Pulse assembly, suction valve, endoscope and implantation system

Abstract

The invention provides a pulse assembly, a suction valve, an endoscope and an implantation system, and relates to the field of medical instruments.The pulse assembly comprises a communication part provided with a channel, the channel is provided with an inlet, a first outlet and a second outlet, and the inlet is used for being communicated with an instrument tube and / or a sheath tube; the shielding piece is movably arranged on the communicating part, and the shielding piece can intermittently block the first outlet under the movable condition; and the driving part is used for driving the shielding part to move, so that the first outlet is intermittently blocked. Compared with the prior art, the device has the advantages that pulse control over the flow speed of washing liquid is achieved, the stone removing efficiency in the operation process is remarkably improved, meanwhile, different operation requirements can be flexibly met, the operation time is effectively shortened finally, and discomfort and risks of a patient are reduced.

Description

Technical Field

[0001] The present invention relates to the technical field of medical devices, and in particular to a pulse component, a suction valve, an endoscope and an insertion system. Background Art

[0002] With the continuous advancement of medical technology, medical endoscopes have become the core tools for diagnosing and treating a variety of diseases such as the digestive system and urinary system, especially in the treatment of stone diseases (such as kidney stones and gallstones). In the lithotripsy of the urinary system, the endoscope enters the renal pelvis through the sheath and uses laser or other energy sources to crush the stones. After lithotripsy, the gap between the endoscope and the sheath usually serves as a reflux channel to help remove the broken stones and flushing fluid, thereby keeping the operation area clean and reducing the occurrence of complications.

[0003] During this process, flushing fluid is injected through the instrument tube and sucked out through the sheath to remove the gravel and keep the field of vision clear. However, due to the complex operation area and narrow space, some gravel is difficult to be effectively removed by the flushing fluid, resulting in longer flushing time to remove. This not only prolongs the operation time, but also increases the risk and discomfort of the patient. Summary of the invention

[0004] In order to solve the above problems, the present application provides a pulse assembly, a suction valve, an endoscope and an insertion system.

[0005] In a first aspect, the present application provides a pulse assembly, which adopts the following technical solution: A pulse assembly is applied to an endoscope and / or a sheath tube, wherein the endoscope includes an instrument tube, comprising: A communication portion, comprising a channel, wherein the channel comprises an inlet, a first outlet, and a second outlet, wherein the inlet is used to communicate with the instrument tube and / or the sheath tube; a shielding member, movably disposed on the connecting portion, wherein the shielding member can intermittently block the first outlet when in motion; and A driving member is used to drive the shielding member to move so that the first outlet is intermittently blocked.

[0006] Preferably, when the first outlet is intermittently blocked, the flow rates of the first outlet when it is opened twice adjacently are different; And / or, the flow area of ​​the first outlet is greater than the flow area of ​​the second outlet.

[0007] Preferably, the shielding member comprises a rotating portion, the rotating portion is slidably matched with the inner wall of the communicating portion, the rotating portion is provided with a communicating hole, and the communicating hole is communicated with the channel; When the rotating part slides relative to the communicating part, the first outlet may be intermittently connected to the communicating hole, and the driving member is used to drive the rotating part to slide relative to the communicating part.

[0008] Preferably, the rotating part is rotatably arranged on the communicating part with the first axis as the rotation center, the number of the communicating holes is at least two, and at least two communicating holes are circumferentially distributed on the rotating part with the first axis as the center, and when the rotating part rotates, the first outlet can be communicated with different communicating holes, and the driving member is used to drive the rotating part to rotate; And / or, the connecting portion is provided with an elastic diaphragm, a buffer space is formed between the elastic diaphragm and the connecting portion, and the elastic diaphragm can be elastically deformed when the pressure at the inlet exceeds a threshold value, thereby increasing or decreasing the internal space of the channel and decreasing or increasing the buffer space at the same time; And / or, the flow areas of adjacent connecting holes are different.

[0009] Preferably, the rotating part has a first position, a second position and a third position, and when the rotating part rotates relative to the connecting part, it can rotate in sequence between the first position, the second position and the third position; When the rotating part is in the first position, the rotating part closes the inlet; When the rotating part rotates between the first position and the second position, the rotating part opens the inlet, and the first outlet is closed by the rotating part; When the rotating portion rotates between the second position and the third position, the rotating portion opens the inlet, and the first outlet is intermittently connected to the communication hole.

[0010] In a second aspect, the present application provides a suction valve, which adopts the following technical solution: A suction valve, comprising a pulse assembly according to the above technical solution, and further comprising a valve cap, wherein the valve cap is arranged on the communication portion, the valve cap comprises a pressing portion, the pressing portion is elastic, the pressing portion is provided with an atmospheric port, and the atmospheric port is communicated with the channel; The driving member is arranged on the connecting portion. When the pressing portion is pressed by an external force, the pressing portion can be elastically deformed to close the air port and trigger the driving member, thereby driving the rotating portion to rotate relative to the connecting portion.

[0011] Preferably, the driving member comprises a valve stem, the valve stem is movably arranged on the communicating portion, one of the rotating portion and the valve stem is provided with a spiral groove, and the other is provided with a protrusion matched with the spiral groove, the valve stem is connected to the pressing portion, and the spiral axis of the spiral groove coincides with the first axis; When the pressing portion is pressed by an external force, the pressing portion may be elastically deformed to close the atmospheric port and move the valve stem along the first axis direction, thereby driving the rotating portion to rotate relative to the communicating portion.

[0012] Preferably, the communication portion is provided with an elastic limiting portion, and the elastic limiting portion is on the moving path of the valve stem, and when the rotating portion is in the second position, the valve stem contacts the elastic limiting portion; When the rotating portion rotates between the second position and the third position, the valve stem can push the elastic limiting portion to undergo elastic deformation.

