Portable blood purification device with multi-layer filtering function

Abstract

The invention discloses a portable blood purification device with a multi-layer filtering function, and relates to the technical field of blood purification devices.The portable blood purification device comprises a purification main machine, a primary plasma separation assembly, a secondary plasma separation assembly, a perfusion assembly and a dialysis assembly are arranged in the purification main machine, and the purification main machine is further internally provided with a rotational flow mixing assembly, a first filtering assembly and a second filtering assembly; the rotational flow mixing assembly is arranged between the primary plasma separation assembly and the secondary plasma separation assembly, and the rotational flow mixing assembly is used for mixing plasma and blood; an inlet of the perfusion assembly is connected with the secondary plasma separation assembly, the perfusion assembly is provided with a bidirectional perfusion port and a bidirectional outlet, and the bidirectional perfusion port and the bidirectional outlet are respectively provided with a cooling channel; the inlet of the dialysis assembly is connected with the dialysis assembly, and the output section of the dialysis assembly is provided with a heating channel; according to the invention, the problem of non-uniform load of each filtering unit in the multi-layer filtering process is solved.

Description

Technical Field

[0001] This invention relates to the technical field of blood purification devices, specifically a portable blood purification device with multi-layer filtration function. Background Technology

[0002] Portable blood purification devices are used for patients who need blood purification treatment. They are small in size, portable, and easy to operate. Typically, these devices are suitable for patients who need dialysis long-term, especially those living in remote areas where medical care is not readily available or in environments where blood problems need to be addressed quickly.

[0003] For example, Chinese Patent No. CN119868698B discloses a portable blood purification device, which relates to the field of medical technology. The portable blood purification device includes a purifier and a placement table. A shoulder strap is fixedly installed on the surface of the purifier. A hanging tube is fixedly installed on the surface of the purifier. An anticoagulant canister is fixedly installed on the surface of the purifier. A switch is fixedly installed on the surface of the purifier. A clamp is fixedly installed on the surface of the purifier. The portable blood purification device uses a telescopic spring rod to deform and recover, and pushes an inclined block to move and limit a trapezoidal block. At this time, the placement table limits the purifier.

[0004] Meanwhile, Chinese patent publication number CN120204498A discloses a quadruple plasma blood purification device and purification method. The device includes: a primary plasma separator, a secondary plasma separator, an perfusion device, and a dialyzer; the inlet of the primary plasma separator is connected to the patient's artery; the inlet of the secondary plasma separator is connected to the primary plasma separator; the inlet of the perfusion device is connected to the secondary plasma separator; and the dialyzer is connected to both the perfusion device and the primary plasma separator.

[0005] While existing portable blood purification devices achieve preliminary filtration stratification in multi-layer filtration systems, the workload and duration of each filtration unit are not intelligently adjusted according to dynamic changes in the patient's condition (such as toxin levels and inflammatory markers) during the multi-layer filtration process. This results in uneven loads among the filtration units, with some filter layers being overloaded and others redundant, leading to low overall purification efficiency. Furthermore, the adjustment response of blood / plasma flow rate is lagging, failing to quickly adjust to pressure fluctuations or system load changes during the filtration process, causing a sharp drop in filtration efficiency and system bottlenecks. More critically, existing systems fail to achieve sufficient mixing and temperature control coordination between filtration components. In particular, the thorough mixing of blood and plasma is not efficiently completed in different processing stages, resulting in unstable treatment effects and affecting the therapeutic outcome. Summary of the Invention

[0006] To address the shortcomings of existing technologies, this invention provides a portable blood purification device with multi-layer filtration capabilities.

[0007] To solve the above-mentioned technical problems, the present invention provides the following technical solution:

[0008] This invention provides a portable blood purification device with multi-layer filtration function, including a purification unit. The purification unit internally houses a primary plasma separation component, a secondary plasma separation component, an perfusion component, and a dialysis component. The purification unit also internally houses:

[0009] A swirling mixing assembly is disposed between the primary plasma separation assembly and the secondary plasma separation assembly, and the swirling mixing assembly is used for mixing plasma and blood;

[0010] The inlet of the perfusion assembly is connected to the secondary plasma separation assembly. The perfusion assembly is provided with a bidirectional perfusion port and a bidirectional outlet. Cooling channels are provided at the bidirectional perfusion port and the bidirectional outlet, respectively.

[0011] The inlet of the dialysis unit is connected to the dialysis unit, and the output section of the dialysis unit is provided with a heating channel.

