Pulse assembly, suction valve, endoscope, and insertion system

Abstract

The present application provides a pulse assembly, a suction valve, an endoscope, and an insertion system and relates to the field of medical devices. The pulse assembly comprises: a communication portion provided with a channel, wherein the channel is provided with an inlet and an outlet, and the inlet is used for communicating with a sheath tube and / or an instrument tube of the endoscope; a shielding member, arranged on the communication portion and located between the inlet and the outlet, wherein the shielding member has a first state and a second state; and a driving member, used for driving the shielding member to switch between the first state and the second state, wherein when the shielding member is in the first state, the channel is completely opened; when the shielding member is in the second state, at least part of the channel is blocked. Compared to the prior art, the present application has the advantage of intermittently changing the circulation area of an irrigation fluid to regulate the flow velocity of the irrigation fluid, thereby effectively improving the irrigation effect on calculi.

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, the pulse assembly comprising:

[0007] A connecting portion having a channel having an inlet and an outlet, the inlet being for communication with the instrument tube and / or sheath;

[0008] A blocking member is disposed in the connecting portion and located between the inlet and the outlet, the blocking member having a first state and a second state;

[0009] A driving element is used to drive the blocking element to switch between a first state and a second state.

[0010] When the blocking component is in the first state, the channel is fully open; when the blocking component is in the second state, at least a portion of the channel is blocked.

[0011] Secondly, this application provides an suction valve, which adopts the following technical solution:

[0012] A suction valve includes a valve body and a valve stem. The valve body has a valve cavity and is provided with an atmospheric port, a sample port, and a negative pressure port communicating with the valve cavity. The valve stem is movably disposed on the valve body to switch between a closed position and a suction position. When the valve stem is in the closed position, the atmospheric port can be connected to the negative pressure port. When the valve stem is in the suction position, the sample port can be connected to the negative pressure port.

[0013] It also includes a pulse component as described in the above technical solution, wherein the outlet is connected to the sample port, the driving member is disposed on the valve body, and when the valve stem moves, the driving member can be triggered to switch the blocking member between a first state and a second state.

[0014] Thirdly, this application provides an endoscope, which adopts the following technical solution:

[0015] An endoscope, comprising the suction valve described in the above technical solution.

[0016] Fourthly, this application provides an implantation system, which adopts the following technical solution:

[0017] 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.

[0018] This application has the following advantages and beneficial effects:

[0019] The shielding component of this application can intermittently change the flow area of ​​the flushing fluid, thereby regulating the flow rate of the flushing fluid and effectively improving the flushing effect of stones. Specifically, during the flushing process, the design of the shielding component can cause the flow rate of the flushing fluid to change periodically by changing the flow area. When the flow rate is faster, the flushing fluid can more effectively carry the stones away; while when the flow rate slows down, the flushing fluid can create pressure fluctuations in local areas, helping to loosen or push the stones. In this way, the stones can be better removed under the action of flushing fluid at different flow rates, avoiding the problem that stones cannot be effectively carried out when the flushing fluid flows at a constant speed.

[0020] Furthermore, by adjusting the flow area, the shielding element causes the flow of the flushing fluid to become fluctuating rather than constant, thereby improving the efficiency of stone removal. This intermittent flow helps disperse, impact, and expel the stones, reducing the likelihood of stones remaining in the operating area. Ultimately, this flow rate-adjusting design effectively shortens the operation time and reduces patient risks and discomfort during the procedure.

[0021] On the other hand, by adjusting the flow rate of the irrigation fluid using the shielding device, it can be controlled according to different surgical needs, thus avoiding situations where the flow rate is too fast or too slow. Specifically, in some surgeries, a faster flow rate may be needed to quickly remove stone fragments, while in other cases, a slower flow rate may be required to ensure that the irrigation fluid thoroughly cleanses the surgical area and avoids unnecessary impact on surrounding tissues. By adjusting the flow area, the shielding device enables flexible adjustment of the flow rate, ensuring that the flow speed of the irrigation fluid meets the requirements for stone removal while adapting to the actual needs of different surgical procedures, thereby improving the safety and efficiency of the surgery and reducing patient risks and discomfort. Attached Figure Description

[0022] Figure 1 is a first schematic diagram of the connected parts;

[0023] Figure 2 is a second schematic diagram of the connecting part;

[0024] Figure 3 is a schematic diagram of the suction valve;

[0025] Figure 4 is a first cross-sectional view of the suction valve;

[0026] Figure 5 is a second cross-sectional view of the suction valve;

[0027] Figure 6 is a third sectional view of the suction valve;

[0028] Figure 7 is an enlarged structural diagram of part A in Figure 6;

[0029] Figure 8 is a partial cross-sectional view of the endoscope;

[0030] Figure 9 is a schematic diagram of the endoscope;

[0031] Figure 10 is a schematic diagram of the assembled endoscope and sheath.