[0013] In a third aspect, the present application provides an endoscope, which adopts the following technical solution: An endoscope comprises the suction valve described in the above technical solution.

[0014] In a fourth aspect, the present application provides an implantation system, which adopts the following technical solution: An insertion system comprises a sheath tube and the endoscope described in the above technical solution; and also comprises a connecting tube, one end of which is connected to the sheath tube, and the other end of which is connected to the inlet.

[0015] The present invention has the following advantages and beneficial effects: The pulse assembly of the present invention can flexibly adjust the flow area of ​​the liquid flow through the intermittent control of the shielding member, thereby achieving accurate flow rate control and optimizing the flushing effect of the stones. Specifically, when the shielding member is active, it intermittently opens the first outlet, thereby changing the flow area of ​​the fluid through the channel. The second outlet is always kept open to ensure that the liquid can flow stably. On this basis, by controlling the opening and closing of the first outlet, the flow area and flow rate of the liquid can be adjusted.

[0016] When the first outlet is open, the liquid circulation area is the sum of the areas of the first outlet and the second outlet, thereby increasing the flow rate of the liquid. At this time, the flow rate increases, which can effectively drive the stones to flow outward and improve the efficiency of stone removal. On the contrary, when the first outlet is closed, the area of ​​the liquid circulation is only the area of ​​the second outlet, and the flow rate slows down. This design of slowing down the flow rate can form pressure fluctuations in local areas, which helps to loosen or push the stones, making them easier to be flushed out of the body.

[0017] The advantage of this structural design is that by controlling the opening and closing of the first outlet, the liquid flow rate can be adjusted to ensure that the flow rate of the flushing liquid can meet the needs of stone removal and adapt to the flow rate requirements in different surgeries. At high flow rates, the liquid can effectively drive the stone flow and reduce retention; at low flow rates, the liquid can form pressure fluctuations locally, providing better impact force to help crush the stone or push the stone out.

[0018] Furthermore, the intermittent opening of the first outlet by the shielding member causes the flow of the flushing liquid to no longer remain constant, but to present a fluctuating flow. This fluctuating flow not only increases the efficiency of stone removal, but also helps to disperse, impact and discharge the stones. Compared with the design of constant flow rate, this fluctuating flow can effectively reduce the time that stones stay in the surgical area, avoiding the problem that stones cannot be effectively taken away when the flow rate is uniform, thereby improving the efficiency of the operation.

[0019] In addition, the design of the shield allows the flow rate to be flexibly controlled according to different surgical needs. In some surgeries, a faster flow rate may be required to quickly remove the lithotripsy; in other cases, a slower flow rate can ensure that the flushing fluid can fully clean the surgical area and avoid unnecessary impact on surrounding tissues. The shield can achieve this flexible adjustment by adjusting the flow area, ensuring that the flow rate can meet the needs of lithotripsy removal and can adapt to the actual needs during different surgical procedures, thereby improving the safety and efficiency of the surgery and reducing the risks and discomfort of the patient during the operation.

[0020] In summary, the present invention realizes pulse control of the flow rate of the flushing fluid through the design of adjusting the flow rate, which significantly improves the efficiency of stone removal during the operation. At the same time, it can also flexibly adapt to different surgical needs, ultimately effectively shortening the operation time and reducing patient discomfort and risks. BRIEF DESCRIPTION OF THE DRAWINGS

[0021] In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings required for use in the embodiments or the description of the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying creative work.

[0022] Figure 1 It is a schematic diagram of the structure of an embodiment of the present application; Figure 2 is a first schematic diagram of a cross-sectional view of an embodiment of the present application; Figure 3 is a second schematic diagram of a cross-sectional view of an embodiment of the present application; Figure 4 It is a schematic diagram of the explosion structure of an embodiment of the present application; Figure 5 yes Figure 3 A schematic diagram of the enlarged structure of the middle part A; Figure 6 It is a schematic diagram of the structure of an endoscope; Figure 7 It is a partial cross-sectional view of the endoscope; Figure 8 It is a schematic diagram of the structure of the system embedded in the embodiment of the present application.

[0023] The markings in the figure are: 10. Endoscope; 11. Instrument tube; 12. Through port; 20. Sheath; 30. Connecting tube; 100. Connecting portion; 110. Channel; 120. Inlet; 130. First outlet; 140. Second outlet; 150. Elastic limiting portion; 200. Shielding member; 210. Rotating portion; 211. Connecting hole; 220. Elastic diaphragm; 221. Buffer space; 230. Spiral groove; 300. Driving member; 310. Valve stem; 311. Protrusion; 400. Valve cap; 410. Pressing portion; 411. Atmospheric port. DETAILED DESCRIPTION

[0024] To make the purpose, technical solution and advantages of the present invention clearer, the technical solution of the present invention will be described in detail below. Obviously, the described embodiments are only part of the embodiments of the present invention, rather than all the embodiments. Based on the embodiments of the present invention, all other implementation methods obtained by ordinary technicians in this field without creative work belong to the scope of protection of the present invention.

[0025] The terms "first", "second", etc. in the specification and claims of the present application are used to distinguish similar objects, and are not used to describe a specific order or sequence. It should be understood that the data used in this way can be interchangeable under appropriate circumstances, so that the embodiments of the present application can be implemented in an order other than those illustrated or described here, and the objects distinguished by "first", "second", etc. are generally of one type, and the number of objects is not limited. For example, the first object can be one or more. In addition, "and / or" in the specification and claims represents at least one of the connected objects, and the character " / " generally indicates that the objects associated with each other are in an "or" relationship.

[0026] In each embodiment of the present application, "proximal end" and "distal end" refer to the position of each component relative to the user in the use environment, wherein the end closer to the user is designated as the "proximal end" and the end farther from the user is designated as the "distal end".