[0012] As a preferred embodiment of the present invention, the primary plasma separation component adopts a hollow fiber membrane structure with a membrane pore size of 0.1-0.3 μm. The primary plasma separation component is provided with a pressure regulating mechanism at the artery connection point to control the blood input flow rate and pressure, thereby preventing blood cell retention.

[0013] The secondary plasma separation component adopts a porous membrane structure with a pore size of 0.03–0.05 μm.

[0014] As a preferred embodiment of the present invention, the swirling mixing component is provided with a spiral disturbance structure to enhance the mixing efficiency of plasma and blood.

[0015] As a preferred embodiment of the present invention, the irrigation component is provided with an adsorption unit, which is a resin or fiber membrane material, and the irrigation component achieves automatic flow direction switching through a control module.

[0016] As a preferred embodiment of the present invention, the dialysis assembly is provided with a semi-permeable membrane structure inside, and the pore size of the semi-permeable membrane structure is 0.5 nm.

[0017] As a preferred embodiment of the present invention, the temperature range of the low-temperature channel is 10–15°C;

[0018] The heating band is configured with a two-section structure, with the first section having a temperature of 25°C and the second section having a temperature of 37°C.

[0019] As a preferred embodiment of the present invention, the purification host is further provided with a temperature control module for controlling the temperature of the cooling channel and the heating channel.

[0020] As a preferred technical solution of the present invention, the purification host is further provided with an anticoagulation intelligent control component. The anticoagulation intelligent control component includes an anticoagulation pump and a pressure sensor. The pressure sensor is installed at the front end of the inlet of the perfusion component and is used to detect the membrane resistance of the adsorption unit. The anticoagulation pump adjusts the injection volume of the anticoagulation liquid according to the detected resistance value.

[0021] The beneficial effects of this invention are:

[0022] This invention solves the problem of uneven load on each filtration unit during multi-layer filtration by adding a vortex mixing component and a temperature control module to the blood purification device. The vortex mixing component, located between the primary and secondary plasma separation components, effectively promotes the mixing of plasma and blood, improving the fluid mixing efficiency during blood purification and thus making the load on each filtration unit more uniform. In addition, the temperature control module can precisely control the temperature of the cooling and heating channels, making temperature control during filtration more accurate and ensuring real-time adjustment of the system load, thereby optimizing the overall filtration efficiency of the blood purification device. Attached Figure Description

[0023] The accompanying drawings are provided to further illustrate the invention and form part of the specification. They are used together with the embodiments of the invention to explain the invention and do not constitute a limitation thereof.

[0024] In the attached diagram:

[0025] Figure 1 This is a schematic diagram of the overall structure of the blood purification device of the present invention.

[0026] Figure 2 This is a schematic diagram of the bidirectional inlet and outlet of the irrigation assembly. Detailed Implementation

[0027] The technical solutions of this application will now be clearly and completely described with reference to the accompanying drawings. Obviously, the described embodiments are merely some embodiments of this application, and not all embodiments. The components of this application described and shown in the accompanying drawings can generally be arranged and designed in various different configurations. Therefore, the following detailed description of the embodiments of this application provided in the accompanying drawings is not intended to limit the scope of the claimed application, but merely to illustrate selected embodiments of this application. All other embodiments obtained by those skilled in the art based on the embodiments of this application without inventive effort are within the scope of protection of this application.

[0028] It should be noted that similar reference numerals and letters in the following figures indicate similar items; therefore, once an item is defined in one figure, it does not need to be further defined and explained in subsequent figures. Furthermore, in the description of this application, terms such as "first," "second," etc., are used only to distinguish descriptions and should not be construed as indicating or implying relative importance.

[0029] like Figure 1 As shown, a portable blood purification device with multi-layer filtration function includes a purification unit. The purification unit internally houses a primary plasma separation component, a secondary plasma separation component, an perfusion component, and a dialysis component. The purification unit also internally houses:

[0030] A swirling mixing assembly is disposed between the primary plasma separation assembly and the secondary plasma separation assembly, and the swirling mixing assembly is used for mixing plasma and blood;

[0031] The inlet of the perfusion assembly is connected to the secondary plasma separation assembly. The perfusion assembly is provided with a bidirectional perfusion port and a bidirectional outlet. Cooling channels are provided at the bidirectional perfusion port and the bidirectional outlet, respectively.