[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; 111. Inlet; 112. Outlet; 200. Shielding element; 210. Airbag; 211. Bag body unit; 212. Transition membrane; 300. Driving element; 310. Inflatable bag body; 400. Suction valve; 410. Valve body; 411. Air vent; 412. Sample port; 413. Negative pressure port; 414. Valve cavity; 420. Valve stem; 430. Valve cap; 431. Pressing part; 432. Elastic limiting part. 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 10, through specific embodiments and application scenarios.

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

[0040] Referring to Figures 9 and 10, this application discloses a pulse assembly applied to an endoscope 10 and / or sheath 20 to adjust the flow rate of the irrigation fluid, thereby improving the efficiency of lithotripsy removal and adapting to different surgical needs.

[0041] Exemplarily, the endoscope 10 includes a handle and an insertion section, wherein an instrument tube 11 is disposed within the handle and the insertion section, and the instrument tube 11 is used to inject irrigation fluid into the patient's body. During the surgical procedure, the insertion section of the endoscope 10 is typically inserted into the sheath 20, thereby forming a reflux channel 110 between the sheath 20 and the insertion section. The reflux channel 110 is responsible for draining the irrigation fluid and stone fragments from the body. In the prior art, the irrigation fluid is typically injected and drained at a constant flow rate, but this stable flow rate operation may result in some stone fragments not being effectively removed. 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, a pulse assembly is disposed on the instrument tube 11. This pulse assembly includes a drive element 300 and a blocking element 200, wherein the blocking element 200 is disposed within the flushing fluid channel 110 of the instrument tube 11 and can periodically change its blocking state within the channel 110 by the action of the drive element 300. When the blocking element 200 partially blocks the channel 110, the flow area of ​​the flushing fluid decreases, resulting in an increase in the flow rate of the flushing fluid; when the blocking element 200 unblocks, the channel 110 returns to its original area, and the flow rate decreases. This periodic change in flow rate can generate intermittent impact force, which helps to loosen the stones and change their residence position, thereby facilitating the transport and removal of the stones.

[0043] Through its structural design, this solution avoids the problem of limited force exerted by the liquid on the stone at a single flow rate. Especially when the stone is embedded in tissue folds or has an irregular shape, the higher flow rate and periodic pressure fluctuations help overcome adhesion and friction, making it easier to remove the stone fragments. In addition, the position and shape of the shielding component 200 and the driving component 300 can be adjusted as needed to adapt to different surgical environments.

[0044] In another embodiment, a pulse assembly is mounted on the sheath 20 and communicates with the reflux channel 110 formed between the sheath 20 and the insertion portion. The pulse assembly also includes a drive element 300 and a blocking element 200. The blocking element 200 can change the local flow area of ​​the reflux channel 110, thereby regulating the flow rate of the aspirated flushing fluid. Specifically, when the blocking element 200 reduces the flow area of ​​the reflux channel 110, the negative pressure formed within the channel 110 increases the flow rate, causing more gravel to flow outwards; when the area of ​​the channel 110 recovers, the flow rate decreases, but the pressure fluctuations formed within the channel 110 can help loosen any trapped gravel.

[0045] This design not only enhances the suction effect of the return channel 110 but also creates different velocity gradients in local areas, thus avoiding stagnation issues caused by uniform flow rates. This design is particularly suitable for complex surgical areas with limited space, helping to reduce stone deposition and retention.

[0046] In some designs, pulse components can be applied simultaneously to both the instrument tube 11 and the sheath 20, meaning that pulse components are connected to both tubes, with one connected to tube 11 and the other to sheath 20. By controlling 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. Specifically, when the flow rate in the instrument tube 11 increases, the injection pressure of the flushing fluid is enhanced, which helps loosen the stones; simultaneously, the flow rate in the return channel 110 is synchronously increased, which facilitates the rapid transport of the stones outside the body. The coordinated operation of the two pulse components can reduce stagnation to some extent and optimize the flushing effect.