[0027] In urinary system lithotripsy, especially in percutaneous nephrolithotomy (PCNL), an endoscope is usually inserted into the renal pelvis through a sheath. After the stones are broken up by laser, the flushing fluid and the stones are discharged through the reflux channel formed between the endoscope and the sheath. However, in actual operation, the phenomenon of stone deposition often occurs. These deposited stones may block the operation area, which not only affects the subsequent lithotripsy operation, but also reduces the efficiency of the operation. Therefore, it is usually necessary to remove most of the stones with flushing fluid before continuing the lithotripsy operation.

[0028] The inventors have found that the existing flushing fluid generally maintains a uniform flow rate during flushing. However, when the flow rate of the flushing fluid is constant, its flushing force is often insufficient to effectively remove all stones, especially when the surgical area is complex and the space is narrow. This is because the force exerted on the stones by the liquid with a uniform flow rate is relatively single and stable, and it is difficult to overcome the resistance of the stones due to irregular shapes, rough surfaces or being stuck in tissue folds. In addition, when there are depressions or blind spots in the surgical area, the liquid with a uniform flow rate tends to form stagnant areas in these areas, making it difficult for the stones in these areas to be effectively touched or transported by the flushing fluid. At the same time, the lack of change in flow rate also means that the liquid has insufficient disturbing force on the stones, and cannot destroy the adhesion or friction between the stones and the surrounding tissues, further causing the stones to be retained. These problems make the flushing fluid with a constant flow rate less efficient in removing stones, and it may take longer to flush, thereby increasing the operation time and the patient's discomfort.

[0029] In order to solve the above problems, the present invention provides a shielding design that can dynamically adjust the flow rate of the flushing liquid. The shielding can adjust the flow rate by changing the flow area of ​​the flushing liquid, thereby significantly improving the stone removal effect. When the flow rate is accelerated, the flushing liquid can provide a stronger impact force to help transport the stones; and when the flow rate is slowed down, the pressure fluctuations generated by the flushing liquid in the local area can loosen the embedded stones or change the direction of the stones, making it easier to be taken out. By intermittently changing the flow rate in this way, the retention state of the stones can be effectively destroyed, the stone removal efficiency can be improved, and the operation time can be reduced, and the surgical risks and discomfort of the patients can be reduced. This flow rate adjustment design shows significant advantages in complex surgical environments and provides a more efficient and safe solution for lithotripsy.

[0030] The following is combined with Figures 1 to 8 , a pulse assembly, a suction valve, an endoscope and an insertion system provided by the present application are described in detail through specific embodiments and their application scenarios.

[0031] A first aspect of this embodiment describes a pulse component in detail.

[0032] Reference Figure 6 , Figure 8The embodiment of the present application discloses a pulse component, which is applied to an endoscope 10 and / or a sheath 20 to adjust the flow rate of the flushing fluid, thereby improving the efficiency of lithotripsy and adapting to different surgical requirements.

[0033] Reference Figure 6 , Figure 8 In some embodiments, the endoscope 10 includes a handle and an insertion portion, and an instrument tube 11 is disposed in the insertion portion. The instrument tube 11 is used to inject flushing fluid into the patient's body. During surgical operations, the insertion portion of the endoscope 10 is usually inserted into the sheath 20, thereby forming a reflux channel 110 between the sheath 20 and the insertion portion, and the channel 110 is responsible for discharging the flushing fluid and gravel out of the body. In the prior art, flushing fluid is usually injected and discharged at a constant flow rate, but this stable flow rate may result in some gravel not being effectively removed from the body. In order to solve this problem, the present application provides a technical solution that can periodically adjust the flow rate of the flushing fluid by introducing a pulse component.

[0034] In one embodiment, referring to Figure 7 , Figure 8 , the pulse assembly is arranged on the instrument tube 11. The pulse assembly includes a connecting part 100 and a driving member 300, wherein a shielding member 200 is arranged in the connecting part 100, and the connecting part 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, and the liquid in the instrument tube 11 enters the connecting part 100 through the inlet 120, and then flows out of the connecting part 100 through the first outlet 130 and / or the second outlet 140. The driving member 300 can control the shielding member 200 to intermittently block the first outlet 130. When the shielding member 200 blocks the first outlet 130, the flow area of ​​the flushing liquid is reduced, resulting in an increase in the flow rate; when the shielding member 200 is unblocked, the flow area of ​​the channel 110 is restored and the flow rate is slowed down. This periodic change in flow rate generates intermittent impact force, which helps to loosen the gravel and change its staying position, thereby improving the efficiency of carrying and discharging the gravel.

[0035] Through the above structural design, this solution can overcome the deficiency of limited force of liquid on stones under a single flow rate, especially when stones are embedded in tissue folds or irregular shapes, the effects of high flow rate and periodic pressure fluctuations help to overcome the adhesion and friction between stones and surrounding tissues, making it easier for broken stones to be taken out of the body. In addition, the position and shape of the shielding member 200 and the driving member 300 can be adjusted according to different surgical requirements, so as to adapt to a variety of surgical environments.

[0036] In another embodiment, referring to Figure 6 , Figure 8, the pulse assembly is arranged on the sheath 20, and is connected to the reflux channel 110 between the sheath 20 and the insertion part. The pulse assembly also includes a connecting part 100 and a driving member 300, and a shielding member 200 is arranged in the connecting part 100, which has an inlet 120, a first outlet 130 and a second outlet 140. The flushing liquid 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 shielding member 200 to intermittently block the first outlet 130, thereby changing the flow area of ​​the reflux channel 110. When the shielding member 200 reduces the flow area of ​​the reflux channel 110, a negative pressure is formed in the reflux channel 110, the flow rate increases, and more gravel can be driven to flow outward; when the flow area is restored, the flow rate slows down, but the pressure fluctuation helps to loosen the retained gravel.

