Double-pump variable pressure blood urine suction device

Abstract

The utility model discloses a double pump pressure blood urine suction device, containing catheterization part and suction part. The catheterization part is metal spiral reinforced catheter, and its distal end enters the urinary bladder through the three cavity catheter in reverse, and the proximal end is connected with the suction part. The suction part is composed of centrifugal pump and double shaft pump series connection, and the both are communicated through filter screen, and are drained through the external pipeline with one-way valve. When the thrombus does not block the pipeline, the double pump extracts blood urine and drains simultaneously. When the blockage occurs, the centrifugal pump idles while the double shaft pump operates normally. The suction process of the double shaft pump forms the reverse flow to the external catheter, which causes the one-way valve to close, and the negative pressure area is formed in the centrifugal pump cavity and is continuously strengthened. Finally, the strong negative pressure is transmitted to the distal end of the catheterization part, the blocked thrombus is sucked and discharged by the suction part. The device combines the high flow advantage of the centrifugal pump with the high negative pressure characteristics of the double shaft pump, which effectively solves the problem of pipeline blood clot blockage while ensuring the conventional flushing efficiency, and improves the safety and reliability of blood urine drainage treatment.

Description

Technical Field

[0001] This utility model relates to the field of medical device technology, and in particular to a dual-pump variable pressure hemoury suction device. Background Technology

[0002] After surgery, patients often need to rely on drainage tubes or catheters to drain accumulated fluids, such as blood, urine, and other possible secretions. However, these tubes are prone to blockage in practice, especially when the fluid contains blood clots or other solid substances. Once a blockage occurs, it not only interferes with normal fluid drainage but can also lead to a range of complications, including but not limited to infection, increased pain, and the risk of a second surgery.

[0003] Traditional treatment methods typically involve manual flushing or using negative pressure suction devices to attempt to remove the blockage. However, these traditional methods have significant limitations. While manual flushing can directly target the blockage, it is often difficult to completely remove all obstructions due to the complexity of the procedure, and the process is both time-consuming and labor-intensive, increasing the workload of healthcare workers. Furthermore, improper manual flushing can lead to further infection risks.

[0004] On the other hand, while negative pressure suction devices can provide some suction, their ability to effectively break up and remove larger or harder blood clots is often insufficient. The negative pressure range of traditional negative pressure suction devices (e.g., -125 to -450 mmHg) often results in insufficient suction when dealing with viscous blood clots due to negative pressure attenuation. Clinical observations show that when the blood clot volume exceeds one-third of the lumen diameter, the success rate of traditional negative pressure suction is only about 60%. This indicates that the effectiveness of existing technology in dealing with complex blockages still needs improvement.

[0005] CN216703155U discloses a system device for preventing postoperative blockage of drainage tubes and urinary catheters. This device has a negative pressure pump connector kit connected to its tubing for connecting to an external negative pressure suction device. When it is necessary to remove blood clots blocking the catheter, the negative pressure suction device can be connected through this connector kit to continuously suction and remove the blood clots.

[0006] However, this device primarily relies on a single-configuration negative pressure pump connector kit for negative pressure suction, which limits its negative pressure adjustment capabilities and makes it difficult to flexibly adjust the negative pressure intensity to meet different clinical needs. In cases of large blood clots or complex blockages, a single negative pressure setting may be insufficient to effectively remove the blockage, thus limiting the device's effectiveness in handling complex blockage scenarios.

[0007] Furthermore, on the one hand, there are differences in understanding among those skilled in the art; on the other hand, the applicant studied a large number of documents and patents when making this utility model, but due to space limitations, not all details and contents were listed in detail. However, this does not mean that this utility model does not have the features of these prior art. On the contrary, this utility model has all the features of the prior art, and the applicant reserves the right to add relevant prior art to the background art. Utility Model Content

[0008] To address the shortcomings of existing technologies, this application proposes a dual-pump variable pressure hematuria aspiration device, particularly an aspiration device capable of clearing blood clots from blocked catheters using varying negative pressure, aiming to solve one or more technical problems in the prior art.