[0047] In some designs, referring to Figures 1 and 2, the pulse assembly includes a connecting portion 100, a blocking element 200, and a driving element 300. The connecting portion 100 is a tubular structure with an inlet 111 and an outlet 112, providing a flow channel 110 for irrigation fluid between different components. The connecting portion 100 can be made of rigid or flexible materials to accommodate different surgical instrument requirements. The size and shape of the connecting portion 100 can be optimized according to the specific surgical scenario to ensure smooth flow of the irrigation fluid.

[0048] The baffle 200 is disposed between the inlet 111 and the outlet 112 of the connecting portion 100, and can adjust the flow area of ​​the flushing fluid by changing its own state. The baffle 200 has two working states. First state: The baffle 200 is fully open, keeping the channel 110 between the inlet 111 and the outlet 112 unobstructed, and the flushing fluid can flow through at the original flow rate. Second state: The baffle 200 partially or completely blocks the channel 110, resulting in a reduction in the flow area, thereby changing the flow rate of the flushing fluid or causing pressure fluctuations.

[0049] The drive unit 300 is used to drive the blocking member 200 to switch between a first state and a second state. The drive unit 300 can take various forms, including but not limited to mechanical, electric, or hydraulic devices. For example, the movement of the blocking member 200 can be controlled by rotating a valve plate via an electric motor or by inflating and deflating a pressure regulating airbag 210.

[0050] By adjusting the drive component 300, the shielding component 200 can dynamically change the flow area between the inlet 111 and the outlet 112 of the connecting part 100. When the flushing fluid flows through the connecting part 100, this change in flow area directly affects the flow rate of the flushing fluid.

[0051] When the shield 200 is in the first state, the channel 110 is fully open, and the flushing fluid can flow at the original flow rate, which is suitable for general flushing needs or scenarios that require rapid injection of flushing fluid.

[0052] When the shielding component 200 is in its second state, part of the channel 110 is blocked, reducing the flow area of ​​the channel 110 and significantly increasing the flow rate of the flushing fluid. This generates a large impact force locally, thereby loosening or transporting the stones. At the same time, the intermittent flow rate changes also generate pressure fluctuations, which help to break the adhesion between the stones and surrounding tissues, further enhancing the flushing effect.

[0053] When the inlet 111 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 111 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] For example, the shield 200 can be designed as a rotating plate, and the rotation of the rotating plate is controlled by the drive 300 to adjust the flow area of ​​the channel 110. Specifically, the rotating plate is installed inside the connecting part 100 and can rotate about a fixed axis. By changing the position or angle of the rotating plate, its relative relationship with the instrument tube 11 or the sheath 20 can be dynamically adjusted, thereby affecting the area of ​​the channel 110 in the instrument tube 11 and / or the flow area of ​​the return channel 110 in the sheath 20, and thus adjusting the flow rate of the flushing fluid.

[0057] The rotating plate is typically a flat structure and can be made of rigid materials (such as metal or hard plastic) to ensure stable operation under fluid pressure. The shape and size of the rotating plate can be optimized according to the specific design of channel 110, for example, using curved edges to facilitate smoother and more precise flow control. The drive unit 300 can adopt a simple and easy-to-operate pull-cord structure. When force is applied to the pull cord, the rotating plate can be rotated around the axis through the connecting mechanism, completing the switching of the blocking component 200 between different angles. The drive unit 300 is flexible in its selection and can use mechanical, electric, or pneumatic devices as needed, depending on the application environment and operational requirements.

[0058] According to an optional embodiment, referring to Figures 1 and 2, the blocking member 200 includes an airbag 210 disposed in the channel 110, and a driving member 300 is used to inflate or deflate the airbag 210. In a first state, the blocking member 200 is not inflated, allowing the channel 110 to be fully open; in a second state, the blocking member 200 is inflated, blocking at least a portion of the channel 110. In the first state, the airbag 210 is uninflated, has a small volume, and fits completely against the wall of the channel 110, thus allowing the channel 110 to be fully open. At this time, the flushing fluid can flow through the channel 110 at a uniform rate, suitable for routine flushing operations. In the second state, the driving member 300 inflates the airbag 210, causing it to expand and occupy part of the space in the channel 110, thereby reducing the flow area of ​​the channel 110. The reduced flow area leads to an increased flow rate of the irrigation fluid, creating a higher impact force, which is suitable for removing stubborn stones or improving stone removal efficiency. The inflation and deflation process of the airbag 210 is controlled by the drive unit 300, allowing for flexible switching between a first and second state, thereby achieving dynamic adjustment of the irrigation fluid flow rate. This process can be directly controlled by the surgical operator to respond to surgical needs in real time.

