Pulse assembly, suction valve, endoscope, and placement system

Abstract

Provided are a pulse assembly, a suction valve, an endoscope (10), and a placement system. The pulse assembly comprises a communication part (100), wherein the communication part (100) is provided with a channel (110), the channel (110) is provided with an inlet (120), a first outlet (130), and a second outlet (140), and the inlet (120) is used for communicating with an instrument tube (11) and / or a sheath tube (20); a shielding member (200), which is movably arranged on the communication part (100), wherein the shielding member (200) is capable of intermittently blocking the first outlet (130) in the case of movement; and a driving member (300), which is used for driving the shielding member (200) to move, thereby allowing the first outlet (130) to be intermittently blocked. The present invention achieves pulse control of the flow rate of a rinsing fluid, which significantly enhances the efficiency of calculus removal during surgery and can also flexibly adapt to different surgical requirements, thereby effectively shortening the surgery duration and reducing patient discomfort and risks.

Description

A pulse assembly, a suction valve, an endoscope, and an insertion system. Technical Field

[0001] This application relates to the field of medical device technology, and in particular to a pulse assembly, a suction valve, an endoscope, and an insertion system. Background Technology

[0002] With the continuous advancement of medical technology, medical endoscopes have become a core tool for diagnosing and treating various diseases of the digestive and urinary systems, playing a crucial role, especially in the treatment of stone-related diseases (such as kidney stones and gallstones). In lithotripsy of the urinary system, the endoscope is inserted into the renal pelvis through a sheath, and the stones are broken up using a laser or other energy source. After lithotripsy, the gap between the endoscope and the sheath usually serves as a reflux channel, helping to remove stone fragments and flushing fluid, thereby keeping the operating area clean and reducing the occurrence of complications.

[0003] During this procedure, irrigation fluid is injected through the instrument tubing and aspirated through the sheath to remove lithotripsy and maintain a clear field of vision. However, due to the complex operating area and confined space, some lithotripsy is difficult to remove effectively with the irrigation fluid, requiring a longer irrigation time to expel it. This not only prolongs the operation time but also increases the patient's risks and discomfort. Summary of the Invention

[0004] To address the aforementioned problems, this application provides a pulse assembly, a suction valve, an endoscope, and an insertion system.

[0005] In a first aspect, this application provides a pulse component, which adopts the following technical solution:

[0006] A pulse assembly for use with an endoscope and / or sheath, the endoscope including an instrument tube comprising:

[0007] The connecting portion has a channel having an inlet, a first outlet, and a second outlet, the inlet being used to communicate with the instrument tube and / or sheath;

[0008] A blocking element, movably disposed in the communicating portion, the blocking element being capable of intermittently blocking the first outlet when movable; and

[0009] A driving element is used to drive the blocking element to move so that the first outlet is intermittently blocked.

[0010] Secondly, this application provides an suction valve, which adopts the following technical solution:

[0011] An aspiration valve includes a pulse assembly as described in the above technical solution, and further includes a valve cap disposed on the communicating portion. The valve cap includes a pressing portion, which is elastic, and the pressing portion is provided with an atmospheric port, which is connected to the channel.

[0012] The driving member is disposed in the connecting part. When the pressing part is pressed by an external force, the pressing part can undergo elastic deformation to close the air vent and trigger the driving member, thereby driving the rotating part to rotate relative to the connecting part.

[0013] Thirdly, this application provides an endoscope, which adopts the following technical solution:

[0014] An endoscope, comprising the suction valve described in the above technical solution.

[0015] Fourthly, this application provides an implantation system, which adopts the following technical solution:

[0016] An insertion system includes a sheath and an endoscope as described in the above-described technical solution; it also includes a connecting tube, one end of which is connected to the sheath and the other end of which is connected to the inlet.

[0017] This application has the following advantages and beneficial effects:

[0018] The pulse assembly of this application, through intermittent control of the blocking element, can flexibly adjust the flow area of ​​the liquid, thereby achieving precise flow rate control and optimizing the flushing effect of stones. Specifically, when the blocking element is active, it intermittently opens the first outlet, thereby changing the flow area of ​​the fluid through the channel. The second outlet remains open to ensure stable liquid flow. Based on this, by controlling the opening and closing of the first outlet, the flow area and flow rate of the liquid can be adjusted.

[0019] When the first outlet is open, the liquid flow area is the sum of the areas of the first and second outlets, thus increasing the liquid flow rate. At this time, the increased flow velocity effectively carries the stones outward, improving the stone removal efficiency. Conversely, when the first outlet is closed, the liquid flow area is only the area of ​​the second outlet, and the flow velocity slows down. This reduced flow velocity design can create pressure fluctuations in localized areas, helping to loosen or move the stones, making them easier to flush out of the body.

[0020] The advantage of this structural design lies in its ability to regulate the fluid flow rate by controlling the opening and closing of the first outlet. This ensures that the flow rate of the irrigation fluid meets both the needs of stone removal and the flow rate requirements of different surgeries. At high flow rates, the fluid effectively moves the stones, reducing stagnation; at low flow rates, the fluid creates localized pressure fluctuations, providing better impact force to help break up or expel the stones.

[0021] Furthermore, the intermittent opening of the first outlet by the shielding device causes the flow of the irrigation fluid to become fluctuating rather than constant. This fluctuating flow not only increases the efficiency of stone removal but also helps to disperse, impact, and expel the stones. Compared to a constant flow rate design, this fluctuating flow effectively reduces the time that stones remain in the surgical area, avoiding the problem of stones not being effectively carried away when the flow rate is uniform, thereby improving surgical efficiency.

