Anti-clogging adsorption laser surgical endoscope and method

Abstract

According to the anti-blocking adsorption laser operation endoscope and the method, the anti-blocking adsorption laser operation endoscope is installed at the position far away from an endoscope body and an adsorption opening through an adsorption switch, or the adsorption opening is a plane or a curved surface and comprises a structure of at least two open holes and matched size design. Or an ultrasonic device and an installation mode of the ultrasonic device are adopted, so that the probability that the broken stones block the suction channel is greatly reduced, and blockage is prevented, and meanwhile, the stones are continuously reset at the position of the suction port through a method that the suction switch repeatedly and continuously connects and disconnects the suction port and the suction source; therefore, the continuous laser lithotripsy performance during the operation is kept; through the program control of the suction switch of the anti-blocking adsorption laser operation endoscope, the working intensity of an operation doctor during the operation for controlling an instrument is reduced, so that the operation is more convenient and simpler; through the design of the quick-connection type connector of the anti-blocking broken stone adsorption laser operation endoscope component, instrument sterilization is more convenient, function expansion is more flexible, or independent production is arranged; the invention relates to a method for treating human and animal focuses, especially calculi, by using an anti-clogging laser surgery endoscope catheter.

Description

Technical Field

[0001] The present invention relates to an adsorption laser surgical endoscope and related methods for reducing surgical debris, especially stone blockage. More specifically, the present invention relates to an endoscope with adsorption function and laser surgery, especially lithotripsy, which can simultaneously achieve stone crushing and stone removal for performing laser minimally invasive lithotripsy surgery and methods for the treatment of humans and animals. Background Art

[0002] Stones in humans and animals are a relatively common and recurring disease. Depending on the organ in which the stones form, they can be divided into urinary stones (or urinary stones) and digestive tract stones. Urinary stones are further divided into kidney stones, ureteral stones, and bladder stones based on the site of onset. Gastrointestinal stones commonly include gallbladder stones, bile or common hepatic duct stones, and intrahepatic bile duct stones.

[0003] Common minimally invasive surgical treatments for urinary stones include percutaneous nephrolithotomy, flexible ureteroscopic laser lithotripsy, ureteroscopic lithotripsy, and cystoscopic lithotripsy. These procedures utilize the natural cavities of living organisms for minimally invasive surgical treatment. Currently, flexible ureteroscopic laser lithotripsy is the only technique that utilizes laser energy for lithotripsy. Percutaneous nephrolithotomy is a minimally invasive lithotripsy technique that uses percutaneous transrenal puncture to create an artificial surgical channel. Of course, artificial surgical channels are not limited to those created through percutaneous transbladder puncture in humans or pets.

[0004] During minimally invasive urinary stone surgery, whether artificial or natural, an endoscope is typically used to provide access for surgical instruments, illuminate the surgical field, and flush the lesion with fluid. Energy-based surgical instruments such as laser fibers, ultrasonic rods, and pneumatic rods crush the stones. Fluids flowing from the body back into the body and out again are then carried out of the body by external forces, such as dynamic or intravenous perfusion or vacuum suction, entraining the crushed stones.

[0005] The main pain points of the above-mentioned minimally invasive surgical treatment methods for urinary stones are either the stones jumping when crushing them, or the stones cannot be crushed and cleared out of the body at the same time, and the crushed stones need to be cleaned separately, or only stones of partial composition or hardness can be successfully crushed, and the stone crushing and stone removal can be synchronized during the operation, or they cannot implement complete natural cavity stone crushing like laser fiber, such as ultrasonic energy lithotripsy.

[0006] Minimally invasive surgical treatments for hepatobiliary stones are also gradually being developed. These procedures include duodenoscope-assisted lithotripsy, percutaneous transhepatic biliary lithotripsy, and laparoscopic choledocholithotomy. Compared to urinary stones, minimally invasive surgery for hepatobiliary stones is more complex, demanding, and challenging due to the different organ locations where the stones originate. For example, irrigation water pressure requirements often require intravenous irrigation. Lithotripsy is typically performed using electrohydraulic lithotripsy or mechanical basket extraction. Lasers are rarely used, making them less common than in urinary stone treatment. This is primarily due to the "smoke" generated during laser treatment, which obstructs vision and limits their efficiency. Furthermore, a significant proportion of hepatobiliary stones are muddy and sandy, making intraoperative clearance more challenging. This reduces the efficiency of these procedures. Most gallstones are in the form of mud and sand. Even if the gallbladder-preserving stone removal surgery is successful, the recurrence rate of gallstones is high. Therefore, the current treatment of gallstones mostly involves removing the gallbladder without preserving the gallbladder.