[0037] This solution not only enhances the suction effect of the reflux channel 110, but also forms different flow velocity gradients in the reflux channel 110, thereby avoiding the stagnation problem caused by uniform flow velocity. This design is particularly suitable for situations where the surgical area is complex and the space is narrow, and helps to reduce the deposition and retention of gravel.

[0038] In certain embodiments, the pulse assembly can be applied to both the instrument tube 11 and the sheath tube 20. Specifically, a pulse assembly is connected to each of the instrument tube 11 and the sheath tube 20. By adjusting the flow rate changes in the instrument tube 11 and the reflux channel 110, the injection and discharge of the flushing liquid can be adjusted synchronously. For example, when the flow rate in the instrument tube 11 is accelerated, the injection pressure of the flushing liquid can be increased, which helps to loosen the gravel; at the same time, the flow rate in the reflux channel 110 will also be increased synchronously, which is conducive to quickly transporting the gravel out of the body. The coordinated work of the two pulse assemblies not only optimizes the flushing effect, but also can effectively reduce stagnation and improve the efficiency of gravel removal.

[0039] In some embodiments, reference Figure 1 , Figure 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, and the channel 110 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 tube 20. The first outlet 130 and the second outlet 140 are both flushing liquid outflow channels 110.

[0040] The shielding member 200 is movably disposed on the connecting portion 100, and the shielding member 200 can intermittently block the first outlet 130 when it is moving. The driving member 300 is used to drive the shielding member 200 to move so that the first outlet 130 is intermittently blocked. The movement of the shielding member 200 can cause the first outlet 130 to alternate between blocking and unblocking, thereby adjusting the flow rate of the flushing liquid. When the shielding member 200 blocks the first outlet 130, the flow area is reduced, resulting in an increase in the flow rate of the flushing liquid. This increase in flow rate can generate a strong impact force, which helps to effectively drive the stone crushing, especially when the stone is embedded in tissue folds or irregular shapes, the high flow rate can effectively overcome the adhesion between the stone and the tissue, thereby promoting the discharge of the stone crushing.

[0041] On the contrary, when the shielding member 200 releases the blockage of the first outlet 130, the flow area of ​​the channel 110 is restored to its original state, and the flow rate is reduced accordingly. This reduction in flow rate helps to prevent excessive impact of the surrounding tissues caused by the excessive flow of the flushing liquid, and also provides conditions for the loosening and further movement of the gravel. In this way, the flow rate of the flushing liquid produces beneficial fluctuations in each cycle, which can not only effectively remove stones, but also optimize the transportation and discharge effects of gravel at different flow rates.

[0042] The structure and driving mode of the shielding member 200 can be flexibly selected according to the requirements of the actual application, so as to achieve the purpose of controlling the flow rate of the flushing liquid.

[0043] Specifically, the shielding member 200 can be in the form of a valve plate, which is arranged at the first outlet 130. When the driving member 300 adopts an electric device, the valve plate is driven to rotate or move by the electric device, so as to realize the opening and closing control of the first outlet 130. The electric device may include an electric motor, a stepping motor or a servo motor, etc. Through the precise control of the driving member 300, the valve plate can be accurately switched on and off as needed. When the valve plate blocks the first outlet 130, the flow area is reduced, thereby increasing the flow rate of the flushing liquid; and when the valve plate is unblocked, the flow area is restored, thereby slowing down the flow rate. This control method can flexibly adjust the flow rate of the flushing liquid, thereby adjusting the impact force of the stone, which is beneficial to the discharge of gravel and the optimal distribution of the cleaning liquid.

[0044] In addition, the shielding member 200 can also be arranged at the first outlet 130 in the form of an airbag, and the driving member 300 controls the expansion or contraction of the airbag by inflating or deflating the airbag. The expansion of the airbag will cause the first outlet 130 to be blocked, thereby reducing the flow area and increasing the flow rate; the contraction of the airbag will unblock the first outlet 130, thereby restoring the flow area and slowing down the flow rate. This airbag design is relatively simple and easy to control, and due to the elastic characteristics of the airbag, it can better adapt to the working requirements under different pressures, thereby adjusting the flow state of the flushing liquid and helping to optimize the gravel removal effect.

[0045] When the inlet 120 of the connecting part 100 is connected to the instrument tube 11, the pulse assembly can adjust the injection flow rate of the flushing liquid in the instrument tube 11. The adjusted flushing liquid flow rate can form a strong impact during injection according to actual needs, helping to loosen gravel or clean the surgical area.

[0046] When the inlet 120 of the communication part 100 is connected to the sheath tube 20, the pulse assembly can adjust the suction flow rate of the flushing liquid in the reflux channel 110. By increasing the suction flow rate, the ability of the gravel to be discharged outward can be enhanced, especially for large gravel or gravel deposited in complex areas.

[0047] The pulse assembly of the present application can achieve precise adjustment of the flow rate of the flushing fluid, so that it can meet different surgical needs during injection and suction. This design not only helps to loosen and remove the gravel, but also can adapt to the complexity of the surgical area, which is beneficial to reducing the operation time and patient discomfort. In addition, the pulse assembly has a simple structure and strong adaptability, which can improve the overall surgical effect without significantly increasing the complexity of the equipment.

[0048] According to an alternative embodiment, referring to Figure 2 , Figure 3 , when the first outlet 130 is intermittently blocked, the flow rate when the first outlet 130 is opened twice adjacently is different. This design makes the flow rate when the first outlet 130 is opened each time not exactly the same, thereby forming different flow rate fluctuations. Specifically, when it is opened for the first time, the flow rate may be larger; and when it is opened for the second time, the flow rate may be smaller. This differentiated flow rate change helps to adjust the flow rate of the flushing fluid, so that the pressure fluctuations generated during the flushing process can more effectively disperse the stones and prevent the stones from being trapped in a small space or adsorbed on the tube wall.