[0022] Furthermore, the shielding design allows for flexible control of the flow rate according to different surgical needs. In some surgeries, a faster flow rate may be required to quickly remove stone fragments; while in other cases, a slower flow rate ensures that the irrigation fluid thoroughly cleanses the surgical area, avoiding unnecessary impact on surrounding tissues. The shielding device achieves this flexible adjustment by regulating the flow area, ensuring that the flow rate meets the needs of stone removal while adapting to the actual requirements of different surgical procedures, thereby improving surgical safety and efficiency and reducing patient risks and discomfort during the procedure.

[0023] In summary, this application achieves pulse control of the irrigation fluid flow rate through the design of adjustable flow rate, which significantly improves the efficiency of stone removal during the operation. At the same time, it can flexibly adapt to different surgical needs, ultimately effectively shortening the operation time and reducing patient discomfort and risks. Attached Figure Description

[0024] Figure 1 is a structural schematic diagram of an embodiment of this application;

[0025] Figure 2 is a first schematic cross-sectional view of an embodiment of this application;

[0026] Figure 3 is a second schematic cross-sectional view of an embodiment of this application;

[0027] Figure 4 is a schematic diagram of the exploded structure of an embodiment of this application;

[0028] Figure 5 is an enlarged structural diagram of part A in Figure 3;

[0029] Figure 6 is a schematic diagram of the endoscope;

[0030] Figure 7 is a partial cross-sectional view of the endoscope;

[0031] Figure 8 is a schematic diagram of the implantation system according to an embodiment of this application.

[0032] The diagram is marked as follows:

[0033] 10. Endoscope; 11. Instrument tube; 12. Port; 20. Sheath; 30. Connecting tube; 100. Connecting part; 110. Channel; 120. Inlet; 130. First outlet; 140. Second outlet; 150. Elastic limiting part; 200. Shielding part; 210. Rotating part; 211. Connecting hole; 220. Elastic diaphragm; 221. Buffer space; 230. Spiral groove; 300. Driving part; 310. Valve stem; 311. Protrusion; 400. Valve cap; 410. Pressing part; 411. Air vent. Detailed Implementation

[0034] In the various embodiments of this application, "proximal end" and "far end" refer to the distance of each component from the operator in the usage environment. The end closer to the operator is designated as the "proximal end", and the end farther from the operator is designated as the "far end".

[0035] In urological lithotripsy, particularly percutaneous nephrolithotomy (PCNL), an endoscope is typically inserted into the renal pelvis through a sheath. After the stones are broken up using a laser, the flushing fluid and stone fragments are drained through the reflux channel formed between the endoscope and the sheath. However, in practice, stone fragment deposition frequently occurs. This deposition can obstruct the operating area, affecting subsequent lithotripsy procedures and reducing surgical efficiency. Therefore, it is usually necessary to remove most of the stone fragments with flushing fluid before continuing the lithotripsy procedure.

[0036] The inventors discovered that existing irrigation solutions generally maintain a uniform flow rate during irrigation. However, when the flow rate is constant, the irrigation force is often insufficient to effectively remove all stones, especially in complex surgical areas with confined spaces. This is because the force exerted by a uniformly flowing liquid on the stones is relatively singular and stable, making it difficult to overcome the resistance caused by irregular shapes, rough surfaces, or stones lodged in tissue folds. Furthermore, in surgical areas with depressions or blind spots, a uniformly flowing liquid easily creates stagnant zones in these areas, making it difficult for the irrigation solution to effectively reach or transport stones. Simultaneously, the lack of flow rate variation also means insufficient disturbance force on the stones, failing to break down the adhesion or friction between the stones and surrounding tissues, further leading to stone retention. These problems make irrigation solutions with constant flow rates less efficient at removing stones, potentially requiring longer irrigation times, thus increasing surgical time and patient discomfort.

[0037] To address the aforementioned issues, this application provides a baffle design capable of dynamically adjusting the flow rate of the irrigation fluid. The baffle can regulate the flow rate by altering the flow area of ​​the irrigation fluid, thereby significantly improving stone removal efficiency. When the flow rate increases, the irrigation fluid provides a stronger impact force, aiding in stone transport; conversely, when the flow rate decreases, the pressure fluctuations generated by the irrigation fluid in localized areas can loosen embedded stones or change their orientation, making them easier to remove. This intermittent change in flow rate effectively disrupts stone retention, improves stone removal efficiency, reduces surgical time, and lowers patient surgical risks and discomfort. This flow rate regulation design demonstrates significant advantages in complex surgical environments, providing a more efficient and safer solution for lithotripsy.

[0038] The pulse assembly, suction valve, endoscope, and insertion system provided in this application will be described in detail below with reference to Figures 1 to 8, through specific embodiments and application scenarios.

[0039] The first aspect of this embodiment describes a pulse component in detail.

[0040] Referring to Figures 6 and 8, this application discloses a pulse assembly applied to endoscope 10 and / or sheath 20 to adjust the flow rate of irrigation fluid, thereby improving the efficiency of lithotripsy removal and adapting to different surgical needs.

[0041] Referring to Figures 6 and 8, in some embodiments, the endoscope 10 includes a handle and an insertion portion, within which an instrument tube 11 is disposed. The instrument tube 11 is used to inject irrigation fluid into the patient's body. During the surgical procedure, the insertion portion of the endoscope 10 is typically inserted into the sheath 20, thereby forming a reflux channel 110 between the sheath 20 and the insertion portion. This channel 110 is responsible for expelling the irrigation fluid and stone fragments from the body. In the prior art, the irrigation fluid is typically injected and discharged at a constant flow rate; however, this stable flow rate may result in some stone fragments not being effectively expelled. To address this problem, this application provides a technical solution that can periodically adjust the flow rate of the irrigation fluid by introducing a pulse component.