[0007] The hardness or CT value of stones in animals, especially pets, is also relatively high. Currently, minimally invasive laser stone crushing treatments through natural or artificial channels are also being developed.

[0008] The Chinese utility model patent for a direct adsorption surgical endoscope (ZL202120537926.6) and its invention patent for an adsorption laser surgical endoscope (ZL202110278696.4) can absorb stones during laser lithotripsy, simultaneously achieving intraoperative stone adsorption and laser crushing and removal of the broken stones from the body. This improves and overcomes existing urinary laser lithotripsy issues such as stone pulsation, time-consuming and labor-intensive stone removal, thermal damage to tissue caused by heat accumulation during laser emission, and complications caused by renal perfusion fluid reflux due to high pressure. This approach avoids the "smog" produced by laser pulse excitation, ensuring a superior laser lithotripsy surgical field of view, significantly enhancing the laser treatment of hepatobiliary stones. Furthermore, the separate laser lithotripsy instrument and endoscope are integrated into a single device, simplifying and facilitating instrument operation during surgery.

[0009] However, the above-mentioned adsorption laser surgical endoscope is prone to clogging the adsorption channel when crushing stones during surgery. At the same time, in order to obtain a continuous laser lithotripsy effect, the stones adsorbed on the adsorption port need to be repeatedly adjusted to the position of the adsorption port by manually opening and closing the suction switch, which increases the doctor's workload during surgery. Summary of the Invention

[0010] This technical solution greatly reduces the probability of the suction channel being blocked by placing the suction switch (referring to the suction switch that realizes the function of resetting the stone at the suction port position) externally and installing it at a position away from the endoscope body and the suction port, or designing an suction port surface with no less than 2 openings, or using an ultrasonic component installed at a specific position of the suction channel to break up and clear the blockage of blocked stones. The suction switch is automatically controlled by a program, which reduces the intraoperative operation intensity of the doctor using the adsorption laser surgical endoscope. The endoscope is used for clinical treatment of stones in humans and animals. The treatment is not limited to the treatment of stones, but can be extended to soft tissues.

[0011] An embodiment of an anti-clogging adsorption laser surgical endoscope is composed of at least an endoscope body, a suction tube and a suction switch, wherein the endoscope body at least includes a camera and an image transmission channel, an illumination light channel, a flushing channel, an optical fiber channel and a suction channel, the proximal end of the optical fiber channel is designed with an optical fiber interface, the proximal end of the suction channel is designed with a suction source interface for connecting the suction switch, the suction tube and an external suction source, the suction channel has an adsorption port at the front end of the endoscope tube, a part of the opening of the adsorption port is opened on the side of the suction channel and the other part is opened on the end face of the suction channel, or is completely opened on the side of the suction channel, or is completely opened on the end face of the suction channel, its technical feature is that the attraction switch is designed to be installed outside the endoscope body, and the force generated on the stone-breaking fluid in the suction channel of the endoscope body when the attraction switch is continuously turned off and on is parallel to the axial direction of the suction channel.

[0012] The above-mentioned anti-clogging adsorption laser surgical endoscope has the technical feature that the suction switch is either installed on the suction tube of the external suction source, or installed on the suction source external to the suction tube and used together with the suction source, and the opening and closing of the suction switch is realized either manually or by program control.