[0049] In addition, this change in different flow rates may produce a pulse-like effect, that is, the periodic changes in flow rate and flow rate help increase the impact and disturbance effect of the flushing fluid, thereby improving the efficiency of stone removal. This pulse flow is particularly suitable for cleaning stones because the periodic fluctuations can effectively promote the loosening, dispersion and excretion of stones.

[0050] According to an alternative embodiment, referring to Figure 2 , Figure 3, the flow area of ​​the first outlet 130 is greater than the flow area of ​​the second outlet 140. Since the flow area of ​​the first outlet 130 is larger, it can provide a higher flow rate, thereby achieving a larger flow rate and a stronger impact force when the first outlet 130 is opened. By intermittently blocking the first outlet 130, when the first outlet 130 is blocked, the flow rate is temporarily reduced, which helps to control the fluctuations in the flow rate and pressure of the flushing liquid. When the blockage is released, the flow rate increases, forming an impact force to promote the discharge of stones. The larger flow area of ​​the first outlet 130 can provide a more obvious pulse effect under the action of the shielding member 200, thereby improving the overall cleaning effect.

[0051] It should be noted that the so-called "intermittent blocking" means that the first outlet 130 is regularly opened and closed within a certain period. For example, the first outlet 130 is opened for a first time, closed for a second time, and opened again for a third time. Such switching can effectively adjust the flow state of the flushing liquid and generate a pulse effect by using the flow rate change.

[0052] According to an alternative embodiment, referring to Figure 3 , Figure 4 The shielding member 200 includes a rotating portion 210 , which is slidably matched with the inner wall of the connecting portion 100 . The rotating portion 210 is provided with a connecting hole 211 , which is connected with the channel 110 .

[0053] 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. Through this structural design, the flow rate can be flexibly controlled, so that the liquid presents a periodic fluctuation effect when flowing.

[0054] In this embodiment, the sliding mode of the rotating part 210 determines the intermittent connection between the first outlet 130 and the connecting hole 211. Specifically, the rotating part 210 can control the opening and closing state of the connecting hole 211 at different positions through the sliding cooperation with the connecting part 100, thereby adjusting the flow area of ​​the first outlet 130. When the rotating part 210 slides to a certain position, the first outlet 130 is connected with the connecting hole 211, and the liquid can flow out; when the rotating part 210 slides to other positions, the first outlet 130 is blocked, and the flow of the liquid is temporarily blocked.

[0055] The driving member 300 is used to drive the rotating part 210 to slide relative to the connecting part 100, and can realize intermittent blocking and opening of the first outlet 130 as needed. The driving member 300 can be an electric device, a hydraulic device or other suitable driving method. By accurately controlling the sliding of the rotating part 210, the opening and closing frequency and duration of the first outlet 130 are adjusted, thereby realizing the periodic change of the liquid flow rate. This intermittent blocking method can produce a pulse effect, and by periodically changing the flow area, the liquid flow rate fluctuates, thereby improving the flushing effect.

[0056] In specific 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 flow of the liquid, especially when treating stones or other stubborn substances, it can effectively loosen, push and discharge the broken stones. Through reasonable structural design, this embodiment enables the pulse component to flexibly adjust the flow rate and adapt to different surgical requirements, thereby improving the flushing effect and removal efficiency.

[0057] For example, the rotating part 210 may be provided with a plurality of spaced connecting holes 211. When the rotating part 210 slides relative to the connecting part 100, different connecting holes 211 will be gradually or intermittently connected with the first outlet 130, thereby controlling the opening and closing state of the liquid flow. This design can effectively achieve periodic changes in the liquid flow rate, thereby enhancing the flushing effect.

[0058] Specifically, the rotating part 210 is provided with a plurality of interlaced connecting holes 211. When the rotating part 210 slides in the connecting part 100, different connecting holes 211 will be connected with the first outlet 130 in sequence to form a circulation channel 110. When the rotating part 210 slides to a specific position, a certain connecting hole 211 is connected with the first outlet 130, and the liquid can flow out through the channel 110; and when the rotating part 210 slides to another position, another connecting hole 211 is connected with the first outlet 130, or the circulation channel 110 is completely blocked, and the liquid flow is temporarily interrupted. In this way, intermittent fluctuations in the liquid flow can be achieved, producing a pulse-like effect.

[0059] In some embodiments, a connecting portion 100 may be provided on the rotating portion 210, and the connecting hole 211 provided on the rotating portion 210 is intermittently connected to the first outlet 130 by rotating or sliding the rotating portion 210. By adjusting the rotation angle or sliding distance of the rotating portion 210, the opening and closing frequency of the connecting hole 211 can be controlled, thereby adjusting the flow rate of the liquid. Different from the conventional constant flow rate design, this design can generate periodic flow rate fluctuations, which helps to loosen stones or other retained substances and promote their discharge.

[0060] Through this design, the relative sliding and rotation of the rotating part 210 and the connecting part 100 makes the flow process of the flushing liquid present a rhythmic intermittent change, which is beneficial to the adjustment of the flushing effect under different surgical requirements. When a stronger impact force is required, the sliding or rotation of the rotating part 210 can make the multiple connecting holes 211 quickly dock with the first outlet 130, thereby increasing the flow rate; and when a relatively smooth flow is required, the adjustment of the rotating part 210 can reduce the flow rate fluctuation and ensure the uniform flow of the liquid.

[0061] According to an alternative embodiment, referring to Figure 3 , Figure 4 The rotating part 210 is rotatably arranged on the connecting part 100 with the first axis as the center of rotation. The number of connecting holes 211 is at least two, and at least two connecting holes 211 are circumferentially distributed on the rotating part 210 with the first axis as the center. When the rotating part 210 rotates, the first outlet 130 can be connected with different connecting holes 211, and 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 be alternately or intermittently connected with different connecting holes 211, so that the flow area changes with the position of the rotating part 210. This design allows the flow state of the first outlet 130 to be adjusted according to the needs of the operation, to achieve a pulse effect, and to enhance the flushing effect.