[0059] The airbag 210 is typically made of an elastic material, such as silicone or polyurethane, to ensure good durability and resilience during repeated inflation and deflation. The airbag 210 can be cylindrical, spherical, or designed with a matching irregular shape according to the cross-section of the channel 110, so as to fit tightly against the wall of the channel 110 and achieve a more efficient sealing effect.

[0060] The drive unit 300 is typically an inflation device, which can be a manual pump, a pneumatic system, or an electric pump. By controlling the entry or exit of gas, it regulates the expansion or contraction of the airbag 210. The drive unit 300 can be externally pressed or electrically controlled to flexibly meet the adjustment needs during surgery.

[0061] According to an optional embodiment, referring to Figures 1 and 2, the airbag 210 includes at least two bladder units 211, which are connected to each other. This connection between adjacent bladder units 211 enables a uniform pressure distribution during the inflation process of the airbag 210. Specifically, when the airbag 210 is inflated, gas can flow between the bladder units 211, resulting in a more uniform inflation of the airbag 210 and preventing over-inflation of any one unit, thus providing a stable flow rate regulation effect. With this structure, the overall inflation performance of the airbag 210 is more coordinated, adapting to channels 110 of different shapes and sizes.

[0062] According to an optional embodiment, the airbag 210 extends circumferentially along the channel 110. This arrangement allows the airbag 210 to form a uniform expansion area around the entire circumference of the channel 110, covering all parts of the channel 110. When the airbag 210 inflates, it can change the flow area of ​​the channel 110 over a large range, thereby regulating the flow rate. The circumferential extension helps ensure that the airbag 210 can uniformly block different areas of the channel 110 when inflated, further improving the efficiency and accuracy of gravel flushing.

[0063] According to an optional embodiment, referring to Figures 1 and 2, at least two capsule units 211 are arranged along the direction from inlet 111 to outlet 112. From the inlet side to the outlet side, the expansion pressure of the capsule units 211 gradually decreases or increases. This expansion pressure distribution design allows the capsule units 211 to expand or contract sequentially, thereby generating a more significant pulse effect within the channel 110. The sequential expansion of the capsule units 211 can produce a pulse ripple effect, causing the flow of the irrigation fluid to exhibit periodic changes. This change not only enhances the impact force on lithotripsy but also effectively prevents the formation of stagnant zones in the surgical area.

[0064] As the expansion pressure gradually decreases from the inlet 111 side, the capsule unit 211 closest to the inlet 111 will expand first, gradually pushing the flushing fluid towards the outlet 112. This design can form a stable pressure wave, helping to move the gravel. As the expansion pressure gradually increases from the inlet 111 side, the capsule unit 211 on the outlet 112 side will expand first, thereby providing phased control over the flow velocity in the channel 110, limiting liquid backflow, and enhancing the local flushing effect.

[0065] According to an optional embodiment, referring to Figures 1 and 2, a transition membrane 212 connects the bladder unit 211 near the outlet 112 and the bladder unit 211 near the inlet 111. The transition membrane 212 is located on the side of the bladder unit 211 near the center of the channel 110 and is used to cover the gaps or recessed areas between adjacent bladder units 211. The transition membrane 212 is in close contact with the center of the channel 110 and connects the edges of adjacent bladder units 211, thereby eliminating the recessed areas formed between the bladder units 211 due to their arrangement. The transition membrane 212 is typically made of a material with a certain degree of flexibility, allowing it to deform with the expansion and contraction of the airbag 210 without affecting the function of the bladder unit 211.

[0066] Due to the gaps between the capsule units 211, small recessed areas may form, where gravel or other particles can easily accumulate and become difficult to expel. By providing a transition membrane 212, these recessed areas are effectively sealed, forming a continuous flow channel 110, allowing the flushing fluid to more smoothly remove gravel as it passes through.

[0067] The transition membrane 212 and the capsule unit 211 form an integrated structure, avoiding additional assembly steps and enhancing the sealing and durability of the component. In the expanded state, the transition membrane 212 works together with the adjacent capsule unit 211 to ensure that the flow area within the channel 110 maintains a streamlined design as the flow area changes, reducing the generation of eddies or stagnant flow.