[0042] In one embodiment, referring to Figures 7 and 8, a pulse assembly is disposed on the instrument tube 11. The pulse assembly includes a connecting portion 100 and a driving member 300. A blocking member 200 is disposed within the connecting portion 100, and the connecting portion 100 has an inlet 120, a first outlet 130, and a second outlet 140. The inlet 120, the first outlet 130, and the second outlet 140 are connected to the instrument tube 11. Liquid in the instrument tube 11 enters the connecting portion 100 through the inlet 120 and then flows out of the connecting portion 100 through the first outlet 130 and / or the second outlet 140. The driving member 300 can control the blocking member 200 to intermittently block the first outlet 130. When the blocking member 200 blocks the first outlet 130, the flow area of ​​the flushing fluid decreases, resulting in an increase in flow rate; when the blocking member 200 unblocks, the flow area of ​​the channel 110 is restored, and the flow rate decreases. This periodic change in flow velocity generates intermittent impact force, which helps to loosen the gravel and change its position, thereby improving the efficiency of gravel transportation and discharge.

[0043] Through the above structural design, this solution overcomes the limitation of the liquid's limited force on stones under a single flow rate. Especially when stones are embedded in tissue folds or have irregular shapes, the high flow rate and periodic pressure fluctuations help overcome the adhesion and friction between the stone and surrounding tissue, making it easier to remove the stone fragments from the body. Furthermore, the position and shape of the shielding component 200 and the driving component 300 can be adjusted according to different surgical needs, thus adapting to diverse surgical environments.

[0044] In another embodiment, referring to Figures 6 and 8, the pulse assembly is disposed on the sheath 20 and communicates with the return channel 110 between the sheath 20 and the insertion part. This pulse assembly also includes a connecting part 100 and a driving member 300. A blocking member 200 is disposed within the connecting part 100, having an inlet 120, a first outlet 130, and a second outlet 140. The flushing fluid enters the connecting part 100 through the inlet 120 and flows out through the first outlet 130 and / or the second outlet 140. The driving member 300 can control the blocking member 200 to intermittently block the first outlet 130, thereby changing the flow area of ​​the return channel 110. When the blocking member 200 reduces the flow area of ​​the return channel 110, a negative pressure is formed within the return channel 110, increasing the flow velocity and driving more gravel outwards; when the flow area recovers, the flow velocity slows down, but pressure fluctuations help loosen the retained gravel.

[0045] This design not only enhances the suction effect of the return channel 110, but also creates different flow velocity gradients within the return channel 110, avoiding the stagnation problem caused by uniform flow velocity. This design is particularly suitable for situations with complex surgical areas and narrow spaces, helping to reduce the deposition and retention of lithotripsy.

[0046] In some implementations, the pulse assembly can be applied to both the instrument tube 11 and the sheath 20 simultaneously. Specifically, one pulse assembly is connected to each of the instrument tube 11 and the sheath 20. By adjusting the flow rate changes within the instrument tube 11 and the return channel 110, the injection and discharge of the flushing fluid can be synchronously regulated. For example, when the flow rate in the instrument tube 11 increases, the injection pressure of the flushing fluid can be enhanced, which helps to loosen the stones; simultaneously, the flow rate in the return channel 110 will also increase synchronously, which is beneficial for quickly transporting the stones out of the body. The coordinated operation of the two pulse assemblies not only optimizes the flushing effect but also effectively reduces stagnation and improves the efficiency of stone removal.

[0047] In some embodiments, referring to Figures 1 and 2, the pulse assembly includes a connecting portion 100, a shielding member 200, and a driving member 300. The connecting portion 100 has a channel 110, which has an inlet 120, a first outlet 130, and a second outlet 140. The inlet 120 is used to communicate with the instrument tube 11 and / or the sheath 20. The first outlet 130 and the second outlet 140 are both irrigation fluid outflow channels 110.

[0048] A blocking member 200 is movably disposed in the connecting portion 100, and the blocking member 200 can intermittently block the first outlet 130 when it is active. A driving member 300 is used to drive the blocking member 200 to move, so that the first outlet 130 is intermittently blocked. The movement of the blocking member 200 allows the first outlet 130 to alternate between blocking and unblocking, thereby regulating the flow rate of the flushing fluid. When the blocking member 200 blocks the first outlet 130, the flow area decreases, resulting in an increase in the flow rate of the flushing fluid. This increase in flow rate can generate a stronger impact force, which helps to effectively dislodge stones, especially when the stones are embedded in tissue folds or have irregular shapes. The high flow rate can effectively overcome the adhesion between the stones and the tissue, thereby promoting the discharge of the stones.

[0049] Conversely, when the obstruction 200 releases its blockage of the first outlet 130, the flow area of ​​the channel 110 returns to its original state, and the flow rate slows down. This slowdown helps prevent excessive impact on surrounding tissues from the rapid flow of flushing fluid, while also providing conditions for the loosening and further movement of the fragments. In this way, the flow rate of the flushing fluid produces beneficial fluctuations in each cycle, which not only effectively removes stones but also optimizes the transport and discharge of fragments at different flow rates.

[0050] The structure and driving method of the shielding component 200 can be flexibly selected according to the actual application requirements in order to control the flow rate of the flushing fluid.

[0051] Specifically, the blocking component 200 can be in the form of a valve plate, located at the first outlet 130. When the driving component 300 is an electric device, the valve plate is rotated or moved by the electric device, thereby controlling the opening and closing of the first outlet 130. The electric device can include an electric motor, a stepper motor, or a servo motor, etc. Through precise control of the driving component 300, the valve plate can be precisely switched on and off as needed. When the valve plate blocks the first outlet 130, the flow area decreases, thereby increasing the flow rate of the flushing fluid; when the valve plate unblocks, the flow area is restored, thereby slowing down the flow rate. This control method can flexibly adjust the flow rate of the flushing fluid, thereby regulating the impact force on the stones, which is beneficial for the discharge of stone fragments and the optimized distribution of the cleaning fluid.