[0062] Exemplarily, a bearing or a swivel may be provided between the rotating part 210 and the connecting part 100 to reduce the friction between the rotating part 210 and the connecting part 100. The reduction of friction can improve the durability and response speed of the system, making the rotation smoother and more stable. In addition, a sealing ring may be provided between the rotating part 210 and the connecting part 100 to prevent the flushing liquid from leaking from the gap between the rotating part 210 and the connecting part 100, thereby ensuring the stability and accuracy of the liquid flow. The sealing design helps to ensure that the liquid flows within the predetermined path without being disturbed by the outside world, thereby avoiding pressure loss or waste caused by liquid leakage.

[0063] According to an alternative embodiment, referring to Figure 2 , Figure 3, the connecting part 100 is provided with an elastic diaphragm 220, and a buffer space 221 is formed between the elastic diaphragm 220 and the connecting part 100. The elastic diaphragm 220 can undergo elastic deformation when the pressure at the inlet 120 exceeds a threshold value, thereby increasing or decreasing the internal space of the channel 110, and reducing or increasing the buffer space 221 at the same time. The elastic diaphragm 220 can undergo elastic deformation when the pressure at the inlet 120 exceeds a threshold value, thereby adjusting the size of the internal space of the channel 110, thereby alleviating or compensating for the 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, slow down the flow rate of the liquid, and avoid excessive pressure on the patient's body tissue; and 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 ensure the normal flow of the liquid. Through this design, whether in the application of the instrument tube 11 or the sheath tube 20, it can be ensured that the pressure at the inlet 120 is always maintained within a reasonable range, avoiding discomfort or damage to the patient's body tissue due to improper pressure.

[0064] It is understandable that both the instrument tube 11 and the sheath tube 20 are connected to the patient's body. Therefore, in some special cases, when the flow state of the first outlet 130 is changed, the pressure at the inlet 120 may be too low or too high. Too low or too high pressure will directly affect the pressure fluctuations in the internal space, and the tissues in the patient's body are very fragile and easily damaged by inappropriate pressure. For example, excessive pressure may squeeze the surrounding tissues, causing tissue damage or discomfort; while too low pressure may not provide sufficient impact force, resulting in poor flushing effect and ineffective removal of stones. Therefore, it is crucial to ensure patient safety, avoid tissue damage and improve surgical results by adjusting the pressure of the inlet 120 to keep it within an appropriate range.

[0065] According to an alternative embodiment, referring to Figure 2 , Figure 3 , the flow areas of adjacent communicating holes 211 are different. The communicating holes 211 of different areas help to produce different flow rate changes, thereby enhancing the pulse effect of the flushing liquid and further optimizing the stone removal process. Through the reasonable design of the size of the communicating holes 211, the flow rate change range can be adjusted according to the surgical requirements to ensure that the liquid flow produces appropriate impact force at different stages, which is conducive to the loosening and discharge of stones.

[0066] According to an optional embodiment, the rotating portion 210 has a first position, a second position and a third position. When the rotating portion 210 rotates relative to the connecting portion 100, it can rotate sequentially among the first position, the second position and the third position.

[0067] When the rotating part 210 is in the first position, the rotating part 210 closes the inlet 120. In this state, the flushing liquid cannot flow into the connecting part 100 through the inlet 120, thereby completely cutting off the flow of the liquid. At this time, by controlling the closed state of the inlet 120, the flow of the flushing liquid can be effectively controlled, unnecessary liquid inflow can be avoided, and accurate flow control can be ensured.

[0068] 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. At this time, since the first outlet 130 is closed, the liquid flow is no longer disturbed by the pulse, ensuring a stable and uniform flow. This state can be used for operations that require a stable flow rate, ensuring the continuity of the liquid inflow, and avoiding flow rate fluctuations caused by pulses.

[0069] 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. In this state, by controlling the intermittent connection between the connecting hole 211 and the first outlet 130, the flow of the flushing liquid has a pulse effect. Each time the connecting hole 211 is intermittently connected to the first outlet 130, the liquid flow rate increases rapidly, forming a pulse, thereby generating a periodic impact force. This pulse effect helps to loosen and drive the movement of stones, thereby improving the stone removal effect.

[0070] 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 cleaning effect through intermittent pulses, especially in the lithotripsy process, it can effectively improve the flow effect, thereby optimizing the surgical operation and improving the surgical effect.

[0071] Illustratively, when the rotating portion 210 is in the first position, a partial area of ​​the rotating portion 210 will close the entrance 120 , and when the rotating portion 210 rotates away from the first position, the entrance 120 will not be closed by the rotating portion 210 , thereby achieving opening of the entrance 120 .

[0072] A second aspect of this embodiment describes a suction valve in detail.

[0073] Reference Figure 2 , Figure 3 A suction valve includes a pulse assembly in the above embodiment, and also includes a valve cap 400, the valve cap 400 is arranged on the connecting part 100, the valve cap 400 includes a pressing part 410, the pressing part 410 is elastic, and the pressing part 410 is provided with an atmospheric port 411, and the atmospheric port 411 is connected to the channel 110.

[0074] The driving member 300 is disposed on the connecting portion 100 . When the pressing portion 410 is pressed by an external force, the pressing portion 410 may be elastically deformed to close the air port 411 and trigger the driving member 300 , thereby driving the rotating portion 210 to rotate relative to the connecting portion 100 .

[0075] When the pressing part 410 is pressed by an external force, its elastic deformation can trigger the following two functions: first, the pressing part 410 will close the atmospheric port 411 after deformation, thereby cutting off the connection between the atmosphere and the valve cavity; 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 elastic material, such as silicone, rubber or other elastic polymers suitable for medical devices. When pressed, the pressing part 410 deforms along the set direction. When the deformation reaches a certain degree, it can effectively close the atmospheric port 411 and transmit the force to the valve stem 310 to achieve precise operation.