[0009] This utility model relates to a dual-pump variable pressure hematuria aspiration device, which includes an aspiration section and a catheter section. The distal end of the catheter section is connected to the urethra via a urinary catheter, and the proximal end is detachably connected to the aspiration section. The aspiration section includes a centrifugal pump assembly and a biaxial pump assembly arranged in series. The outlet of the centrifugal pump assembly is connected to the inlet of the biaxial pump assembly to form a first passage inside the two assemblies. Both the centrifugal pump assembly and the biaxial pump assembly are connected to a connecting pipe to form a second passage outside the two assemblies. When the distal end of the catheter section is blocked, the one-way valve configured on the connecting pipe is closed to cut off the second passage, so that the biaxial pump assembly can independently form a stronger negative pressure to act on the blocked site through the first passage.

[0010] This novel hematuria aspiration device combines the advantages of a centrifugal pump and a biaxial pump, enabling flexible adjustment of negative pressure and flow rate under different conditions. When the passage is clear, the centrifugal pump provides a higher flow rate to ensure smooth drainage of the liquid; while when the distal end is blocked by blood clots or other obstructions, the biaxial pump provides a larger negative pressure, which, through the closure of the one-way valve, creates a strong negative pressure to suck up and remove the obstruction, thereby restoring the passage to its original patency.

[0011] According to a preferred embodiment, the centrifugal pump assembly includes a centrifugal pump chamber for accommodating the centrifugal pump. The distal end of the centrifugal pump chamber is configured with an assembly port connected to a catheter. The assembly port includes an inner sealing ring and an outer support ring. The outer periphery of the support ring has an annular snap-fit ​​protrusion that mates with the proximal interface of the catheter. The sealing ring is designed to expand radially during screwing, forming a dynamic adaptive seal that effectively prevents urine leakage. The snap-fit ​​protrusion of the support ring mates with the spiral guide groove of the catheter interface, achieving anti-torsional fixation through mechanical interlocking, preventing accidental loosening due to tubing traction during clinical operations.

[0012] According to a preferred embodiment, the biaxial pump assembly includes a biaxial pump chamber for housing the biaxial pump. A widening transition section is provided at the series interface between the biaxial pump chamber and the centrifugal pump chamber, with the inner wall of the transition section having a smooth, flared shape. This gradual widening design ensures a smooth decrease in flow velocity of urine as it enters the biaxial pump from the centrifugal pump outlet, eliminating turbulence and cavitation phenomena caused by sudden expansion of the flow channel. The streamlined connection between the flared end and the front guide plate of the biaxial pump rotor reduces energy loss caused by flow separation. This structure improves the overall efficiency of the biaxial pump series system by reducing the flow resistance coefficient, while simultaneously preventing high-speed flow from impacting and damaging the internal components of the pump body.

[0013] According to a preferred embodiment, the biaxial pump assembly includes a drive gear set and a drive motor. The drive motor is fixedly connected to the outer wall of the biaxial pump chamber via a flange, and its output shaft is coaxially connected to the drive gear of the drive gear set. The radial wedge-shaped anti-slip teeth on the flange contact surface form a mechanical interlock to prevent torque slippage, ensuring stable power transmission under high load conditions. The split flange design, combined with positioning guide posts, allows for micron-level alignment accuracy between the motor and the gear set, while also facilitating quick replacement of the drive unit. This structure solves the problems of vibration transmission and maintenance difficulties inherent in traditional direct-drive methods.

[0014] According to a preferred embodiment, the drive gear set includes a pair of meshing gears, with the gear screws penetrating the side wall of the biaxial pump chamber to transmit the driving force output by the drive motor to the biaxial pump inside the chamber. A stepped sealing ring at the penetration point of the drive gear shaft, together with the graphite stuffing box, forms a multi-level sealing barrier, preventing urine from seeping along the shaft and contaminating the drive system, while also preventing lubricating oil from entering the fluid channels. The bellows protective sleeve of the spline coupling ensures torque transmission efficiency while completely isolating external contaminants from entering the gear meshing area, ensuring long-term stable operation of the system in a sterile environment.