[0052] Furthermore, the blocking component 200 can also be configured as an airbag at the first outlet 130, and the driving component 300 controls the expansion or contraction of the airbag by inflating or deflating it. The expansion of the airbag causes the first outlet 130 to be blocked, thereby reducing the flow area and increasing the flow rate; the contraction of the airbag unblocks the first outlet 130, thereby restoring the flow area and slowing the flow rate. This airbag design is relatively simple and easy to control, and due to the elasticity of the airbag, it can adapt well to the working requirements under different pressures, thereby regulating the flow state of the flushing fluid and helping to optimize the stone removal effect.

[0053] When the inlet 120 of the connecting part 100 is connected to the instrument tube 11, the injection flow rate of the irrigation fluid in the instrument tube 11 can be adjusted by the pulse assembly. The adjusted irrigation fluid flow rate can generate a strong impact during injection as needed, helping to loosen stones or clean the surgical area.

[0054] When the inlet 120 of the connecting section 100 is connected to the sheath 20, the suction flow rate of the flushing fluid in the return channel 110 can be adjusted by the pulse assembly. By increasing the suction flow rate, the ability to discharge gravel can be enhanced, especially for larger gravel or gravel deposited in complex areas.

[0055] The pulse assembly of this application enables precise adjustment of the irrigation fluid flow rate, meeting diverse surgical needs during both injection and aspiration. This design not only facilitates the loosening and removal of lithotripsy but also adapts to the complexity of the surgical area, reducing surgical time and patient discomfort. Furthermore, the pulse assembly's simple structure and high adaptability enhance overall surgical outcomes without significantly increasing equipment complexity.

[0056] According to an optional embodiment, referring to Figures 2 and 3, when the first outlet 130 is intermittently blocked, the flow rate when the first outlet 130 is opened two consecutive times is different. This design ensures that the flow rate is not exactly the same each time the first outlet 130 is opened, thus creating different flow rate fluctuations. Specifically, the flow rate may be larger when the outlet is opened for the first time, while the flow rate may be smaller when it is opened for the second time. This differentiated flow rate helps to regulate the flushing fluid flow rate, allowing the pressure fluctuations generated during flushing to more effectively disperse the stones and prevent them from remaining in the confined space or being adsorbed onto the pipe wall.

[0057] Furthermore, these variations in flow rate can produce a pulse-like effect, where periodic changes in velocity and flow rate help increase the impact and agitation of the flushing fluid, thereby improving the removal efficiency of the stones. This pulsed flow is particularly suitable for cleaning stones because the periodic fluctuations effectively promote the loosening, dispersion, and expulsion of the stones.

[0058] According to an optional embodiment, referring to Figures 2 and 3, the flow area of ​​the first outlet 130 is larger than that of the second outlet 140. Due to the larger flow area of ​​the first outlet 130, it can provide a higher flow rate, thereby achieving a larger flow velocity and stronger impact force when the first outlet 130 is open. By intermittently blocking the first outlet 130, the flow velocity is temporarily reduced when the first outlet 130 is blocked, which helps control fluctuations in the flow rate and pressure of the flushing fluid. When the blockage is released, the flow velocity increases, creating an impact force to drive the stones out. The larger flow area of ​​the first outlet 130 can provide a more pronounced pulse effect under the action of the shielding element 200, thereby improving the overall cleaning effect.

[0059] It is important to note that the so-called "intermittent closure" refers to the periodic opening and closing of the first outlet 130 within a certain cycle. For example, the first outlet 130 is opened at the first time, closed at the second time, and opened again at the third time. Such switching can effectively regulate the flow state of the flushing fluid and generate a pulse effect by utilizing the change in flow rate.

[0060] According to an optional embodiment, referring to Figures 3 and 4, the shielding member 200 includes a rotating part 210, which slides in conjunction with the inner wall of the communicating part 100. The rotating part 210 is provided with a communicating hole 211, which communicates with the channel 110.

[0061] When the rotating part 210 slides relative to the connecting part 100, the first outlet 130 can intermittently communicate with the connecting hole 211, and the driving member 300 is used to drive the rotating part 210 to slide relative to the connecting part 100. Through this structural design, flexible control of the flow rate can be achieved, so that the liquid flow exhibits a periodic fluctuation effect.

[0062] In this embodiment, the sliding mode of the rotating part 210 determines the intermittent communication between the first outlet 130 and the connecting hole 211. Specifically, by sliding with the connecting part 100, the rotating part 210 can control the opening and closing state of the connecting hole 211 at different positions, thereby adjusting the flow area of ​​the first outlet 130. When the rotating part 210 slides to a certain position, the first outlet 130 communicates with the connecting hole 211, and the liquid can flow out; while when the rotating part 210 slides to other positions, the first outlet 130 is blocked, and the flow of liquid is temporarily interrupted.

[0063] The drive unit 300 drives the rotating part 210 to slide relative to the communicating part 100, enabling intermittent blocking and opening of the first outlet 130 as needed. The drive unit 300 can be an electric device, a hydraulic device, or other suitable driving method. By precisely controlling the sliding of the rotating part 210, the opening and closing frequency and duration of the first outlet 130 are adjusted, thereby achieving periodic changes in the liquid flow rate. This intermittent blocking method can generate a pulse effect, causing fluctuations in the liquid flow rate by periodically changing the flow area, thus improving the flushing effect.