[0076] Specifically, the suction valve adjusts the flow state through the pulse assembly to achieve pulse suction of the liquid. When the suction valve is closed, the rotating part 210 is in the first position, the inlet 120 is closed, the suction valve is in a closed state, and the second outlet 140 is connected to the negative pressure device. External air enters the channel 110 through the atmospheric port 411 and is discharged through the second outlet 140. At this time, the suction valve is equivalent to being in a closed state and will not suck the liquid in the body.

[0077] 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 air port 411 is closed after the pressing part 410 is deformed, so that the liquid can be drawn out through the inlet 120 and the second outlet 140.

[0078] Furthermore, in order to achieve the pulse effect during the suction process, the rotating part 210 rotates between the second position and the third position, at which time the inlet 120 and the second outlet 140 are always connected, while the first outlet 130 is intermittently closed. In this way, through the regulation of the pulse effect, the liquid flow can be effectively driven to help remove the liquid and debris in the body, especially when cleaning hard-to-move substances, the pulse flow helps to loosen and promote their flow.

[0079] In general, the present invention can achieve precise suction function through reasonable design of structures such as the valve cap 400, the pressing part 410, the atmospheric port 411, the rotating part 210 and the driving member 300, and can produce a pulse effect as needed, effectively optimize the suction process, enhance the treatment effect, and reduce patient discomfort.

[0080] According to an alternative embodiment, referring to Figure 2 , Figure 3The driving member 300 includes a valve stem 310, which is movably arranged 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.

[0081] When the pressing portion 410 is pressed by an external force, the pressing portion 410 may be elastically deformed to close the air port 411 and move the valve stem 310 along the first axis, thereby driving the rotating portion 210 to rotate relative to the connecting portion 100. Through the cooperation between 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 portion 210.

[0082] During operation, the external force of the pressing portion 410 causes the valve stem 310 to move along the first axis. The spiral groove 230 and the protrusion 311 between the valve stem 310 and the rotating portion 210 cooperate to convert the linear motion of the valve stem 310 into the rotation of the rotating portion 210, thereby adjusting the working state of the suction valve.

[0083] In this way, the linear motion of the valve stem 310 can drive the rotating part 210 to rotate and control the switching state of the suction valve. The cooperation of 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 flow of the flushing liquid. In addition, this driving method is consistent with the conventional use operation of the suction valve, that is, the current suction valve realizes suction and non-suction functions by pressing. On the basis of not changing the existing driving method, this solution enables the suction valve to have a pulse suction function on the basis of the suction function. This not only improves the functionality of the suction valve, but also increases its applicability in medical operations, especially when pulse suction is required to achieve better cleaning effects.

[0084] According to an alternative embodiment, referring to Figure 3 , Figure 5 The connecting portion 100 is provided with an elastic limiting portion 150 . The elastic limiting portion 150 is on the moving path of the valve stem 310 . When the rotating portion 210 is in the second position, the valve stem 310 contacts the elastic limiting portion 150 .

[0085] 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. The elastic limiting part 150 provides clear tactile feedback to help the user clearly perceive the current state of the suction valve, thereby achieving graded operation of the normal suction and pulse suction functions and avoiding mis-triggering of the pulse component.

[0086] Specifically, when the normal suction function is needed, the user adjusts the rotating part 210 to between the first position and the second position. When the rotating part 210 rotates to a position close to the second position, the valve stem 310 contacts the elastic limiting part 150 and generates a certain sense of resistance. This tactile sensation prompts the user that the normal suction position has been reached and there is no need to continue pressing hard. When the user needs to enable pulse suction on the basis of the suction function, continue to press the valve cap 400 so that the valve stem 310 pushes the elastic limiting part 150 to further deform, thereby triggering subsequent linkage operations and entering the pulse suction mode. In this way, the elastic limiting part 150 not only provides physical feedback, but also ensures that the user can clearly distinguish between different functional modes, avoid misoperation, and improve the accuracy and comfort of operation.

[0087] Primary operation (normal suction): the user presses the valve cap 400 until the valve stem 310 touches the elastic limiter 150 to provide a basic suction function, and the pulse assembly is not triggered at this time.

[0088] Secondary operation (pulse suction): the user continues to press the valve cap 400, so that the valve stem 310 pushes the elastic limiting portion 150 to deform, triggering the rotating portion 210 to rotate between the second position and the third position, thereby further achieving a pulse effect.

[0089] Without increasing the complexity of the operation, the dual functions of the suction valve (suction and pulse) are realized, meeting the diverse needs in different surgical scenarios. The pulse component is triggered only when the user intentionally continues to press the valve cap 400, avoiding the waste of resources caused by starting the pulse component when it is not needed.

[0090] The elastic limiting part 150 may be made of a material with good elasticity and deformation recovery performance (such as silicone, medical plastic or elastic metal sheet). The elastic limiting part 150 and the valve body or the valve cap 400 may be fixed by snap-fitting, integrated or welding.

[0091] A third aspect of this embodiment provides a detailed description of an endoscope.

[0092] Reference Figure 6 , Figure 7 An endoscope 10 includes the suction valve in the above embodiment. In this way, the endoscope 10 has the beneficial effects of the above suction valve, which will not be described in detail here. The suction valve is connected to the reflux channel 110 of the insertion part, so that the endoscope 10 can achieve the comprehensive effects of suction and pulse flushing through the suction valve while having the basic endoscope function.