[0015] According to a preferred embodiment, the valve core of the one-way valve has a conical flow-guiding structure, and a progressive sealing contact area is formed between its closing surface and the valve seat. A guide rib is provided at the tail of the valve core to limit the deflection of the valve core. The sealing structure between the conical surface and the valve seat achieves reliable interlocking under all operating conditions from low pressure to high pressure through the progressive cooperation of line contact, surface contact and auxiliary sealing. The sliding cooperation between the tail guide rib and the inner wall of the valve body effectively limits the deflection of the valve core and ensures the alignment of the sealing pair.

[0016] According to a preferred embodiment, the catheter includes a tube body with an internally formed urinary drainage channel, and a fluid outlet at the proximal end of the tube body. The fluid outlet is detachably connected to an assembly port at the distal end of the suction unit. This detachable connection structure, through a progressive compression sealing design between the fluid outlet and the assembly port, significantly reduces the risk of interface leakage and simplifies clinical procedures. An anti-torsion snap-fit ​​mechanism ensures a secure connection, preventing accidental loosening due to patient movement or tubing traction, thus improving the overall reliability of the device.

[0017] According to a preferred embodiment, the connecting pipe includes a first channel opening connected to the outlet of the centrifugal pump assembly and a second channel opening connected to the outlet of the biaxial pump assembly, with a one-way valve disposed between the first and second channel openings. The one-way valve allows for switching between the two pump operating modes. When the pipeline is unobstructed, a high flow rate is maintained; when blockage occurs, a rapid switch to a strong negative pressure mode is made to effectively remove stubborn blood clots and restore the flow, significantly improving the device's adaptability to different clinical scenarios.

[0018] According to a preferred embodiment, the biaxial pump assembly includes a first gear and a second gear that mesh with each other, the tooth tips of which abut against the inner wall of the biaxial pump chamber to form a radial seal. The precise fit between the gears and the biaxial pump chamber creates multiple sealing barriers, significantly reducing fluid leakage and maintaining a stable negative pressure output. The continuous squeezing action generated by the dynamic meshing efficiently breaks up blood clots while reducing the risk of tissue damage caused by pressure fluctuations.

[0019] According to a preferred embodiment, the assembly port of the suction section is provided with a support core tube, the distal end of which is equipped with an anchoring tip, and the proximal end is detachably connected to the assembly port. When the catheter part is connected to the suction section, the support core tube can be advanced along the inner lumen of the catheter body, with its tip extending from the drainage window of the catheter head to form bidirectional anchoring. By integrating the support core tube into the assembly port of the suction section instead of the catheter body, it can be applied to existing three-lumen catheters without customized modifications. The distal anchoring tip of the support core tube extends from the drainage window of the catheter head to form bidirectional fixation, ensuring that the internal flow channel of the catheter maintains a sufficient cross-sectional area under strong negative pressure, effectively avoiding negative pressure attenuation caused by lumen collapse. Attached Figure Description

[0020] Figure 1 This is a perspective view of the suction part of the suction device of this utility model under conditions of blood and urine flow;

[0021] Figure 2 This is a perspective view of the suction part of the suction device of this utility model in the case of blood clot blockage;

[0022] Figure 3 This is a schematic diagram of the overall structure of the suction part and the catheterization part of the suction device of this utility model;

[0023] Figure 4 This is a schematic diagram of the internal structure of the suction device of this utility model under the condition of smooth urination;

[0024] Figure 5 This is a schematic diagram of the internal structure of the suction device of this utility model when it is blocked by blood clots;

[0025] Figure 6This is a schematic diagram of the internal structure of the suction device of this utility model when the blood clot is being sucked up and broken up.

[0026] List of reference numerals

[0027] 100: Suction section; 110: Centrifugal pump assembly; 111: Centrifugal pump chamber; 112: Assembly port; 120: Biaxial pump assembly; 121: Biaxial pump chamber; 122: Drive gear set; 123: Drive motor; 124: Power cord; 125a: First gear; 125b: Second gear; 130: Connecting tube; 131: One-way valve; 132: First channel opening; 133: Second channel opening; 200: Urinary catheter section; 210: Tube body; 211: Support core tube; 220: Catheter tip; 230: Discharge port. Detailed Implementation

[0028] The present invention will now be described in detail with reference to the accompanying drawings.