[0064] In practical applications, the cooperation between the rotating part 210 and the connecting part 100 can generate a certain degree of impact force and pressure fluctuation during the liquid flow process. Especially when dealing with stones or other stubborn substances, it can effectively loosen, push, and expel the stones. Through its rational structural design, this embodiment allows the pulse assembly to flexibly adjust the flow rate and adapt to different surgical needs, thereby improving the flushing effect and removal efficiency.

[0065] For example, the rotating part 210 may be provided with a plurality of spaced-apart connecting holes 211. When the rotating part 210 slides relative to the connecting part 100, different connecting holes 211 will gradually or intermittently connect with the first outlet 130, thereby controlling the opening and closing state of the liquid flow. This design can effectively realize the periodic change of liquid flow rate, thereby enhancing the flushing effect.

[0066] Specifically, the rotating part 210 is provided with multiple spaced-apart connecting holes 211. When the rotating part 210 slides within the connecting part 100, different connecting holes 211 will sequentially connect with the first outlet 130 to form a flow channel 110. When the rotating part 210 slides to a specific position, a certain connecting hole 211 connects with the first outlet 130, and liquid can flow out through this channel 110; while when the rotating part 210 slides to another position, another connecting hole 211 connects with the first outlet 130, or the flow channel 110 is completely blocked, and the liquid flow is temporarily interrupted. In this way, intermittent fluctuations in liquid flow can be achieved, producing a pulse-like effect.

[0067] In some designs, a connecting portion 100 can be provided on the rotating part 210. By rotating or sliding the rotating part 210, the connecting hole 211 on the rotating part 210 is intermittently connected to the first outlet 130. By adjusting the rotation angle or sliding distance of the rotating part 210, the opening and closing frequency of the connecting hole 211 can be controlled, thereby regulating the change in liquid flow rate. Unlike traditional constant flow rate designs, this design can generate periodic flow rate fluctuations, which helps to loosen stones or other retained substances, thereby promoting their expulsion.

[0068] Through this design, the relative sliding and rotation of the rotating part 210 and the connecting part 100 cause the flow of the irrigation fluid to exhibit rhythmic intermittent changes, which is beneficial for adjusting the irrigation effect under different surgical needs. When a stronger impact force is required, the sliding or rotation of the rotating part 210 can quickly connect the multiple connecting holes 211 with the first outlet 130, thereby increasing the flow rate; while when a more stable flow is required, the adjustment of the rotating part 210 can reduce flow rate fluctuations and ensure uniform liquid flow.

[0069] According to an optional embodiment, referring to Figures 3 and 4, a rotating part 210 is rotatably disposed on the communicating part 100 about a first axis. The number of communicating holes 211 is at least two, and these at least two communicating holes 211 are circumferentially distributed around the first axis on the rotating part 210. When the rotating part 210 rotates, the first outlet 130 can communicate with different communicating holes 211. The driving member 300 is used to drive the rotating part 210 to rotate. When the rotating part 210 rotates, the first outlet 130 can alternately or intermittently communicate with different communicating holes 211, thereby changing the flow area as the position of the rotating part 210 changes. This design allows the flow state of the first outlet 130 to be adjusted according to surgical needs, achieving a pulse effect and enhancing the flushing effect.

[0070] For example, a bearing or a rotating ring may be provided between the rotating part 210 and the connecting part 100 to reduce the friction between them. Reduced friction improves system durability and response speed, resulting in smoother and more stable rotation. Furthermore, a sealing ring may be provided between the rotating part 210 and the connecting part 100 to prevent flushing fluid from leaking through the gap between them, ensuring the stability and accuracy of fluid flow. The sealing design helps ensure that fluid flow remains within a predetermined path, unaffected by external interference, thereby preventing pressure loss or waste caused by fluid leakage.

[0071] According to an optional embodiment, referring to Figures 2 and 3, the connecting portion 100 is provided with an elastic diaphragm 220, forming a buffer space 221 between the elastic diaphragm 220 and the connecting portion 100. The elastic diaphragm 220 can elastically deform when the pressure at the inlet 120 exceeds a threshold, thereby increasing or decreasing the internal space of the channel 110, and simultaneously decreasing or increasing the buffer space 221. This elastic diaphragm 220 can elastically deform when the pressure at the inlet 120 exceeds a threshold, thereby adjusting the size of the internal space of the channel 110, thus alleviating or compensating for instability caused by excessive or insufficient pressure. When the pressure at the inlet 120 is too high, the deformation of the elastic diaphragm 220 can increase the internal space of the channel 110, slowing down the flow rate of the liquid and avoiding excessive pressure on the patient's tissues; while when the pressure at the inlet 120 is too low, the deformation of the elastic diaphragm 220 increases the buffer space 221, thereby helping to increase the flow rate and ensuring normal liquid flow. This design ensures that the pressure at the inlet 120 remains within a reasonable range, whether in the instrument tube 11 or the sheath 20, thus preventing discomfort or damage to the patient's tissues due to improper pressure.

[0072] Understandably, both instrument tube 11 and sheath 20 are connected to the patient's body. Therefore, in certain special circumstances, changing the flow state of the first outlet 130 may result in excessively low or high pressure at the inlet 120. Both excessive and insufficient pressure directly affect pressure fluctuations within the body, and the patient's tissues are very fragile and easily damaged by inappropriate pressure. For example, excessive pressure may compress surrounding tissues, leading to tissue damage or discomfort; while insufficient pressure may fail to provide enough impact force, resulting in poor flushing and ineffective stone removal. Therefore, adjusting the pressure at the inlet 120 to maintain it within an appropriate range is crucial for ensuring patient safety, avoiding tissue damage, and improving surgical outcomes.