[0013] An embodiment of an anti-clogging adsorption laser surgical endoscope is composed of at least an endoscope body, a suction tube and a suction switch, wherein the endoscope body at least includes a camera and an image transmission channel, an illumination light channel, a flushing channel, an optical fiber channel and a suction channel, a proximal end of the optical fiber channel is designed with an optical fiber interface, and a proximal end of the suction channel is designed with a suction source interface for connecting the suction switch, the suction tube and an external suction source, and the suction channel has an adsorption port at the front end of the endoscope tube, and its technical feature is that the adsorption port is an adsorption port surface with at least two openings, and the adsorption port surface is either a plane or a curved surface, and the angle of the oblique plane or the size of the curved surface depression is related to the optical fiber digital aperture and the laser window divergence angle, the optical fiber core diameter and the inner diameter of the suction channel, and the opening size is related to the inner diameter of the suction channel, the laser lithotripsy rate and the crushed stone particle size, and the edge position of the adsorption port surface is partly on the side of the suction channel and partly on the end face of the suction channel, or completely on the side of the suction channel, or completely on the end face of the suction channel.

[0014] The above-mentioned anti-clogging adsorption laser surgical endoscope has the technical feature that its adsorption holes have at least one hole for passing a guide wire.

[0015] The anti-clogging adsorption laser surgical endoscope has the technical feature that the endoscope tube is either rigid and inflexible or soft and flexible.

[0016] An embodiment of an anti-clogging adsorption laser surgical endoscope is composed of at least an endoscope body, a suction tube, and a suction switch, wherein the endoscope body at least includes a camera and an image transmission channel, an illumination light channel, a flushing channel, an optical fiber channel and a suction channel, and an ultrasonic component. The proximal end of the optical fiber channel is designed with an optical fiber interface, and the proximal end of the suction channel is designed with a suction source interface for connecting to an external suction source. The suction channel has an adsorption port at the front end of the endoscope tube, and a portion of the adsorption port is opened on the side of the suction channel and another portion is opened on the end face of the suction channel, or is completely opened on the side of the suction channel, or is completely opened on the end face of the suction channel. The suction channel is designed with a suction switch, and the ultrasonic component is connected to an external ultrasonic source. Its technical feature is that an ultrasonic component is installed on the suction channel, and the ultrasonic component is installed on the suction channel after the bifurcation of the optical fiber channel and the suction channel and before the suction switch. The suction channel generates mechanical vibration under the action of ultrasound, which prevents the stones that are blocked in the suction channel from rupturing and realizes the function of clearing the blockage.

[0017] The technical feature of the anti-clogging adsorption laser surgical endoscope described above is that the ultrasonic components are an ultrasonic transducer and a transformer, and there is a conical channel between the suction channel at the installation location of the ultrasonic transformer and the suction channel at the installation location of the suction switch, and the diameter of the suction channel at the suction switch is larger than the diameter of the suction channel at the installation location of the transformer.

[0018] The anti-clogging adsorption laser surgical endoscope has the technical feature that the opening and closing of the attraction switch can be realized manually or by program control.

[0019] The anti-clogging adsorption laser surgical endoscope has the technical feature that the suction channel and the optical fiber channel are either tangent to each other or overlapped.

[0020] The anti-clogging adsorption laser surgical endoscope has the technical feature that the optical fiber channel contained in the endoscope body is designed with an optical fiber delivery button.

[0021] The anti-clogging adsorption laser surgical endoscope has the technical feature that the endoscope body is either an inseparable whole or separate components and is designed with a quick-connect installation structure to enable the components to be assembled into one.

[0022] The above-mentioned method for producing the anti-clogging adsorption laser surgical endoscope is characterized in that the endoscope body and the suction switch are respectively independent components, and each component can be produced independently.

[0023] The method for ensuring continuous laser lithotripsy during the operation of the anti-clogging adsorption laser surgical endoscope is technically characterized in that the suction switch is opened and closed during the laser lithotripsy and this process is continuously repeated, so that the suction port is repeatedly opened and disconnected from the external suction source.

