exchange cavity (18). A Venturi drain pipe (6) is fixedly installed at the bottom of the expansion cavity (11), and an air suction pipe (61) is fixedly installed on the side wall of the Venturi drain pipe (6). The air inlet end of the air suction pipe (61) is connected to the top of the side wall of the expansion cavity (11). The housing (1) is provided with a gas-liquid separation section, and the exhaust end of the gas-liquid separation section is connected to the expansion cavity (11).

2. The hemodialysis coagulation inhibition device based on porous modified materials according to claim 1, characterized in that, The gas-liquid separation unit includes a gas-liquid separation chamber (12) disposed in the housing (1), and a gas guiding chamber (16) with a high periphery and a low center is disposed at the top of the gas-liquid separation chamber (12). An exhaust hose (17) is fixedly installed on the inner wall of the housing (1). The top of the exhaust hose (17) extends into the expansion cavity (11), and the exhaust port of the exhaust hose (17) is higher than the drain port of the overflow pipe (111). The air inlet of the exhaust hose (17) is connected to the top of the air guide cavity (16). A spiral guide plate (13) is fixedly installed inside the gas-liquid separation chamber (12). A liquid inlet (15) communicating with the exchange chamber (18) is provided on the top of the side wall of the gas-liquid separation chamber (12). The position of the liquid inlet (15) is higher than the spiral guide plate (13) and lower than the gas guide chamber (16).

3. The hemodialysis coagulation inhibition device based on porous modified materials according to claim 2, characterized in that, The spiral blades of the spiral guide plate (13) are inclined at an angle of 10°-15° relative to the horizontal plane, forming a sloping structure with high sides and low middle. The bubbles separated from the dialysate gather along the sloping side of the cylinder wall and enter the gas guide chamber (16). The gas guide chamber (16) is discharged into the expansion chamber (11) through the exhaust hose (17).

4. The hemodialysis coagulation inhibition device based on porous modified materials according to claim 2, characterized in that, A liquid inlet pipe (4) is fixedly installed on the side wall of the housing (1). The liquid inlet pipe (4) is connected to the gas-liquid separation chamber (12). The dialysate entering the gas-liquid separation chamber (12) through the liquid inlet pipe (4) flows spirally upward along the spiral guide plate (13) to achieve the initial separation of the gas and liquid phases.

5. A hemodialysis coagulation inhibition device based on porous modified materials according to claim 2, characterized in that, The porous modified material filter element (3) includes a porous filter membrane bundle (33), a floating connector (32) fixedly installed on the top of the porous filter membrane bundle (33), and a fixed connector (34) fixedly installed on the bottom of the porous filter membrane bundle (33). A float (36) is fixedly installed at the bottom of the floating connector (32), an inlet tube (31) is fixedly installed at the top of the floating connector (32), and an outlet tube (35) is fixedly installed at the bottom of the fixed connector (34).

6. A hemodialysis coagulation inhibition device based on porous modified materials according to claim 5, characterized in that, The inlet tube (31) is fixedly connected to and sealed with the upper shell cover (2), and the outlet tube (35) is fixedly connected to and sealed with the lower shell cover (21). The inlet tube (31) is a flexible tube. When the dialysate is discharged through the overflow tube (111), the floating connector (32) is driven by the flowing dialysate to deflect 1mm to 3mm in any direction within the horizontal plane of the outlet of the overflow tube (111). The inlet tube (31) swings with the floating connector (32).

7. A hemodialysis coagulation inhibition device based on porous modified materials according to claim 6, characterized in that, When the floating connector (32) swings, it drives the porous filter membrane bundle (33) to swing synchronously to eliminate the static boundary layer on the membrane surface. At the same time, the exhaust hose (17) serves as a limiting structure and a rebound structure, constraining the movement stroke of the floating connector (32) while driving the floating connector (32) to rebound.

8. A hemodialysis coagulation inhibition device based on porous modified materials according to claim 5, characterized in that, The housing (1) is provided with a snap-fit ​​groove (14), and the fixed connector (34) is snapped into the snap-fit ​​groove (14). A locking block (5) is threaded into the snap-fit ​​groove (14), and the locking block (5) is fixed by contact with the bottom of the fixed connector (34).

9. A hemodialysis coagulation inhibition device based on porous modified materials according to claim 8, characterized in that, The fixed connector (34) is provided with a first drain hole (341) that runs vertically through the joint, and the locking block (5) is provided with a second drain hole (51) that runs vertically through the joint. When the locking block (5) abuts against the fixed connector (34) and is fixed, the first drain hole (341) and the second drain hole (51) coincide. The bottom of the lower cover (21) is fixedly installed with a bottom drain pipe (22), and a flow regulating valve (23) is provided on the bottom drain pipe (22).

10. A hemodialysis coagulation inhibition device based on porous modified materials according to claim 5, characterized in that, A connecting shaft (7) is fixedly installed on the outer wall of the expansion cavity (11), and a connecting plate (71) is fixedly installed on the connecting shaft (7). Before pumping blood into the porous modified material filter element (3), the housing (1) is rotated 180° so that the upper cover (2) faces down before pumping blood. When the blood enters the porous filter membrane bundle (33) or the draining blood vessel (35), the housing (1) is driven to rotate 180° so that the upper cover (2) faces up. Under the action of the dialysate, blood and the gravity of the device itself, the end face of the overflow pipe (111) of the housing (1) is parallel to the ground.

Images