[0032] The inlet of the dialysis unit is connected to the dialysis unit, and the output section of the dialysis unit is provided with a heating channel.

[0033] The purification unit, as the core support platform of this device, has an outer shell made of ABS engineering plastic and carbon fiber composite material, which combines mechanical strength with lightweight and portable characteristics, making it suitable for various scenarios such as hospital mobility, emergency transport, or battlefield medical care.

[0034] A swirling mixing assembly refers to a mixing cavity with a spiral flow channel structure. Specifically, it can be made of stainless steel or medical-grade plastic with built-in spiral guide vanes. Specifically, it can be implemented using continuous spiral blades (similar to an auger mechanism, not shown in the specific structural diagram) or segmented spiral guide vanes. It breaks up the aggregated state of macromolecules by generating high-shear swirling flow.

[0035] The perfusion assembly is located after the secondary plasma separation assembly. Structurally, it has a bidirectional perfusion port structure, allowing plasma to pass through the assembly in either forward or reverse direction. The perfusion assembly is equipped with an adsorption unit, which can efficiently adsorb and remove medium-molecular-weight toxins and lipid-soluble toxins. The assembly achieves dynamic switching of flow direction through a control module to avoid the formation of perfusion dead zones and ensure that plasma always follows the optimal adsorption path.

[0036] The dialysis unit is mainly used to remove low molecular weight toxins from plasma. It should be noted that the inlet and outlet of the dialysis unit can be equipped with gas blocking mechanisms to prevent air bubbles generated during operation from entering the blood passage and to ensure blood safety.

[0037] Specifically, the primary plasma separation unit extracts blood from the patient's artery and separates the plasma through a hollow fiber membrane. The swirling mixing unit applies swirling shear force to the plasma, causing large molecules to disperse evenly. The secondary plasma separation unit performs secondary filtration through a porous membrane to remove medium-molecular-weight substances. The perfusion unit switches the flow direction through a bidirectional outlet, allowing the adsorption unit to fully contact the target toxins. The dialysis unit uses a semi-permeable membrane to remove small-molecule toxins, completing the final purification.

[0038] Through the above technical solutions, this application achieves dynamic load balancing of multi-layer filtration units, effectively eliminating efficiency fluctuations caused by flow rate response lag. The combination of swirling mixing and pulsed flow control makes the inlet fluid distribution of each filtration layer more uniform, and the gradient temperature control design improves the removal efficiency of toxins with different molecular characteristics.

[0039] Furthermore, the primary plasma separation component adopts a hollow fiber membrane structure with a membrane pore size of 0.1–0.3 μm. The primary plasma separation component is equipped with a pressure regulating mechanism at the artery connection point to control the blood infusion flow rate and pressure, thereby preventing blood cell retention.

[0040] The secondary plasma separation component adopts a porous membrane structure with a pore size of 0.03–0.05 μm.

[0041] Hollow fiber membrane structure refers to a filtration unit composed of multiple hollow fiber tubes, which can be made of polysulfone or polyethersulfone materials. A continuous flow channel is formed inside the fiber tube. By setting a specific pore size range, the physical separation of blood cells and plasma is achieved. The pressure regulation mechanism refers to a hydraulic control device with dynamic feedback function. Specifically, it can be an adjustable valve assembly driven by a stepper motor. By monitoring the inlet pressure change in real time, the opening and closing degree is automatically adjusted to prevent sudden changes in flow rate from causing blood cell accumulation.

[0042] Porous membrane structures refer to filter media with nanoscale pores, which can be made of polyacrylonitrile or polyvinylidene fluoride materials. Their pore size range can retain plasma components of specific molecular weights.

[0043] Specifically, in the primary plasma separation process, the pore size of the hollow fiber membrane is set to a critical size that can both block blood cells from passing through and maintain plasma flow. When blood enters from the arterial end, the pressure regulating mechanism dynamically adjusts the valve opening according to the real-time detected inlet pressure, so that the blood flow rate is stabilized within the set threshold range, avoiding blood cells from being retained on the membrane surface due to a sudden increase in pressure. The secondary plasma separation stage uses a filter membrane with a smaller pore size, which further removes large molecules in the plasma through the molecular sieve effect of porous membranes or ultrafiltration membranes. In addition, the secondary plasma separation component is also equipped with a liquid distribution plate. The liquid distribution plate uses the guide grooves designed on its surface to evenly disperse the incoming fluid to different areas of the membrane surface, eliminating the pressure concentration phenomenon caused by local flow velocity differences, thereby maintaining a uniform filtration pressure across the entire membrane surface.