[0068] According to an optional embodiment, the drive unit 300 includes an inflatable bladder 210 body, which is connected to the airbag 210. When an external force presses on the inflatable bladder 210 body, the inflatable bladder 210 body deforms to inflate the airbag 210. When the external force is removed, the inflatable bladder 210 body returns to its original shape, and the gas in the airbag 210 is extracted to the inflatable bladder 210 body. The inflatable bladder 210 body is designed with elastic deformation and self-resetting functions. The inflation and deflation of the airbag 210 can be achieved by pressing and releasing the external force, thereby controlling the expansion and contraction state of the airbag 210.

[0069] The inflatable bladder 210 body is connected to the air bladder 210 via an air guide tube, allowing gas to flow freely between them. When an external force is applied to the inflatable bladder 210 body, the gas inside the bladder is compressed and enters the air bladder 210 along the air guide tube, causing the air bladder 210 to inflate. The inflation of the air bladder 210 can partially or completely block the channel 110, thereby altering the flow rate or circulation pattern of the flushing fluid. After the external force is removed, the inflatable bladder 210 body returns to its original shape due to its elastic material, creating a negative pressure inside. The gas inside the air bladder 210 is drawn back into the inflatable bladder 210 body, causing the air bladder 210 to contract to its original state. This process can be repeated without complex operation or additional power devices.

[0070] Inflation and deflation of the balloon 210 can be quickly achieved through simple pressing and releasing operations, thereby changing the flow area of ​​the channel 110 and improving the ease of operation of the device. The inflation state of the balloon 210 can be adjusted by pressing pressure and time, adapting to different surgical needs and flexibly controlling the flow rate of the irrigation fluid. The self-resetting characteristic of the balloon 210 body reduces the dependence on additional drive devices, ensuring the simplicity and reliability of the device, while reducing maintenance requirements. In urological surgeries, especially in complex anatomical areas, the balloon 210 body can effectively expel stone fragments and avoid fluid retention or stone residue by dynamically adjusting the inflation state of the balloon 210.

[0071] According to an optional embodiment, the flow area at the connection between the inflatable bladder 210 body and the bladder unit 211 is larger than the flow area at the connection between adjacent bladder units 211. This structural layout facilitates the staged transmission of airflow. Specifically, when an external force presses on the inflatable bladder 210 body, the airflow preferentially enters the bladder unit 211 directly connected to the inflatable bladder 210 body, causing it to inflate first; subsequently, the airflow gradually passes through the smaller connection between adjacent bladder units 211, causing them to inflate sequentially. This design achieves segmented, stepwise expansion dynamic adjustment, thereby creating a more pronounced pulse effect. The inflatable bladder 210 body is connected to the first bladder unit 211 via an air passage, and the flow area at this connection is relatively large, ensuring that when the inflatable bladder 210 body is pressed, the airflow preferentially enters the first bladder unit 211, causing it to inflate rapidly. Adjacent bladder units 211 are connected by air passages, and the flow areas of these air passages are relatively small, thus limiting the airflow velocity. This restriction requires a certain time difference for airflow transmission, causing the capsule units 211 to expand sequentially, gradually extending from the inlet side 111 to the outlet side 112. When the external force is removed, the gas flows in the opposite direction, sequentially flowing back from the capsule units 211 on the outlet side 112 to the inflatable capsule 210, causing each capsule unit 211 to gradually return to its initial state.

[0072] Understandably, to further optimize the exhaust process of the airbag 210 structure and prevent the first airbag unit 211 to return to its original shape from blocking the exhaust channels 110 of the remaining airbag units 211, a protruding structure (hereinafter referred to as a "protrusion strip") can be provided inside the first airbag unit 211 to return to its original shape. This protrusion strip can form a dedicated airflow channel between its inner wall and the center of the channel 110 when the airbag unit 211 returns to its original shape. Through this channel, the first airbag unit 211 to return to its original shape can be connected to adjacent airbag units 211, thereby effectively avoiding the blockage of the channel 110 caused by the exhaust of a single airbag unit 211. When the airbag unit 211 returns to its original shape, most of its inner wall will be tightly against the channel 110, thus blocking the gas flow path. However, due to the presence of the protrusion strip, a gap is maintained between the inner wall of the airbag unit 211 and the channel 110, thus forming an independent airflow channel 110. This flow channel can connect the capsule unit 211 that has recovered to its original state first and the adjacent capsule unit 211 that has not yet fully recovered, ensuring that gas can continue to be discharged.