[0024] A method for treating stones with an anti-clogging adsorption laser surgical endoscope has the following technical features: an anti-clogging adsorption laser surgical endoscope is inserted during surgery through a natural cavity of a human or animal, or an artificial surgical channel; the anti-clogging adsorption laser surgical endoscope is externally connected to a video recording host, an illumination light source, an external laser source through a laser optical fiber, an external suction source through a suction source interface, and an external flushing fluid; during surgery, the flushing fluid flows through the endoscope and the lesion where the surgery is performed; the adsorption port is brought close to the stone under the field of view of the endoscope; the suction channel is connected to the suction source and emits a laser; the adsorption port is continuously connected and disconnected from the suction source so that the position of the stone and the adsorption port is reset to obtain a continuous laser lithotripsy effect; the surgical haze generated by the stone crushing and laser excitation is attracted away from the lesion to achieve synchronization of laser lithotripsy and adsorption stone removal. BRIEF DESCRIPTION OF THE DRAWINGS

[0025] Figure 1 : A schematic diagram of an embodiment of an anti-clogging adsorption laser surgical endoscope, wherein the suction tube B schematic diagram is another suction tube including a surgical debris collector.

[0026] Figure 2 : Longitudinal cross-section of the endoscope body.

[0027] Figure 3: Schematic diagram of the structure of the endoscope tube tip: a top view, b side view.

[0028] Figure 4 : Schematic diagram of the cross-section of the adsorption port surface structure.

[0029] Figure 5 : Schematic diagram of the forces generated in the suction channel of the endoscope due to the combined effect of the suction switch being turned off and on and the suction force. Schematic diagram A shows typical turbulence. In Figure B, b1 is the force diagram when the switch is turned off, and b2 is the force diagram when the switch is turned on.

[0030] Figure 6: Schematic diagram of an embodiment of an attraction switch. The figure on the right is a schematic diagram of the process of a programmable attraction switch.

[0031] Figure 7 : An independent attraction switch embodiment.

[0032] Figure 8 : Schematic diagram of the longitudinal section of the endoscope tube tip after the endoscope body is installed with the plug.

[0033] Figure 9: An embodiment of the structural position of the optical fiber channel and the attraction channel.

[0034] Figure 10A : Schematic diagram of the endoscope tube tip with the fiber optic channel endo-suction channel structure, top view on the left and lateral view on the right.

[0035] Figure 10B : Schematic diagram of the longitudinal section of the endoscope tube tip after the laser optical fiber is installed in the endoscope body of the optical fiber channel internal incision suction channel structure.

[0036] Figure 11 : Schematic diagram of the adsorption port surface structure, upper left side view, upper right top view of 3 openings on the adsorption port surface, G-direction schematic diagram of 3 openings on the left and 2 openings on the right of the adsorption port surface.

[0037] Figure 12 : Schematic diagram of the partial structure of the ultrasonic component and its installation position on the suction channel, optical fiber channel, and suction switch.

[0038] Figure 13 : Schematic diagram of the position of the optical fiber application end and the adsorption port after the laser optical fiber is installed in place. This position has a higher laser lithotripsy efficiency and stone clearing effect. DETAILED DESCRIPTION

[0039] The technical solution of the present invention for an anti-clogging adsorption laser surgical endoscope is as follows: Figure 1 As shown, its components are composed of endoscope body 300, suction tube 180 and suction switch 160. The endoscope body is divided into at least endoscope tube 310, handle 320 and image illumination light branching body 334 according to its components. According to its functions, it is divided into at least suction channel 110, surgical optical fiber channel 210 (abbreviated as optical fiber channel), image transmission channel 332, illumination light channel 342, flushing channel (conventional design) Figure 2 (not shown), the above five channels are integrated in the endoscope tube shell 311 to form the endoscope tube component 310. The endoscope tube shell 311 is also a partial shell of the illumination light channel and the suction channel as shown in Figure 3a. The image transmission channel 332 and the illumination light channel 342 are separated at the handle 320 of the endoscope body 300 in this embodiment to form a separate branch body 334 and extend. The branch body is further separated into an image transmission channel and is externally connected to the video host through the image (video recording) host interface 319, and an illumination light channel and an external illumination light source through the illumination light interface 349. The image transmission channel and illumination light channel separated by the above branch bodies are usually designed as flexible tubes and cables. The optical fiber channel, suction channel, and perfusion channel of the endoscope body continue to extend from the endoscope tube component to the proximal end of the endoscope body along the longitudinal direction of the endoscope and are integrated in the handle shell 321 as shown. Figure 1 and 2As shown, a handle 320 is formed. The flushing channel within the endoscope tube 310 is designed with a flushing inlet 519 on the handle 320 of the endoscope body 300. This inlet is connected to an external water infusion pump or irrigation pump for continuous flushing to ensure a clear surgical field of view and to cool the surgical lesion. The outer shell of the endoscope handle 320 is 321, which also facilitates the handling and operation of the anti-clogging adsorption laser surgical endoscope.