[0044] Furthermore, the swirling mixing component is equipped with a spiral disturbance structure to enhance the mixing efficiency of plasma and blood.

[0045] After the plasma is output from the primary plasma separation component, it enters the vortex mixing component, which has a spiral disturbance structure inside. By forming a three-dimensional vortex, the plasma is fully disturbed and mixed with high shear. This process helps to break up any large molecular aggregates that may exist in the plasma, and improves the contact efficiency and removal capacity of the subsequent filtration unit for the target toxins.

[0046] Specifically, the spiral perturbation structure can generate a swirling effect through its rotating fluid path, bringing plasma molecules and toxins into the subsequent filtration components in a more uniform and efficient manner. This hybrid structure can ensure that toxins are evenly distributed throughout the plasma, providing better conditions for the interaction between plasma and subsequent filtration materials. The ultimate goal is to improve the overall purification efficiency of the system, reduce the load on each filter membrane, and avoid overloading of a single filter layer due to excessive concentration of certain substances.

[0047] Taking the clinical treatment of diseases such as hypertriglyceridemia and cytokine storm as an example, the patient's plasma contains a lot of lipid particles and cell debris. If it is not effectively mixed, it may overburden the subsequent filter. At this time, in the cyclone mixing component, the plasma is subjected to strong shearing action, and the macromolecules and cell debris in the plasma are broken and evenly distributed. Through this process, the composition of the plasma is optimized, and the subsequent secondary plasma separator can remove the remaining toxins and macromolecules more efficiently. At the same time, the design of the cyclone mixing component ensures that the process can operate stably at different flow rates, and can maintain high purification efficiency even when the plasma concentration is high.

[0048] In practice, medical staff can dynamically adjust the operating parameters of the swirl mixing component according to the patient's condition to achieve the best therapeutic effect.

[0049] Furthermore, such as Figure 2 As shown, the irrigation assembly has an adsorption unit inside, which is a resin or fiber membrane material. The irrigation assembly automatically switches the flow direction through a control module.

[0050] The perfusion assembly is equipped with a bidirectional infusion port and a bidirectional outlet. The structure consists of two independent fluid interfaces, which are respectively located at both ends of the perfusion assembly, allowing the plasma to automatically switch between forward perfusion and reverse perfusion. The bidirectional infusion port and the bidirectional outlet at both ends of the perfusion assembly are equipped with electromagnetic control valves. These valves are driven by a control module and can achieve seamless switching between forward and reverse perfusion under preset conditions.

[0051] Before the plasma enters the perfusion assembly, the system comprehensively determines the current filtration efficiency based on multiple parameters such as the trend of toxin concentration changes before and after filtration, membrane pressure difference changes, and flow rate feedback data. If the control module detects that the adsorption rate in a certain perfusion direction tends to saturate or that a pressure rise occurs, it will automatically drive the solenoid valve to switch the flow direction, thereby realizing reverse perfusion of plasma in the perfusion assembly, enhancing the utilization rate of the cleaning material and avoiding the formation of dead zones.

[0052] The adsorption process continues, and the state of the adsorbent material is evaluated within a set period. If the adsorbent material is detected to be close to saturation, the system will also issue a replacement prompt signal.

[0053] Furthermore, the dialysis assembly has a semi-permeable membrane structure inside, and the pore size of the semi-permeable membrane structure is 0.5 nm.

[0054] Specifically, the dialysis unit is located after the perfusion unit and is directly connected to its fluid outlet, while its other end is connected to the liquid outlet of the purification unit, forming a continuous purification path.

[0055] The dialysis unit is equipped with a semi-permeable membrane structure made of polysulfone material with a pore size of 0.5 nm, which can effectively remove low-molecular-weight water-soluble toxins (such as urea and creatinine). The membrane material is supported by a membrane frame to maintain structural stability. Plasma channels and dialysate channels are respectively provided on both sides of the membrane area, and it operates in a parallel flow mode.

[0056] After the perfusion unit completes the adsorption of medium-molecular toxins and lipid-soluble substances, the plasma enters the dialysis unit. At this time, the system precisely controls the flow rate, concentration gradient and temperature parameters of the dialysate, so that low-molecular toxins can pass through the semipermeable membrane into the dialysate channel under the action of concentration driving force and osmotic pressure difference, thereby achieving efficient removal.