[0073] According to an optional embodiment, referring to Figures 2 and 3, the flow areas of adjacent connecting holes 211 are different. Connecting holes 211 with different areas help to generate different flow rate variations, thereby enhancing the pulsating effect of the irrigation fluid and further optimizing the stone removal process. Through a reasonable design of the connecting hole 211 dimensions, the range of flow rate variation can be adjusted according to surgical needs, ensuring that the fluid flow generates appropriate impact force at different stages, which is beneficial for loosening and expelling stones.

[0074] According to an optional embodiment, the rotating part 210 has a first position, a second position, and a third position. When the rotating part 210 rotates relative to the communicating part 100, it can rotate sequentially between the first position, the second position, and the third position.

[0075] When the rotating part 210 is in the first position, it closes the inlet 120. In this state, the flushing fluid cannot flow into the connecting part 100 through the inlet 120, thus completely cutting off the fluid flow. At this time, by controlling the closed state of the inlet 120, the flow of the flushing fluid can be effectively controlled, unnecessary fluid inflow can be avoided, and precise flow control can be ensured.

[0076] When the rotating part 210 rotates between the first and second positions, it opens the inlet 120 and closes the first outlet 130. At this time, because the first outlet 130 is closed, the liquid flow is no longer disturbed by pulses, ensuring stable and uniform flow. This state can be used in operations requiring a stable flow rate, ensuring continuous liquid inflow and avoiding flow rate fluctuations caused by pulses.

[0077] When the rotating part 210 rotates between the second and third positions, it opens the inlet 120, and the first outlet 130 is intermittently connected to the connecting hole 211. In this state, by controlling the intermittent connection between the connecting hole 211 and the first outlet 130, the flow of the flushing fluid generates a pulse effect. Each time the connecting hole 211 intermittently connects to the first outlet 130, the fluid velocity increases rapidly, forming a pulse and generating a periodic impact force. This pulse effect helps to loosen and move the stones, improving the stone removal effect.

[0078] Through the above structural design, the precise switching of the rotating part 210 between different positions can not only achieve stable control of the liquid flow, but also bring better clearance effect through intermittent pulses. In particular, it can effectively improve the flow effect during the lithotripsy process, thereby optimizing the surgical operation and improving the surgical effect.

[0079] For example, when the rotating part 210 is in the first position, a portion of the rotating part 210 will close the inlet 120. When the rotating part 210 rotates away from the first position, the inlet 120 will not be closed by the rotating part 210, thereby opening the inlet 120.

[0080] The second aspect of this embodiment describes a suction valve in detail.

[0081] Referring to Figures 2 and 3, an aspiration valve includes a pulse assembly as described in the above embodiments, and also includes a valve cap 400. The valve cap 400 is disposed in the communicating portion 100. The valve cap 400 includes a pressing portion 410, which is elastic. The pressing portion 410 is provided with an atmospheric port 411, which is connected to the channel 110.

[0082] The driving member 300 is provided in the connecting part 100. When the pressing part 410 is pressed by an external force, the pressing part 410 can undergo elastic deformation to close the air vent 411 and trigger the driving member 300, thereby driving the rotating part 210 to rotate relative to the connecting part 100.

[0083] When the pressing part 410 is pressed by an external force, its elastic deformation triggers the following two functions: First, the pressing part 410, after deformation, seals the atmospheric port 411, thereby cutting off the connection between the atmosphere and the valve chamber; second, the deformation of the pressing part 410 further acts on the driving member 300, thereby realizing the rotation of the rotating part 210 between different positions. The pressing part 410 is made of an elastic material, such as silicone, rubber, or other elastic polymers suitable for medical devices. When pressed, the pressing part 410 deforms in a set direction. When the deformation reaches a certain level, it can effectively seal the atmospheric port 411 and transmit the force to the valve stem 310, achieving precise operation.

[0084] Specifically, the suction valve regulates the flow state through a pulse assembly to achieve pulsed suction of the liquid. When the suction valve is closed, the rotating part 210 is in the first position, at which time the inlet 120 is closed, the suction valve is in the closed state, and the second outlet 140 is connected to the negative pressure device. Outside air enters the channel 110 through the atmospheric port 411 and exits through the second outlet 140. At this time, the suction valve is equivalent to being in the closed state and will not suction the liquid inside the body.

[0085] When the suction valve needs to be opened, the rotating part 210 rotates between the first position and the second position. At this time, the inlet 120 is connected to the second outlet 140, and the atmospheric port 411 is closed after the pressing part 410 is deformed, thereby allowing liquid to be drawn out through the inlet 120 and the second outlet 140.

[0086] Furthermore, to achieve a pulse effect during suction, the rotating part 210 rotates between the second and third positions, during which the inlet 120 and the second outlet 140 remain in constant communication, while the first outlet 130 is intermittently closed. In this way, by adjusting the pulse effect, the liquid flow can be effectively driven, helping to remove liquid and debris from the body. Especially when cleaning difficult-to-move substances, the pulse flow helps to loosen and propel them.

[0087] Overall, this application, through the rational design of the valve cap 400, pressing part 410, air vent 411, rotating part 210, and driving component 300, can achieve precise suction function and generate pulse effect as needed, effectively optimizing the suction process, enhancing the therapeutic effect, and reducing patient discomfort.

[0088] According to an optional embodiment, referring to Figures 2 and 3, the drive member 300 includes a valve stem 310, which is movably disposed in the connecting portion 100. One of the rotating portion 210 and the valve stem 310 is provided with a spiral groove 230, and the other is provided with a protrusion 311 that cooperates with the spiral groove 230. The valve stem 310 is connected to the pressing portion 410, and the spiral axis of the spiral groove 230 coincides with the first axis.

[0089] When the pressing part 410 is pressed by an external force, the pressing part 410 can undergo elastic deformation to close the atmospheric port 411 and move the valve stem 310 along the first axis, thereby driving the rotating part 210 to rotate relative to the communicating part 100. Through the cooperation of the spiral groove 230 and the protrusion 311, the linear motion of the valve stem 310 is converted into the rotational motion of the rotating part 210.