[0029] Orientation definition: The end of the device closer to the operator is the proximal end, and the end of the device closer to the user's urethra is the distal end.

[0030] This utility model relates to a dual-pump variable pressure hematuria aspiration device, such as... Figure 1 , Figure 3 As shown, the device includes a suction section 100 and a catheterization section 200. The distal end of the catheterization section 200 is provided with a urinary catheter to connect to the urethra, and the proximal end is connected to the suction section 100 through an interface. The suction section 100 is composed of a centrifugal pump assembly 110 and a biaxial pump assembly 120 connected in series. The centrifugal pump assembly 110 adopts a volute structure, and its outlet is directly connected to the inlet of the biaxial pump assembly 120 through a transition hole. A stainless steel filter screen is provided between the two to intercept blood clots and solid impurities, forming a first passage. The biaxial pump assembly 120 includes a symmetrically arranged dual-rotor structure. The rotor surface is covered with a flexible material layer, and a pressure relief port can be provided on the top of the housing. A connecting pipe 130 is led out from the side of the first passage to form a second passage for urine flow. A one-way valve 131 is installed in the middle of the connecting pipe 130, and the valve body adopts a conical sealing head that cooperates with the valve seat.

[0031] Preferably, the centrifugal pump assembly 110 and the biaxial pump assembly 120 of the dual-pump variable pressure hematuria suction device are modularly connected via a flange structure. An annular sealing groove is formed on the flange mating surface, and an elastic sealing ring is embedded within the groove. The sealing ring is made of corrosion-resistant fluororubber, which undergoes multi-directional deformation under pressure to achieve a three-dimensional seal. The housings of both pump assemblies are made of lightweight cast aluminum alloy, and locating pin holes and guide keys are evenly distributed along the edge of the flange to ensure precise alignment of the flow channel axis during docking.

[0032] Preferably, the main passage is formed by a centrifugal pump outlet connected directly to the biaxial pump inlet via a gradually expanding section, with a continuous and smooth flow path cross-section. A connecting pipe 130 extends from the middle of the main passage to form a bypass passage. The pipe body is made of transparent medical-grade polymer material, and the inner wall can be provided with spiral flow-guiding patterns to stabilize the flow. A one-way valve 131 is installed on the bypass passage, with the valve core using a conical sealing head that engages with the inclined surface of the valve seat. Figure 4 As shown, when the device is working normally, the main passage undertakes the main diversion function, the centrifugal pump impeller rotates to generate a stable negative pressure, and the twin-shaft pump synchronously assists in increasing the flow rate; the bypass passage maintains the basic flow rate, and the one-way valve 131 is in the open state.

[0033] Preferably, such as Figure 1 , Figure 2 As shown, the connecting pipe 130 includes a first channel opening 132 connected to the outlet of the centrifugal pump assembly 110 and a second channel opening 133 connected to the outlet of the biaxial pump assembly 120. A one-way valve 131 is disposed between the first channel opening 132 and the second channel opening 133. Figure 5 As shown, when a blockage occurs at the distal end of the catheter 200, the pressure in the main passage rises abnormally. At this time, the speed of the biaxial pump increases stepwise, and the pressure change in the connecting pipe 130 causes the diaphragm of the one-way valve 131 to close under load, cutting off the connection between the bypass passage and the main passage. At this time, the fluid path between the first channel opening 132 in the connecting pipe 130 and the one-way valve 131 is blocked. The biaxial pump assembly 120 independently forms a closed negative pressure circuit in the first passage, and its dual rotor meshing gap generates a pulsating suction force, which applies a directional impact force through the distal interface of the catheter 200 to break down the blockage (such as blood clots, thrombi, etc.). At the same time, the centrifugal pump disengages from the drive shaft through the electromagnetic clutch, and the impeller rotates freely to reduce energy consumption. The device housing adopts an upper and lower split structure, with the centrifugal pump drive unit and the biaxial pump motor independently encapsulated in an isolated compartment. During maintenance, the housing module can be quickly separated to avoid cross-contamination. After the blockage is suctioned and broken up, as Figure 6 As shown, the one-way valve 131 reopens, allowing urine containing debris from the blockage to drain through the second passage.