[0057] The dialysis unit and the purification unit have a built-in liquid temperature control system that works together to maintain the dialysate at a constant temperature (usually 37°C) according to the system settings. This ensures that the toxin transfer rate is not affected by low temperature and avoids protein denaturation or back osmosis. At the same time, the dialysate outlet is equipped with a dynamic drain control valve to ensure stable liquid flow and prevent membrane damage caused by back pressure.

[0058] As mid-to-back processing units of the purification host, the perfusion and dialysis components are logically linked and communicate with each other through the main control module. During operation, the main control module monitors the adsorption efficiency of the perfusion component and the cleaning effect of the dialysis component in real time, and realizes multiple functions such as switching the perfusion direction, adjusting the dialysate concentration, and alarming the gas blockage status based on the feedback data.

[0059] The entire purification process can be adaptively adjusted under different pathological types. For example, when treating hypertriglyceridemia, the system will prioritize increasing the flow rate and contact time of the lipid-soluble toxin adsorbent material in the perfusion component; while when treating the blood of uremia patients, it will increase the flow efficiency of the dialysis component and improve the removal capacity of low molecular weight toxins, thereby achieving a personalized and precise purification strategy.

[0060] In a practical application, this device was used to treat patients with severe pancreatitis and hyperlipidemia. The perfusion unit was filled with a resin specifically designed to dissolve lipid-soluble toxins, while the dialysis unit used a standard dialysis solution (Na+). + ,Cl - HCO3 - The concentrations were 135, 110, and 35 mmol / L. During the purification process, the system monitored that the difference in toxin concentration before and after the perfusion component decreased to about 10%. It automatically switched the perfusion direction and adjusted the temperature control system to 25°C to enhance the adsorption efficiency of lipid-soluble toxins. The dialysis section continued to operate at a constant temperature of 37°C to effectively maintain the removal capacity of small molecule toxins.

[0061] Furthermore, the temperature range of the low-temperature channel is 10–15°C;

[0062] The heating band is configured with a two-section structure, with the first section having a temperature of 25°C and the second section having a temperature of 37°C.

[0063] The purification unit is also equipped with a temperature control module to control the temperature of the cooling channel and the heating channel.

[0064] The cryogenic channel refers to the fluid pathway used to maintain a low temperature environment for plasma flow. It can be implemented by using a built-in cooling coil or circulating coolant. Its function is to inhibit the denaturation or degradation of proteins in the plasma through a low-temperature environment. The constant-temperature heating belt refers to the temperature regulation device set between different filtration layers. It can be implemented by using resistance wire or semiconductor heating element. Its function is to provide temperature conditions that are adapted to the specific toxin removal requirements of different filtration layers.

[0065] The temperature control module is an electronic control unit used to monitor and adjust the temperature in real time. Specifically, it can be implemented by combining a microcontroller with a temperature sensor. Its function is to dynamically adjust the temperature of each segment according to preset parameters.

[0066] Specifically, the low-temperature channel controls the plasma temperature within the range of 10 to 15°C to avoid damage to plasma components caused by high temperatures. After the primary filtration layer, the first constant-temperature heating band raises the temperature to 25°C. This temperature range is conducive to the efficient binding of lipid-soluble toxins (such as bilirubin, lipid peroxides, etc.) with the resin adsorbent material. After the secondary filtration layer, the second constant-temperature heating band raises the temperature to 37°C. This temperature is close to physiological conditions, promoting the diffusion and removal of water-soluble toxins (such as urea, creatinine, amino acid residues, etc.) through the semi-permeable membrane. The temperature control module can optionally monitor the temperature of each section in real time through a thermistor valve. When the temperature deviates from the preset range, the heating band power or coolant flow rate is automatically adjusted to ensure that different filtration stages are always within the temperature window suitable for the removal of the target toxins.

[0067] In some specific implementations, the coolant circulation system of the low-temperature channel can be integrated into the purification host, and the refrigerant circulation is driven by a micro compressor. The constant temperature heating belt can be controlled independently in segments. For example, the first segment uses resistance wire heating and the second segment uses semiconductor heating element to achieve rapid response in different temperature zones. Thermistor valves can be set at the junction of the heating belt and the low-temperature channel, and the mixing ratio of hot and cold fluids can be adjusted by the deformation characteristics of shape memory alloy.

[0068] Furthermore, the purification host is also equipped with an anticoagulation intelligent control component, which includes an anticoagulation pump and a pressure sensor. The pressure sensor is installed at the front end of the inlet of the perfusion component to detect the membrane resistance of the adsorption unit. The anticoagulation pump adjusts the injection volume of the anticoagulation liquid according to the detected resistance value.