[0090] During operation, the external force applied by the pressing part 410 causes the valve stem 310 to move along the first axis. The engagement of the helical groove 230 and the protrusion 311 between the valve stem 310 and the rotating part 210 converts the linear motion of the valve stem 310 into the rotation of the rotating part 210, thereby regulating the working state of the suction valve.

[0091] In this way, the linear motion of the valve stem 310 drives the rotating part 210 to rotate, controlling the opening and closing state of the suction valve. The cooperation between the spiral groove 230 and the protrusion 311 ensures that the rotating part 210 rotates at a controllable and stable speed, thereby achieving precise control of the flushing fluid flow. Furthermore, this driving method conforms to the conventional operation of the suction valve, where the current suction valve achieves suction and non-suction functions by pressing. Without changing the existing driving method, this solution enables the suction valve to have a pulse suction function in addition to its existing suction function. This not only improves the functionality of the suction valve but also increases its applicability in medical surgery, especially in situations where pulse suction is required for better cleaning results.

[0092] According to an optional embodiment, referring to Figures 3 and 5, the connecting portion 100 is provided with an elastic limiting portion 150. When the rotating portion 210 is in the second position, the valve stem 310 contacts the elastic limiting portion 150 on the moving path of the valve stem 310.

[0093] When the rotating part 210 rotates between the second and third positions, the valve stem 310 can push the elastic limiting part 150 to undergo elastic deformation. The elastic limiting part 150 provides clear tactile feedback, helping the user to clearly perceive the current state of the suction valve, thereby realizing graded operation of normal suction and pulse suction functions and avoiding accidental triggering of the pulse component.

[0094] Specifically, when using the normal suction function, the user adjusts the rotating part 210 between the first and second positions. When the rotating part 210 rotates closer to the second position, the valve stem 310 contacts the elastic limit part 150 and generates a certain resistance. This tactile feedback indicates to the user that the normal suction position has been reached and no further pressure is required. When the user needs to activate pulse suction in addition to the normal suction function, they continue to press the valve cap 400, causing the valve stem 310 to push the elastic limit part 150 to deform further, thereby triggering subsequent linkage operations and entering the pulse suction mode. In this way, the elastic limit part 150 not only provides physical feedback but also ensures that the user can clearly distinguish between different functional modes, avoids misoperation, and improves the accuracy and comfort of operation.

[0095] Level 1 Operation (Normal Suction): The user presses the valve cap 400 until the valve stem 310 touches the elastic limit part 150 to provide basic suction function. At this time, the pulse component is not triggered.

[0096] Secondary operation (pulse suction): The user continues to press the valve cap 400, causing the valve stem 310 to push the elastic limit part 150 to deform, triggering the rotating part 210 to rotate between the second and third positions, further realizing the pulse effect.

[0097] Without adding complexity to the operation, the suction valve achieves dual functions (suction and pulse), meeting diverse needs in different surgical scenarios. The pulse component is only triggered when the user intentionally continues to press the valve cap 400, avoiding resource waste caused by activating the pulse component when not needed.

[0098] The elastic limiting part 150 can be made of a material with good elasticity and deformation recovery properties (such as silicone, medical plastic or elastic metal sheet). The elastic limiting part 150 can be fixed to the valve body or valve cap 400 by snap-fit, integral or welded.

[0099] The third aspect of this embodiment describes an endoscope in detail.

[0100] Referring to Figures 6 and 7, an endoscope 10 includes the suction valve described in the above embodiments. This gives the endoscope 10 the beneficial effects of the suction valve, which will not be elaborated further here. The suction valve is connected to the return channel 110 of the insertion section, enabling the endoscope 10 to achieve a combined effect of suction and pulse irrigation while possessing basic endoscopic functions.

[0101] In this embodiment, the suction valve is connected to the instrument tube 11 of the endoscope 10. The instrument tube 11 has a port 12 through which it can be connected to other tubes. This allows other tubes to divide the instrument tube 11 into a section on the suction valve side and a distal section, enabling the suction valve to aspirate liquid from other tubes. Specifically, when it is necessary to aspirate material from the instrument tube 11 using the endoscope 10, the port 12 can be closed to ensure that the suction valve is only connected to the instrument tube 11. Conversely, when it is necessary to aspirate material through other tubes, the port 12 can be opened and a connecting component inserted to block the instrument tube 11, while simultaneously maintaining communication between the suction valve and other tubes, ensuring that liquid or material can be aspirated from other tubes.

[0102] To achieve the aforementioned switching function, the connecting component can be a blocking block with a flow channel inside, which communicates with the instrument tube 11 facing the suction valve. This design effectively isolates the instrument tubes 11 on both sides of the blocking block, while the flow channel connects the suction valve to other pipes, thus enabling flexible operation of the suction valve.

[0103] The fourth aspect of this embodiment provides a detailed description of an insertion system.

[0104] Referring to Figures 6 and 8, an insertion system includes a sheath 20 and an endoscope 10 as described in the above embodiment; it also includes a connecting tube 30, one end of which is connected to the sheath 20, and the other end is connected to the inlet 120, thereby connecting the sheath 20 and the inlet 120. After the irrigation fluid is injected into the body through the instrument tube 11 of the endoscope 10, it passes through the return channel 110 between the sheath 20 and the insertion part, carrying stone fragments or tissue debris, and is discharged through the connecting tube 30, thus forming a circulating irrigation path. The flexible design of the connecting tube 30 allows the relative position of the sheath 20 and the suction valve to be adjusted according to surgical needs, improving the operational flexibility of the system. The suction valve of the endoscope 10, combined with a pulse assembly, can periodically change the flow rate of the irrigation fluid in the connecting tube 30 during aspiration, creating a pulse effect.