[0040] The structural design and composition of the above-mentioned image channel, illumination light channel, and flushing channel are all conventional technologies in the current endoscopy field.

[0041] At the end of the endoscope tube, the suction channel has an adsorption port 11, an optical fiber channel port 21, and a camera 31 for the image transmission channel. The camera design includes viewing angle, field of view, electronic, optical and other technical elements, and displays the surgical image in real time and dynamically on the screen of the image host. The illumination light port 41 provides illumination for the surgical field of view, and the flushing (tip) outlet 51 is as shown. Figure 3A As shown ( Figure 3A for Figure 1 The top view (i.e., the schematic diagram in direction A) is generally divided into two symmetrical outlets, and is positioned as close as possible to the fiber channel laser application end 221 that generates heat during surgery. Figure 3B The optical fiber in the middle serves as an external laser source during surgery and is installed in the fiber channel 210 of the anti-clogging adsorption laser surgical endoscope. The fiber channel opening 21 is located longitudinally between the endoscope camera 41 and the adsorption opening 11. This structural arrangement ensures that the optical fiber application end 221 is installed close to the adsorption opening and allows for real-time observation by the camera during surgery.

[0042] The suction port 11 at the front end of the suction channel can be summarized into three structural modes in this embodiment: Figure 4 As shown, the structure of the adsorption port 11a is that a portion of the opening is opened on the side of the suction channel 110 and adjacent to the optical fiber channel, and another portion of the opening is opened on the front end face of the suction channel; the structure of the adsorption port 11b is that all the openings are opened on the side of the suction channel 110 and adjacent to the optical fiber channel; the structure of the adsorption port 11c is that all the openings are on the front end face of the suction channel. The opening structure of the adsorption ports 11a and 11c enables the anti-clogging adsorption laser surgical endoscope to facilitate entry into human channels such as ureteroscopes with the help of a guide wire when entering the human body; and facilitate entry into human channels such as cystoscopes with the help of an endoscope plug (a conventional accessory of current endoscopes). Considering the convenience of inserting the endoscope tube into the human body and animals through the surgical channel, Figure 4 The tip of the suction channel can be shaped as Figure 4 The shape shown by the dotted line in FIG. 1 is a schematic diagram of a design of an endoscope plug of a matching embodiment. Figure 8 shown. The positional structure between the suction channel 110 and the optical fiber channel 210 on the endoscope tube 310 features a close fit, i.e., a two-channel circumscribed structural design. This allows the optical fiber application end 221 to be closer to the suction port 11, enabling the laser to achieve optimal lithotripsy for the target lesion, such as a calculus. Furthermore, the combined outer diameter of the suction channel and the optical fiber channel is reduced, allowing the suction channel 210 to have sufficient space for efficient stone removal and flushing, ensuring smooth operation. The anti-clogging adsorption laser surgical endoscopes of this embodiment are available in a wide variety of types and specifications. The outer diameter of the scope tube, the inner diameter of the optical fiber channel, and the inner diameter of the suction channel for a ureterorenoscope and a choledochoscope are schematically illustrated in the following table.