[0069] Among them, the pressure sensor refers to the device used to monitor the fluid pressure at the inlet of the perfusion component in real time. Specifically, it can be implemented using a piezoresistive or capacitive sensor. By detecting changes in membrane resistance, it reflects the coagulation or impurity deposition. The anticoagulant pump refers to the device used to quantitatively deliver heparin solution. Specifically, it can be implemented using a precision injection pump driven by a stepper motor. The anticoagulant injection rate is dynamically adjusted based on the resistance data fed back by the pressure sensor.

[0070] Specifically, as blood flows through the perfusion assembly, the pressure sensor continuously collects the fluid pressure signal at the inlet. When the membrane surface resistance increases due to coagulation or impurity deposition, the change in pressure signal is transmitted to the control unit. The control unit generates an anticoagulant injection volume adjustment command according to a preset algorithm, and the anticoagulant pump increases the injection rate of heparin solution to inhibit the coagulation process. When the membrane surface resistance decreases, the anticoagulant pump automatically reduces the injection volume to avoid excessive anticoagulant. This closed-loop control system establishes a dynamic matching mechanism between anticoagulant supply and membrane surface status by monitoring the membrane surface operating parameters in real time.

[0071] Finally, it should be noted that the above descriptions are merely preferred embodiments of the present invention and are not intended to limit the present invention. Although the present invention has been described in detail with reference to the foregoing embodiments, those skilled in the art can still modify the technical solutions described in the foregoing embodiments or make equivalent substitutions for some of the technical features. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of the present invention should be included within the protection scope of the present invention.

Claims

1. A portable blood purification device with multi-layer filtration function, comprising a purification unit, wherein the purification unit internally houses a primary plasma separation component, a secondary plasma separation component, an perfusion component, and a dialysis component, characterized in that, The purification unit also contains: A swirling mixing assembly is disposed between the primary plasma separation assembly and the secondary plasma separation assembly, and the swirling mixing assembly is used for mixing plasma and blood; The inlet of the perfusion assembly is connected to the secondary plasma separation assembly. The perfusion assembly is provided with a bidirectional perfusion port and a bidirectional outlet. Cooling channels are provided at the bidirectional perfusion port and the bidirectional outlet, respectively. The inlet of the dialysis unit is connected to the dialysis unit, and the output section of the dialysis unit is provided with a heating channel.

2. The portable blood purification device with multi-layer filtration function according to claim 1, characterized in that, The primary plasma separation component adopts a hollow fiber membrane structure with a membrane pore size of 0.1-0.3 μm. The primary plasma separation component is equipped with a pressure regulating mechanism at the artery connection point to control the blood infusion flow rate and pressure, and to avoid blood cell retention. The secondary plasma separation component adopts a porous membrane structure with a pore size of 0.03–0.05 μm.

3. A portable blood purification device with multi-layer filtration function according to claim 1, characterized in that, The swirling mixing component has a spiral disturbance structure inside, which is used to enhance the mixing efficiency of plasma and blood.

4. A portable blood purification device with multi-layer filtration function according to claim 1, characterized in that, The irrigation assembly is equipped with an adsorption unit, which is a resin or fiber membrane material. The irrigation assembly achieves automatic flow direction switching through a control module.

5. A portable blood purification device with multi-layer filtration function according to claim 1, characterized in that, The dialysis unit has a semi-permeable membrane structure inside, and the pore size of the semi-permeable membrane structure is 0.5 nm.

6. A portable blood purification device with multi-layer filtration function according to claim 1, characterized in that, The temperature range of the low-temperature channel is 10–15°C; The heating band is configured with a two-section structure, with the first section having a temperature of 25°C and the second section having a temperature of 37°C.

7. A portable blood purification device with multi-layer filtration function according to claim 6, characterized in that, The purification unit is also equipped with a temperature control module to control the temperature of the cooling channel and the heating channel.

8. A portable blood purification device with multi-layer filtration function according to claim 4, characterized in that, The purification unit is also equipped with an anticoagulation intelligent control component, which includes an anticoagulation pump and a pressure sensor. The pressure sensor is installed at the inlet of the perfusion component to detect the membrane resistance of the adsorption unit. The anticoagulation pump adjusts the injection volume of the anticoagulation solution according to the detected resistance value.

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