[0093] In the present embodiment, the suction valve is connected to the instrument tube 11 of the endoscope 10. The instrument tube 11 is provided with a through-port 12, through which other pipelines can be connected. In this way, the other pipelines can divide the instrument tube 11 into a section on the suction valve side and a section at the distal end, so that the suction valve can suck liquids in other pipelines. Specifically, when it is necessary to use the endoscope 10 to suck substances from the instrument tube 11, the through-port 12 can be closed to ensure that the suction valve is only connected to the instrument tube 11. On the other hand, when it is necessary to suck substances through other pipelines, the through-port 12 can be opened and a connecting component can be inserted to block the instrument tube 11, while the suction valve is connected to other pipelines to ensure that liquids or substances can be sucked from other pipelines.

[0094] To achieve the above switching function, the connecting component can be a blocking block, in which a flow channel is provided, and the flow channel is connected to the instrument tube 11 facing the suction valve side. Through this design, the instrument tubes 11 on both sides of the blocking block can be effectively isolated, and the suction valve is connected to other pipelines through the flow channel, thereby realizing flexible operation of the suction valve.

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

[0096] Reference Figure 6 , Figure 8 , an insertion system, comprising a sheath 20 and the endoscope 10 of the above embodiment; wherein, it also comprises a connecting tube 30, one end of the connecting tube 30 is connected to the sheath 20, and the other end is connected to the port 12, so that the sheath 20 is connected to the inlet 120. After the flushing fluid is injected into the body through the instrument tube 11 of the endoscope 10, it passes through the reflux channel 110 between the sheath 20 and the insertion part, and is discharged through the connecting tube 30 carrying gravel or tissue debris, thereby forming a circulating flushing path. Through the flexible design of the connecting tube 30, the relative position of the sheath 20 and the suction valve can be adjusted according to the surgical requirements, thereby improving the operational flexibility of the system. The suction valve of the endoscope 10 can periodically change the flow rate of the flushing fluid in the connecting tube 30 during the suction process by combining with the pulse component to form a pulse effect.

[0097] The components of the implantation system (sheath 20, endoscope 10, connecting tube 30) can be modularly designed to facilitate 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, the endoscope 10 and the connecting tube 30, simplifies the layout of surgical instruments, and realizes the unification of flushing, suction and lithotripsy. The design of the suction valve and the connecting tube 30 enables the operator to complete multiple operations in a single system without frequent instrument changes, thus reducing intraoperative intervention. With the guiding effect of the connecting tube 30 and the pulse effect of the suction valve, it helps to quickly remove lithotripsy and avoid interruption of surgery or complications caused by lithotripsy blockage.

[0099] The above description is only a specific implementation mode of the present invention, but the protection scope of the present invention is not limited thereto. Any technician familiar with the technical field can easily think of changes or substitutions within the technical scope disclosed by the present invention, which should be covered by the protection scope of the present invention.

Claims

1. A pulse assembly, applied to an endoscope (10) and / or a sheath tube (20), wherein the endoscope (10) comprises an instrument tube (11), characterized in that: include: A communication portion (100) having a channel (110), wherein the channel (110) has an inlet (120), a first outlet (130) and a second outlet (140), wherein the inlet (120) is used to communicate with the instrument tube (11) and / or the sheath tube (20); a shielding member (200) movably disposed on the connecting portion (100), the shielding member (200) being capable of intermittently blocking the first outlet (130) when in motion; and A driving member (300) is used to drive the shielding 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 rates of the first outlet (130) are different when the first outlet (130) is opened twice in succession; And / or, the flow area of ​​the first outlet (130) is greater than the flow area of ​​the second outlet (140).

3. A pulse assembly according to claim 1, characterized in that: The shielding member (200) comprises a rotating portion (210), the rotating portion (210) being slidably matched with the inner wall of the connecting portion (100), the rotating portion (210) being provided with a connecting hole (211), and the connecting hole (211) being connected 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 rotating part (210) is rotatably disposed on the connecting part (100) with the first axis as the center of rotation, the number of the connecting holes (211) is at least two, and the at least two connecting holes (211) are circumferentially distributed on the rotating part (210) with the first axis as the center, and when the rotating part (210) rotates, the first outlet (130) can be connected to different connecting holes (211), and 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), a buffer space (221) is formed between the elastic diaphragm (220) and the connecting portion (100), and the elastic diaphragm (220) can be elastically deformed when the pressure at the inlet (120) exceeds a threshold value, thereby increasing or decreasing the internal space of the channel (110) and decreasing or increasing the buffer space (221); And / or, the flow areas of adjacent communication holes (211) are different.

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

6. A suction valve, characterized in that: A pulse assembly according to claim 5, further comprising a valve cap (400), wherein the valve cap (400) is arranged on the communication portion (100), the valve cap (400) comprises a pressing portion (410), the pressing portion (410) is elastic, the pressing portion (410) is provided with an atmospheric port (411), and the atmospheric port (411) is in communication with the channel (110); The driving member (300) is arranged on the connecting portion (100), and when the pressing portion (410) is pressed by an external force, the pressing portion (410) can undergo elastic deformation, so that the air port (411) is closed and the driving member (300) is triggered, thereby driving the rotating portion (210) to rotate relative to the connecting portion (100).

7. A suction valve according to claim 6, characterized in that: The driving member (300) comprises a valve stem (310), the valve stem (310) being movably arranged on the connecting portion (100), one of the rotating portion (210) and the valve stem (310) being provided with a spiral groove (230), and the other being provided with a protrusion (311) cooperating with the spiral groove (230), the valve stem (310) being connected to the pressing portion (410), and the spiral axis of the spiral groove (230) being coincident with the first axis; When the pressing portion (410) is pressed by an external force, the pressing portion (410) can undergo elastic deformation to close the air port (411) and move the valve stem (310) along the first axial direction, thereby driving the rotating portion (210) to rotate relative to the connecting portion (100).

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

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

10. An implantation system, characterized in that: It comprises a sheath tube (20) and the endoscope (10) according to claim 9; and further comprises a connecting tube (30), one end of the connecting tube (30) being connected to the sheath tube (20), and the other end of the connecting tube (30) being connected to the inlet (120).

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