[0105] The components of the implantation system (sheath 20, endoscope 10, connecting tube 30) can be modularly designed, facilitating combination or replacement according to different surgical scenarios. For example, in urological surgery, sheaths 20 and connecting tubes 30 of different diameters or lengths can be selected to adapt to the anatomical structures of different patients.

[0106] The insertion system combines the sheath 20, endoscope 10, and connecting tube 30, simplifying the layout of surgical instruments and unifying the functions of irrigation, aspiration, and lithotripsy removal. The design of the suction valve and connecting tube 30 allows the operator to perform multiple procedures within a single system, eliminating the need for frequent instrument changes and reducing intraoperative intervention. The guiding effect of the connecting tube 30 and the pulsating effect of the suction valve facilitate rapid removal of lithotripsy, preventing surgical interruption or complications caused by lithotripsy blockage.

Claims

1. A pulse assembly for use in an endoscope (10) and / or a sheath (20), the endoscope (10) comprising an instrument tube (11), characterized in that, include: The connecting part (100) has a channel (110) having an inlet (120), a first outlet (130) and a second outlet (140), the inlet (120) being used to communicate with the instrument tube (11) and / or the sheath (20); A blocking member (200) is movably disposed in the connecting portion (100). The blocking member (200) can intermittently block the first outlet (130) when it is active. The blocking member (200) includes a rotating portion (210). The rotating portion (210) is rotatably disposed in the connecting portion (100) with a first axis as the rotation center. The number of connecting holes (211) is at least two. The at least two connecting holes (211) are circumferentially distributed in the rotating portion (210) with the first axis as the center. When the rotating portion (210) rotates, the first outlet (130) can communicate with different connecting holes (211). as well as A drive (300) is used to drive the blocking member (200) to move so that the first outlet (130) is intermittently blocked.

2. A pulse assembly according to claim 1, characterized in that, When the first outlet (130) is intermittently blocked, the flow rate is different when the first outlet (130) is opened on two consecutive occasions. And / or, the circulation area of ​​the first outlet (130) is greater than the circulation area of ​​the second outlet (140).

3. A pulse assembly according to claim 1, characterized in that, The rotating part (210) slides with the inner wall of the communicating part (100), and the rotating part (210) is provided with a communicating hole (211), which communicates with the channel (110); When the rotating part (210) slides relative to the connecting part (100), the first outlet (130) can be intermittently connected to the connecting hole (211), and the driving member (300) is used to drive the rotating part (210) to slide relative to the connecting part (100).

4. A pulse assembly according to claim 3, characterized in that, The driving member (300) is used to drive the rotating part (210) to rotate; And / or, the connecting portion (100) is provided with an elastic diaphragm (220), and a buffer space (221) is formed between the elastic diaphragm (220) and the connecting portion (100). The elastic diaphragm (220) can undergo elastic deformation when the pressure at the inlet (120) exceeds a threshold, thereby increasing or decreasing the internal space of the channel (110), and simultaneously decreasing or increasing the buffer space (221). And / or, the flow areas of adjacent connecting holes (211) are different.

5. A pulse assembly according to claim 3 or 4, characterized in that, The rotating part (210) has a first position, a second position and a third position. When the rotating part (210) rotates relative to the connecting part (100), it can rotate sequentially between the first position, the second position and the third position. When the rotating part (210) is in the first position, the rotating part (210) closes the inlet (120); When the rotating part (210) rotates between the first position and the second position, the rotating part (210) opens the inlet (120) and the first outlet (130) is closed by the rotating part (210). When the rotating part (210) rotates between the second position and the third position, the rotating part (210) opens the inlet (120), and the first outlet (130) is intermittently connected to the connecting hole (211).

6. A suction valve, characterized in that, The pulse assembly according to claim 5 further includes a valve cap (400), the valve cap (400) being disposed on the communicating portion (100), the valve cap (400) including a pressing portion (410), the pressing portion (410) being elastic, the pressing portion (410) being provided with an air vent (411), the air vent (411) being communicating with the channel (110); The driving member (300) is disposed on the connecting part (100). When the pressing part (410) is pressed by an external force, the pressing part (410) can undergo elastic deformation to close the air vent (411) and trigger the driving member (300), thereby driving the rotating part (210) to rotate relative to the connecting part (100).

7. A suction valve according to claim 6, characterized in that, The driving component (300) includes a valve stem (310), which is movably disposed in the communicating part (100). One of the rotating part (210) and the valve stem (310) is provided with a spiral groove (230), and the other is provided with a protrusion (311) that cooperates with the spiral groove (230). The valve stem (310) is connected to the pressing part (410), and the spiral axis of the spiral groove (230) coincides with the first axis. When the pressing part (410) is pressed by an external force, the pressing part (410) can undergo elastic deformation to close the air vent (411) and move the valve stem (310) along the first axis direction, thereby driving the rotating part (210) to rotate relative to the connecting part (100).

8. A suction valve according to claim 7, characterized in that, The connecting part (100) is provided with an elastic limiting part (150). When the rotating part (210) is in the second position, the valve stem (310) contacts the elastic limiting part (150) on the moving path of the valve stem (310). When the rotating part (210) rotates between the second position and the third position, the valve stem (310) can push the elastic limiting part (150) to undergo elastic deformation.

9. An endoscope (10), characterized in that, Includes the suction valve as described in any one of claims 6-8.

10. An insertion system, characterized in that, It includes a sheath (20) and an endoscope (10) as described in claim 9; it also includes a connecting tube (30), one end of which is connected to the sheath (20) and the other end of which is connected to the inlet (120).

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