[0043] Ureteronephroscopy Choledochoscopy Mirror tube outer diameter (FR) 9 15 Fiber channel outer diameter (mm) 0.75 0.75 Suction channel outer diameter (mm) 1.2 2.2 The above-mentioned suction channel 110 of this embodiment adopts a straight-through structure, that is, it directly extends from the endoscope tube 310 to the proximal handle 320 of the endoscope body 300, and terminates at a conical interface, that is, the suction source interface 159 of the suction channel on the endoscope body. The conical structure of the suction source interface facilitates quick connection with the suction tube 180. This embodiment 180 adopts a silicone hose with an inner diameter size that matches the conical structure of the suction source interface 159 to facilitate quick connection and airtight performance, while also having the performance of the suction channel for transporting broken stones and flushing fluids, such as a smooth inner wall. The design and connection requirements from the adsorption port 11 to the suction tube 180 ensure airtight performance. In this embodiment, the optical fiber channel 210 has an arc angle on the proximal handle 320 of the endoscope body 310 to change the extension direction, such as Figure 2 As shown, there is a space between the fiber channel and the suction channel in the endoscope handle 320. This design ensures that there is space to install the fiber delivery button 260-2 and its fiber delivery and fixing functional component 260-1; secondly, there is a space between the fiber entrance 219 and the suction source interface 159, so that the external optical fiber 280 and the connecting component suction tube 180 do not interfere with each other before and after connection, which is convenient. The structural design of the fiber delivery and its fixing components needs to meet the following functional requirements: first, fiber delivery includes forward and backward, and the delivery method is either continuous movement or step-by-step movement with a specific step length; second, after fiber delivery is realized, the laser fiber 280 is fixed by the fiber delivery and fixing functional component 260-1, ensuring that the fiber 280 (see reference) during the operation and after the installation of the fiber Figure 9) relative to the endoscope body 300, or the optical fiber application end 221 relative to the adsorption opening 11. The forward and backward movement of the optical fiber delivery mechanism 260 not only coordinates the position of the optical fiber application end 221 with the adsorption opening 11 to achieve optimal laser effect, including lithotripsy, but also serves the purpose of intraoperatively damaging or ablating the optical fiber application end 221 due to the interaction between the laser and the lesion, particularly stones, causing it to retract toward the optical fiber opening 21, reducing the effectiveness of the laser on the lesion. The optical fiber delivery mechanism 260 promptly restores the optical fiber application end 221 to its optimal position for laser effect. Fiber delivery and fixation capabilities can be measured using a basic physical quantity: the gripping force on the optical fiber, typically between 0.2 and 0.6 kg, varying depending on the properties of the optical fiber and the material of the protective layer. The structural design of component 260 is a conventional design in this field and will not be described in detail here. Please refer to the patent document Chinese Patent No. ZL202020144961.0 entitled "Fiber Optic Sheath" and U.S. Patent Publication No. US2015 / 0196361A1, and the patent application name is "Apparatus and Method for Fragmenting and Aspirating Materials from a Body Lumen".

[0044] In this embodiment, the suction tube 180 is connected to the suction port 619 of the suction source 600 after passing through the suction switch 160 (specifically, a suction switch that needs to be repeatedly opened and closed during surgery to reset the position of the adsorbed stone relative to the adsorption port. Switches that cut off the suction channel during surgery, such as when interrupting or resuming surgery, are not included in this suction switch). Once this connection is established, due to the airtightness of the suction channel and the suction tube, when the suction switch 160 is open, the suction force of the suction source is transmitted to the adsorption port 11, causing an adsorption effect on the lesion, particularly a stone, to be attracted to the adsorption port. When the suction switch is closed, the adsorption force acting on the adsorption port disappears, and the lesion, such as a stone, may fall from the adsorption port 11 due to gravity, tissue deformation, or flushing. Alternatively, the surgeon may reposition the adsorption port relative to the lesion while the suction switch is closed. When the suction switch 160 is opened again, the relative position of the lesion, such as a stone, to the optical fiber application end 221 is reset. This repositioning of the lesion and the optical fiber application end is very necessary to maintain the continuous effect of the laser during surgery. Taking stones as an example, when the crushed stones are adsorbed by the adsorption port, the laser emitted from the optical fiber application end 221 can efficiently crush the stones, but as the part of the stone facing the optical fiber application end is crushed and peeled off, a gap will be generated between the adsorbed stone and the optical fiber application end. This gap is filled with flushing water, causing the laser emitted by the optical fiber application end to be completely absorbed by the water before it acts on the stone, resulting in the complete disappearance of the laser's stone crushing function, even with the effect of Moses or enhanced pulses (the so-called enhanced pulses are laser pulses for stone crushing that have a very short interval time, such as hundreds of microseconds or milliseconds).