[0034] Preferably, such as Figure 1 , Figure 2As shown, the centrifugal pump assembly 110 includes a centrifugal pump chamber 111, with a stepped assembly port 112 formed at the distal opening of the chamber. An annular sealing ring, made of medical-grade silicone, is embedded in the inner layer of the assembly port 112. Its cross-section has a hollow lip structure, which expands radially under pressure to achieve dynamic sealing. The outer layer is a support ring made of polycarbonate, with several sets of L-shaped snap-fit ​​protrusions evenly distributed around its outer circumference. The protrusions have elastic barbs at their ends. A spiral guide groove is formed on the inner wall of the proximal interface of the catheterization part 200 at a corresponding position, with a locking recess at the bottom of the groove. When the assembly port 112 is aligned with the interface, the snap-fit ​​protrusions of the support ring screw into the guide groove, and the elastic barbs embed into the locking recess, creating circumferential constraint. Simultaneously, the sealing ring undergoes pre-tightening deformation due to pressure from the interface end face. A limiting step is provided on the inner side of the support ring, forming a double-locking structure with the protrusion at the root of the sealing ring to prevent axial movement of the sealing ring under pressure. After the interface is fully screwed in, the locking protrusion and the guide groove form a mechanical interlock, and the sealing ring lip forms a continuous annular contact surface with the inner wall of the interface, achieving synchronous axial and radial sealing of the fluid channel. The outer surface of the support ring is machined with anti-slip textures to facilitate the application of force during manual screwing operations.

[0035] Preferably, such as Figure 1 , Figure 2 As shown, the biaxial pump assembly 120 includes a biaxial pump chamber 121, whose inlet end is connected to the outlet end of the centrifugal pump chamber 111 via an expanding transition section. The transition section employs a gradually changing flow channel design, with its inlet diameter matching the centrifugal pump outlet and gradually expanding along the flow direction to the inlet size of the biaxial pump chamber 121. The inner wall forms a continuous, smooth, flared surface, with the radius of curvature adjusting synchronously with the pipe diameter to eliminate abrupt flow changes. The outer wall of the transition section is reinforced with annular reinforcing ribs, which are radially distributed along the flow direction to enhance the structural strength of the transition section. A flow guide grid can be installed at the inlet of the biaxial pump chamber 121, with the grid blades tilted at the same angle as the streamline direction at the flared end, guiding urine evenly into the rotor's working area. The transition section and the biaxial pump housing are integrally cast, and the inner surface is coated with an anti-corrosion coating to prevent urine corrosion.

[0036] Preferably, such as Figure 1 , Figure 2As shown, the twin-shaft pump assembly 120 includes a drive gear set 122 and a drive motor 123. The drive motor 123 is modularly connected to the outer wall of the twin-shaft pump chamber 121 via a split flange structure. The motor-side flange and the chamber-side flange adopt a symmetrical design, with radially distributed anti-slip teeth on the contact surfaces of the two flanges. The beveled directions of the teeth are opposite, forming an interlocking structure. Bolt through holes are evenly distributed around the flange circumference, and an annular sealing groove is set on the inner side of the hole and a silicone sealing ring is embedded to achieve simultaneous axial locking and radial sealing. The drive gear set 122 adopts a closed gearbox design, and the gearbox body and the twin-shaft pump chamber 121 are integrally cast to form a rigid base. The meshing clearance between the driving gear and the driven gear is adjusted by an eccentric bushing. The outer surface of the bushing is knurled to enhance the friction with the gearbox wall. A positioning guide post is set at the flange connection. The end of the post is tapered to facilitate assembly centering, and an annular groove is opened on the post body to form a secondary locking with the elastic claw of the chamber-side flange.