[0073] When the pressing force is removed, the gas flows back from the outlet 112 side capsule unit 211 to the inlet 111 side in stages. The flow channel formed by the convex strip ensures that even if a capsule unit 211 recovers first, the gas thereafter can still be smoothly discharged from the subsequent capsule units 211, and the overall exhaust process will not be affected by the closure of the local channel 110.

[0074] The second aspect of this embodiment describes a suction valve in detail.

[0075] Referring to Figures 3 and 4, a suction valve 400 includes a valve body 410 and a valve stem 420. The valve body 410 has a valve cavity 414, and is provided with an atmospheric port 411, a sample port 412, and a negative pressure port 413 communicating with the valve cavity 414. The valve stem 420 is movably disposed in the valve body 410 to switch between a closed position and a suction position. When the valve stem 420 is in the closed position, the atmospheric port 411 can communicate with the negative pressure port 413; when the valve stem 420 is in the suction position, the sample port 412 can communicate with the negative pressure port 413. The suction valve 400 can achieve flexible control of the gas path by switching the position signal of the valve stem 420 to meet different operational requirements.

[0076] Furthermore, the suction valve 400 also incorporates a pulse assembly from the above embodiments. The outlet 112 of the pulse assembly communicates with the sample port 412, and the drive element 300 of the pulse assembly is disposed within the valve body 410 and is associated with the movement of the valve stem 420. When the valve stem 420 moves during operation, it triggers the drive element 300 to switch the blocking element 200 between a first state and a second state, thereby controlling the pulse assembly. It is understood that in some embodiments, the connecting portion 100 can serve as the valve body 410 of the suction valve 400, thus combining the suction valve 400 and the pulse assembly into a single component.

[0077] By integrating the pulse component into the suction valve 400, the effect of the pulse component can be triggered while the suction valve 400 is pressed or switched. Specifically, during the operation of the suction valve 400, not only can the flushing fluid in the return channel 110 between the insertion part and the sheath 20 be aspirated through the sample port 412, but the flow rate of the flushing fluid can also be periodically changed by the pulse component.

[0078] By combining the suction valve 400 with the pulse assembly, a single press of the suction valve 400 can simultaneously perform both suction and alteration of the irrigation fluid flow rate, simplifying the surgical procedure and reducing the operator's workload. The pulse assembly alters the irrigation fluid flow rate during suction, generating periodic pulses that enhance the impact force and removal efficiency of the irrigation fluid on the stones, facilitating faster removal of stones from the surgical area. The linked trigger design of the valve stem 420 and the drive component 300 eliminates the need for separate control of the pulse assembly, making the overall device more efficient and easier to operate.

[0079] The outlet 112 of the pulse assembly is connected to the sample port 412, which is directly connected to the return channel 110 between the insertion section and the sheath 20. This design ensures that the aspiration process of the irrigation fluid is not affected by additional structures, while ensuring that the pulse effect can act synchronously on the irrigation fluid. Pressing the suction valve 400 simultaneously switches the air path and the pulse assembly state, forming a periodic change in flow rate to adapt to the optimization of lithotripsy removal and irrigation effects in different surgical needs.

[0080] According to an optional embodiment, referring to Figures 4 and 5, a valve cap 430 is further included. The valve cap 430 is disposed on the valve body 410 and includes a pressing portion 431. The pressing portion 431 is elastic, and an vent 411 is disposed on the pressing portion 431. The valve cap 430 is connected to the valve stem 420. When the pressing portion 431 is pressed by an external force, the pressing portion 431 can undergo elastic deformation to close the vent 411 and allow the valve stem 420 to move.

[0081] When the pressing part 431 is pressed by an external force, its elastic deformation triggers the following two functions: First, the deformation of the pressing part 431 seals the atmospheric port 411, thereby cutting off the connection between the atmosphere and the valve chamber 414; second, the deformation of the pressing part 431 further acts on the valve stem 420, driving the valve stem 420 to move and realize the switching between different air paths within the valve body 410. The pressing part 431 is made of an elastic material, such as silicone, rubber, or other elastic polymers suitable for medical devices. When pressed, the pressing part 431 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 420, achieving precise operation.