[0045] In order to obtain a continuous force between the laser and the lesion, such as the ability of laser lithotripsy, the suction switch 160 needs to be continuously turned on and off during the operation. Considering that the suction switch is installed on the handle of the endoscope body 300, the combined effect of the turning on and off of the suction switch 160 and the suction force of the suction source is that the fluid and lesion fragments in the suction channel 110, such as broken stones, may be clamped at the moment when the suction switch 160 is turned off, or additional turbulence may be generated for the flushing body, such as water, that is passing due to the mechanical cutting off of the suction tube. Figure 5 As shown by the dotted line and arrow in A (longitudinal cross-sectional diagram). When the suction switch clamps the broken stones, the broken stones will accumulate at the suction switch due to inertia. The irregular edges and corners of the broken stones are likely to cause blockage at the suction switch and in the suction channel 110 extending toward the suction opening. Figure 5The turbulence indicated by the dotted curve and arrows (arrow a1 represents counterclockwise turbulence, or a2 represents clockwise turbulence) in the suction channel, especially the suction channel 110 in the endoscope tube 310, will cause the crushed stones 110a, 110c in the suction channel 110 to tumble, thereby causing blockage of the longer section of the suction channel, especially the inner section of the endoscope tube 310.

[0046] Therefore, the suction switch 160 is quickly connected to the suction channel suction source interface 159 of the endoscope body 300 through the suction tube 180. That is, one of the technical features of the present invention is that the suction switch is designed and installed outside the endoscope body 310 and away from the suction channel of the endoscope body, especially the suction channel of the endoscope tube. Figure 1 As shown, even if the broken stone is clamped at the suction switch 160, since the inner diameter of the suction tube 180 does not have a strict requirement on the inner diameter d1 of the suction channel like the endoscope tube because it needs to enter the human body, its inner diameter will be 3-5 times d1, and no blockage will occur in the suction tube 180. Figure 1 Schematic diagram of the structure of the suction tube 180 in Figure B. A stone or tissue debris collector 182 (a standard product available on the market, which collects surgical debris such as stone fragments, soft tissue fragments, etc.) is installed before the suction switch 160 in the suction tube 180. In this way, the only fluid that is attracted and flows to the suction switch 160 is fluid. The suction switch 160 closes the suction tube 180 more completely because there is no stone fragment to interfere. When the suction switch is turned off, the turbulence a1 or a2 generated in the suction tube where it is located is as shown in FIG. Figure 5 As shown in A, or the combination of the two turbulences, the turbulence characteristics completely disappear when it is conducted in the reverse direction to the endoscope body suction source interface 159, and the force generated on the stone-breaking fluid in the suction channel 110 in the endoscope body 300 is in the direction b1 parallel to the axial direction of the suction channel 110, as shown in FIG. Figure 5 As shown in Figure B, which is the solid line and direction b1, this force only prevents the movement of the broken stones 110a, 110b, and 110c in the suction channel 110 toward the suction source 600, but does not cause the broken stones to tumble, especially the broken stones 110a and 110c, which would otherwise cause blockage in the suction channel. On the contrary, when the suction switch 160 is turned on, the turbulent flow generated at the suction switch has a shorter distance due to the suction force of the suction source, and the suction force b2 transmitted to the endoscope body suction channel 159 is completely parallel to the axis of the suction channel 110, as shown in FIG. Figure 5 As shown in FIG. 1B , the broken stones and the fluid are moved toward the suction source without the broken stones rolling, thereby avoiding or at least greatly reducing the blockage of the broken stones in the suction channel 110 .

[0047] The suction switch 160 of this embodiment is installed on the external suction source 600. The suction switch is also a component of the suction source and is shared with the adsorption laser surgical endoscope. An embodiment of the suction switch 160 adopts a pinch valve, and its structure and working principle are shown in the following figure. Figure 6A As shown in the figure, the pinch valve is indicated at 700. Its pinch groove 701 and squeeze tongue 702 respectively secure the suction tube 180 and close and open the suction source. The suction source 600 is closed and opened by squeezing and releasing the suction tube 160. During this period, the squeeze tongue 702 is not inserted into the suction tube 180. Springs 705 and 703 within the pinch valve body 710 and its fixing 704 enable the squeeze tongue 702 to maintain the closed and open positions and their switching. This suction switch 700 closes and opens the suction tube 180 using electrical or optical signals.