[0037] Preferably, such as Figure 1 , Figure 2 As shown, the drive gear set 122 includes a meshing driving gear and a driven gear, with their axes arranged parallel within a closed gearbox. The driving gear shaft penetrates the side wall of the dual-shaft pump chamber 121, and a combined sealing structure is used at the penetration point. The driven gear shaft is connected to the dual-shaft pump rotor via a spline coupling. The extended end of the driving gear shaft is connected to the output shaft of the drive motor 123 via a flange coupling. The flange contact surface of the coupling is machined with wedge-shaped anti-slip teeth, the direction of which is perpendicular to the torque transmission direction. After being bolted diagonally, an anti-slip connection is formed. A locating pin set is installed at the flange connection between the drive motor 123 and the gearbox to ensure positioning accuracy after repeated disassembly and assembly. The entire drive system housing adopts a split design, with the gearbox cover fixed by quick-release clamps, facilitating quick inspection of the internal gear pair status during maintenance.

[0038] Preferably, the power cable 124 is led out from the side of the housing of the drive motor 123. The lead-out end adopts an integrally formed waterproof elbow structure. The inner wall of the elbow is embedded with an annular stress buffer sleeve. The sleeve is interference-fitted with the outer sheath of the power cable 124. The root of the elbow is sealed to the motor housing by ultrasonic welding to prevent liquid from seeping in and to disperse the concentrated stress when the cable is bent, and to avoid the core of the wire from breaking.

[0039] Preferably, such as Figure 1 , Figure 2 As shown, the biaxial pump assembly 120 includes a first gear 125a and a second gear 125b that mesh with each other. Both gears have the same tooth profile and size and are symmetrically mounted on a parallel axis within the biaxial pump chamber 121. The tooth tips of the first gear 125a and the second gear 125b are fitted against the inner wall of the biaxial pump chamber 121 to form a radial seal.

[0040] When the two gears rotate, the meshing area of ​​the two gears and the inner wall of the twin-shaft pump chamber 121 together form a dynamically sealed chamber. The inlet end of the twin-shaft pump chamber 121 is directly connected to the outlet of the centrifugal pump assembly 110 via a flange, and the outlet end is fixed to the connecting pipe 130 via a threaded joint. The gear shaft end is connected to the output shaft of the drive gear set 122 via a coupling, and the torque of the drive motor 123 is transmitted to the gear shaft through this coupling. During gear meshing, the sealed chamber moves from the inlet side to the outlet side, and the volume of the chamber gradually decreases, thereby continuously squeezing the liquid to the outlet. Preferably, the top of the twin-shaft pump chamber 121 is provided with a removable maintenance cover plate for easy replacement of the sealing plate or cleaning of blockages.

[0041] Preferably, such as Figure 1 , Figure 2 As shown, the valve core of the one-way valve 131 adopts a conical flow-guiding structure design, with its conical surface forming a gradually narrowing sealing contact zone with the conical hole inside the valve seat. Several evenly distributed arc-shaped guide ribs extend from the tail of the valve core, with the outer edge of the ribs maintaining a sliding fit with the inner wall of the valve body, limiting radial displacement during axial movement of the valve core. A limiting flange is provided at the end of the valve core of the one-way valve 131, forming an axial stop with the step inside the valve body, thereby preventing the one-way valve 131 from falling out of the connecting pipe 130. An axial flow-guiding channel is provided inside the valve core, with a spiral texture on the inner wall of the channel to reduce flow resistance. The valve seat sealing surface is coated with a composite silicon carbide layer, forming a hard-soft fit sealing pair with the medical-grade silicone layer on the conical surface of the valve core. A visual observation window is provided on the side wall of the valve body, with a transparent resin sheet embedded at the edge of the window, allowing direct observation of the valve core's opening and closing status from the outside. A return spring is connected to the tail of the valve core. When reverse pressure is applied, the progressive contact between the conical surface of the valve core and the valve seat effectively disperses sealing stress.