[0082] The valve cap 430 is connected to the valve stem 420 by means of snap-fit, thread, adhesive, or integral molding, ensuring that the force of the pressing part 431 can be reliably transmitted to the valve stem 420. When the pressing part 431 deforms, its thrust on the valve stem 420 can be precisely controlled to achieve flexible switching of the valve stem 420 between the closed position and the suction position.

[0083] According to an optional embodiment, referring to Figures 6 and 7, the valve cap 430 and / or valve body 410 include a resilient limiting portion located on the movement path of the valve stem 420, for providing tactile feedback and dynamic switching functionality. When the valve stem 420 is in the suction position, the valve stem 420 contacts the resilient limiting portion.

[0084] When the valve stem 420 is in the suction position, it can deform the elastic limiting part to switch between a first pulse position and a second pulse position. When the valve stem 420 switches between the first and second pulse positions, it can trigger the drive member 300 to switch the blocking member 200 between a first state and a second state. The elastic limiting part provides clear tactile feedback, allowing the user to clearly perceive the current position and functional status of the valve stem 420. The tiered operation of normal suction and pulse suction functions avoids accidental triggering of the pulse component.

[0085] When the valve cap 430 is pressed to position the valve stem 420 in the suction position, the valve stem 420 contacts the elastic limiting part, generating a sense of resistance. This tactile sensation indicates to the user that the position required for normal suction function has been reached, and no further pressure is needed. If a pulse function is required in addition to suction, the user can continue to press the valve cap 430, causing the valve stem 420 to further deform the elastic limiting part, thereby triggering subsequent linkage operations.

[0086] In some designs, referring to Figures 4 and 5, the drive component 300 is configured as an inflatable bladder 210 body, located between the valve cap 430, valve stem 420, and valve body 410, and connected to the shielding component 200. Initially, when the valve cap 430 is pressed, the inflatable bladder 210 body is not fully compressed, only providing a suction function. After the valve stem 420 pushes the elastic limiting part to deform, further pressing the valve cap 430 will compress the inflatable bladder 210 body, thereby inflating the bladder 210 connected to the shielding component 200, triggering the shielding component 200 to switch between a first state and a second state, creating a pulse effect.

[0087] Level 1 Operation (Normal Suction): The user presses the valve cap 430 until the valve stem 420 touches the elastic limit position to provide basic suction function. At this time, the pulse component is not triggered.

[0088] Secondary operation (pulse suction): The user continues to press the valve cap 430, causing the valve stem 420 to push the elastic limit part to deform, triggering the inflation bag 210 to work, further realizing the pulse effect.

[0089] Without increasing operational complexity, the suction valve 400 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 430, avoiding resource waste caused by activating the pulse component when not needed. The linkage design between the deformation of the elastic limit part and the inflation balloon 210 body ensures the accuracy of the switching of the shielding part 200, making the pulse adjustment of the irrigation fluid flow rate more regular and controllable.

[0090] The elastic limiting part 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 can be fixed to the valve body 410 or valve cap 430 by snap-fit, integral, or welding.

[0091] The third aspect of this embodiment describes an endoscope in detail.

[0092] Referring to Figures 8 and 9, an endoscope 10 includes the suction valve 400 described in the above embodiments. This gives the endoscope 10 the beneficial effects of the suction valve 400, which will not be elaborated further here. The suction valve 400 is connected to the return channel 110 of the insertion section, enabling the endoscope 10 to achieve both suction and pulse flushing effects while possessing basic endoscopic functions.

[0093] In this embodiment, the suction valve 400 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 side of the suction valve 400 and a distal section, enabling the suction valve 400 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 400 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 400 and other tubes, ensuring that liquid or material can be aspirated from other tubes.

[0094] 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 400. With this design, the instrument tubes 11 on both sides of the blocking block can be effectively isolated, while the flow channel allows the suction valve 400 to connect with other pipes, thus enabling flexible operation of the suction valve.

[0095] The fourth aspect of this embodiment provides a detailed description of an insertion system.

[0096] Referring to Figures 9 and 10, 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 12, thereby connecting the sheath 20 to the inlet 111. 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 adjustment of the relative position of the sheath 20 and the suction valve 400 according to surgical needs, improving the operational flexibility of the system. The suction valve 400 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.

[0097] 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.

[0098] 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 400 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 400 facilitate rapid removal of lithotripsy, preventing surgical interruption or complications caused by lithotripsy blockage.