[0042] In the dual-pump pressure-variable hematuria aspiration device, the opening and closing state of the one-way valve 131 is dynamically correlated with the device's operating conditions. During normal drainage, the centrifugal pump assembly 110 and the biaxial pump assembly 120 operate in tandem. Urine flows from the outlet of the centrifugal pump assembly 110 to the inlet (i.e., the first passage) of the biaxial pump assembly 120, while some fluid is diverted through the second passage of the connecting pipe 130. At this time, the positive fluid pressure in the connecting pipe 130 acts on the conical valve core of the one-way valve 131, pushing it to open. The guide ribs at the tail of the valve core slide along the inner wall of the valve body, ensuring that the valve core is centered and does not deflect, and the connecting pipe 130 remains unobstructed (see...). Figure 4 When the proximal end of the catheter 200 becomes blocked, the continuous operation of the biaxial pump assembly 120 causes a sudden drop in pressure at its inlet side (downstream of the connecting pipe 130), while the pressure at the outlet side of the centrifugal pump assembly 110 (upstream of the connecting pipe 130) rises due to fluid blockage. The pressure difference drives the conical valve core of the one-way valve 131 to move in the opposite direction, and the conical surface forms a progressive seal with the valve seat, completely closing the connecting pipe 130 (see...). Figure 5At this point, the biaxial pump assembly 120 independently forms a closed loop, and its high negative pressure acts directionally on the distal obstruction through the tube body 210 of the catheter section 200. After the obstruction is cleared, the catheter section 200 is unobstructed, the outlet pressure of the centrifugal pump assembly 110 decreases, the inlet pressure of the biaxial pump assembly 120 rises, and the pressure difference decreases, causing the locking force acting on the valve core of the one-way valve 131 to disappear. Under the action of gravity and the thrust of the fluid resuming flow, the valve core slides down and resets along the path defined by the guide ribs, the conical surface disengages from the valve seat, and the connecting pipe 130 reopens (see...). Figure 6 The device returns to the dual-pump coordinated drainage mode.

[0043] Preferably, such as Figure 3 As shown, the outer layer of the catheter body 210 of the catheter section 200 is covered with a spiral braided reinforcing layer, which is formed by interweaving polymer fibers and stainless steel wires to form an anti-torsion rib. The inner layer forms a urination channel with an oval cross-section. This channel is formed with a hydrophobic lubricating layer by co-extrusion process, and the surface has a micron-level texture to reduce the coefficient of friction. The catheter head 220 at the distal end of the catheter body 210 has a smooth arc-shaped end, and two sets of elliptical drainage windows are symmetrically opened on its side wall. The drainage windows are connected to the urination channel. The proximal end of the catheter body 210 is provided with a functional interface, the outlet 240, which adopts a standard Luer connector structure. The inner wall of the interface is machined with an annular sealing boss, which can form an interference fit with the sealing ring of the assembly port 112 of the suction section 100. When screwed on, a progressive compression seal is generated, so that the urination channel in the catheter body 210 can be detachably connected to the suction section 100.

[0044] Preferably, such as Figure 3 As shown, the assembly port 112 of the suction unit 100 integrates a support core tube 211. This support core tube 211 is made of elastic metal and is straight in its natural state. Its proximal end is connected to the assembly port 112 via a locking mechanism with anti-slip texture, and its distal end is designed as a J-shaped elastic anchoring tip. When the catheter body 210 of the catheter unit 200 is aligned with the suction unit 100, the support core tube 211 can be advanced forward along the inner lumen of the catheter body 210. When the support core tube 211 is advanced to the distal end of the catheter body 210, its elastic anchoring tip can protrude outward from the drainage window on the side wall of the catheter tip 220, forming a stable distal anchoring point. Simultaneously, the locking teeth of the proximal locking mechanism engage with the groove on the inner wall of the assembly port 112, achieving bidirectional anchoring of both ends of the support core tube 211. The outer surface of the support core tube 211 is covered with a smooth medical coating to ensure smooth urine flow. When the biaxial pump assembly 120 is started, the rigid tube body supporting the core tube 211 resists the radial contraction of the tube body 210, maintaining the flow channel unobstructed.