Claims

1. A suction valve applied to an endoscope (10) and / or a sheath (20), the endoscope (10) comprising an instrument tube (11), characterized in that, The suction valve includes a valve body (410) and a valve stem (420). The valve body (410) has a valve cavity (414). The valve body (410) is provided with an atmospheric port (411), a sample port (412), and a negative pressure port (413) communicating with the valve cavity (414). The valve stem (420) is movably disposed on the valve body (410) to switch between a closed position and a suction position. When the valve stem (420) is in the closed position, the atmospheric port (411) can be connected to the negative pressure port (413). When the valve stem (420) is in the suction position, the sample port (412) can be connected to the negative pressure port (413). The valve also includes: A connecting part (100), the connecting part (100) being a valve body (410), the connecting part (100) having a channel (110), the channel (110) having an inlet (111) and an outlet (112), the inlet (111) being for communicating with the instrument tube (11) and / or the sheath (20); A shielding member (200) is disposed in the connecting portion (100) and located between the inlet (111) and the outlet (112), the shielding member (200) having a first state and a second state; The outlet (112) is connected to the sample port (412). The driving member (300) is disposed on the valve body (410). When the valve stem (420) is active, the driving member (300) can be triggered to switch the blocking member (200) between the first state and the second state. The blocking state can be periodically changed in the channel (110) by the action of the driving member (300). When the blocking member (200) is in the first state, the channel (110) is fully open; when the blocking member (200) is in the second state, at least a portion of the channel (110) is blocked. The shielding component (200) includes an airbag (210) disposed in the channel (110); the airbag (210) includes at least two bladder units (211) connected to each other; at least two bladder units (211) are arranged along the direction from the inlet (111) to the outlet (112), and from the inlet (111) side to the outlet (112) side, the expansion pressure of the bladder unit (211) gradually decreases or increases to achieve individual expansion or contraction and generate pulse fluctuations.

2. The suction valve according to claim 1, characterized in that, The drive unit (300) is used to inflate or deflate the airbag (210); When the shield (200) is in the first state, the airbag (210) is not inflated so that the channel (110) is fully open; when the shield (200) is in the second state, the airbag (210) is inflated so that at least a portion of the channel (110) is blocked.

3. The suction valve according to claim 2, characterized in that, The airbag (210) is arranged to extend circumferentially along the channel (110).

4. A suction valve according to claim 3, characterized in that, A transition membrane (212) is connected between the capsule unit (211) near the outlet (112) side and the capsule unit (211) near the inlet (111) side, and the transition membrane (212) is located on the capsule unit (211) near the center of the channel (110); And / or, the drive unit (300) includes an inflatable bladder (210) body, the inflatable bladder (210) body being in communication with the airbag (210), when an external force presses the inflatable bladder (210) body, the inflatable bladder (210) body deforms to inflate the airbag (210); when the external force is removed, the inflatable bladder (210) body returns to its original shape, and the gas in the airbag (210) is extracted to the inflatable bladder (210) body.

5. A suction valve according to claim 4, characterized in that, The flow area at the connection between the inflatable bladder (210) and the bladder unit (211) is greater than the flow area at the connection between adjacent bladder units (211).

6. A suction valve according to claim 5, characterized in that, It also includes a valve cap (430), which is disposed on the valve body (410). The valve cap (430) includes a pressing part (431) which is elastic. The vent (411) is disposed on the pressing part (431). The valve cap (430) is connected to the valve stem (420). When the pressing part (431) is pressed by an external force, the pressing part (431) can undergo elastic deformation to close the atmospheric port (411) and move the valve stem (420).

7. A suction valve according to claim 6, characterized in that, The valve cap (430) and / or valve body (410) include an elastic limiting part (432) on the movement path of the valve stem (420). When the valve stem (420) is in the suction position, the valve stem (420) contacts the elastic limiting part (432). When the valve stem (420) is in the suction position, the valve stem (420) can push the elastic limiting part (432) to deform, so as to switch between the first pulse position and the second pulse position; when the valve stem (420) switches between the first pulse position and the second pulse position, it can trigger the driving member (300) to make the blocking member (200) switch between the first state and the second state.

8. An endoscope, characterized in that, Includes the suction valve (400) as described in any one of claims 6-7.

9. An insertion system, characterized in that, It includes a sheath (20) and an endoscope (10) as described in claim 8; 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 (111).

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