[0045] It should be noted that the above specific embodiments are exemplary. Those skilled in the art can devise various solutions inspired by the disclosure of this utility model, and these solutions all fall within the scope of this utility model and its protection scope. Those skilled in the art should understand that this utility model specification and its drawings are illustrative and do not constitute a limitation on the claims. The protection scope of this utility model is defined by the claims and their equivalents. Throughout the text, features introduced by "preferred" are merely optional and should not be construed as mandatory. Therefore, the applicant reserves the right to abandon or delete relevant preferred features at any time.

Claims

1. A dual-pump variable pressure hematuria aspiration device, comprising an aspiration section (100) and a catheter section (200), wherein the distal end of the catheter section (200) is connected to the urethra via a urinary catheter, and the proximal end is detachably connected to the aspiration section (100), characterized in that, The suction unit (100) includes a centrifugal pump assembly (110) and a biaxial pump assembly (120) arranged in series. The outlet of the centrifugal pump assembly (110) is connected to the inlet of the biaxial pump assembly (120) to form a first passage inside the two assemblies. Both the centrifugal pump assembly (110) and the biaxial pump assembly (120) are connected to a connecting pipe (130) to form a second passage outside the two assemblies. The connecting pipe (130) includes a first channel opening (132) connected to the outlet of the centrifugal pump assembly (110) and a second channel opening (133) connected to the outlet of the biaxial pump assembly (120). The one-way valve (131) is disposed between the first channel opening (132) and the second channel opening (133). When the distal end of the catheter (200) is blocked, the one-way valve (131) configured on the connecting tube (130) closes, thereby cutting off the second channel and allowing the biaxial pump assembly (120) to independently form a stronger negative pressure on the blocked area through the first passage. The assembly port (112) of the suction part (100) is provided with a support core tube (211). The distal end of the support core tube (211) is provided with an anchoring head end, and the proximal end is detachably connected to the assembly port (112). When the catheter part (200) is connected to the suction part (100), the support core tube (211) can be advanced along the inner lumen of the tube body (210), and its head end extends out from the drainage window of the catheter head (220) to form bidirectional anchoring.

2. The suction device according to claim 1, characterized in that, The centrifugal pump assembly (110) includes a centrifugal pump chamber (111) for accommodating the centrifugal pump. The distal end of the centrifugal pump chamber (111) is provided with an assembly port (112) connected to the catheter part (200). The assembly port (112) includes a sealing ring located in the inner layer and a support ring located in the outer layer. The outer periphery of the support ring is provided with an annular snap-fit ​​protrusion that mates with the proximal interface of the catheter part (200).

3. The suction device according to claim 2, characterized in that, The biaxial pump assembly (120) includes a biaxial pump chamber (121) for accommodating the biaxial pump. The biaxial pump chamber (121) and the centrifugal pump chamber (111) are connected in series with an enlarged transition section, the inner wall of which is in the shape of a smooth flared mouth.

4. The suction device according to claim 3, characterized in that, The biaxial pump assembly (120) includes a drive gear set (122) and a drive motor (123), wherein the drive motor (123) is fixedly connected to the outer wall of the biaxial pump chamber (121) via a flange, and its output shaft is coaxially connected to the drive gear set (122).

5. The suction device according to claim 4, characterized in that, The drive gear set (122) includes a pair of meshing gears, the screws of which pass through the sidewall of the biaxial pump chamber (121) to transmit the driving force output by the drive motor (123) to the biaxial pump inside the biaxial pump chamber (121).

6. The suction device according to claim 1, characterized in that, The valve core of the one-way valve (131) has a conical flow guiding structure, and a progressive sealing contact area is formed between its closing surface and the valve seat. The valve core tail is provided with guide ribs to limit the valve core deflection.

7. The suction device according to claim 2, characterized in that, The catheter (200) includes a tube (210) with an internal urination channel, and a liquid outlet (230) is provided at the proximal end of the tube (210). The liquid outlet (230) is detachably connected to the assembly port (112) at the distal end of the suction part (100).

8. The suction device according to claim 3, characterized in that, The biaxial pump assembly (120) includes a first gear (125a) and a second gear (125b) that mesh with each other, and the tips of the two gears are fitted with the inner wall of the biaxial pump chamber (121) to form a radial seal.

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