[0048] The pinch valve 700 is Figure 6B The attraction switch on and off program control flow chart shown is implemented Figure 1 At the beginning of the operation, the doctor turns on the "suction channel opening" of the control program of the suction switch 160. At this time, the suction force of the suction source 600 is transmitted to the adsorption port 11. When the doctor further emits the laser, the synchronous suction switch turns on the suction source according to the programmed ton time, and then turns off the suction source according to the toff time, and the cycle continues. Figure 6B The on-off cycle T = ton + toff within the dotted box. The programmable on and off of the attraction switch is synchronized with the laser output, meaning that the laser continues to emit when the attraction switch is on and off, and laser emission also stops when the attraction switch is programmed to stop. When the surgery is completed, the surgeon turns off the attraction source 600 via the attraction switch 160. Figure 6 shows a typical programmable method. The time ton corresponds to the case where a stone is adsorbed to the adsorption port and pulverized by the laser. If the stone detaches from the adsorption port due to factors such as gravity during the toff time, if the stone is re-adsorbed by the adsorption port during the next cycle ton, the position relative to the optical fiber application end 221 changes, maintaining good laser lithotripsy efficiency.

[0049] Figure 7 Figure 6 shows another embodiment of an adsorption laser surgical endoscope. The suction switch 160 is a separate component. Depending on its operation, it can be a programmable suction switch similar to the one shown in Figure 6 or a manual suction switch (i.e., the suction switch 160 is manually turned on and off during surgery by the physician). The term "separate component" means that the suction switch is not a component of the endoscope body 300, nor is it a component of the suction tube 180 or the external suction source 600. It can be manufactured separately and, when connected to or attached to the suction tube 160, enables the intraoperative shutoff and opening function of the adsorption laser surgical endoscope. Of course, airtight performance is also a basic requirement.

[0050] The suction channel 110 and the optical fiber channel 210 in the endoscope tube 310 have different structural positional relationships. Figure 9 As shown, the structural diagram on the left in the figure shows that the two are tangent and the extended line of the tangent line intersects with the adsorption port 11. Figure 9 The optical fiber channel cuts into the suction channel and the extended axis of the optical fiber channel intersects with the adsorption port. Figure 9 The right optical fiber channel is inscribed into the suction channel and the extended axis of the optical fiber channel intersects with the adsorption port. Figure 9 The schematic diagram of the lateral axis of the endoscope tube 310 of the embodiment of the right structural design is as follows Figure 10A As shown in the figure on the right, the front end attempts to Figure 10A As shown in the left picture. Figure 10A The schematic diagram of the axial cross-section of the endoscope tube of the anti-clogging adsorption laser surgical endoscope in the embodiment shown in FIG. Figure 10B As shown, the application end 221 of the optical fiber 280 can be observed by the field of view of the camera 41, ensuring the implementation monitoring of the surgical scene of the optical fiber application end 221 and the safety of the surgery.

[0051] In embodiments of anti-clogging adsorption laser surgical endoscopes, the suction channel, fiber optic channel, and endoscope tube housing 311 are either rigid, such as medical stainless steel, or made of relatively hard polymer materials such as Peek or Pom. Endoscope tubes made of these materials are non-bendable. In some embodiments, the suction channel, fiber optic channel, endoscope tube housing, or flushing channel are flexible, such as polymer materials such as PA, polyurethane, or silicone. Furthermore, the image transmission channel and illumination light channel also utilize flexible fiber optic cables. Endoscope tubes constructed of such flexible materials are bendable during use. This type of bending can be categorized as passive or active, such as passive bending during insertion of a flexible endoscope tube into a surgical cavity, artificial, or natural human or animal cavity. Actively bendable anti-clogging adsorption laser surgical endoscopes include a pull-wire structure. The pull-wire is made of stainless steel, a specially made nickel-titanium wire, or a polymer material, and is distributed along the long axis of the endoscope. The distal end is fixed to the bending section, and the proximal end is connected to a control mechanism on the handle. To ensure that the endoscope tube components maintain their shape during bending and that the tip of the tube can pass through the surgical cavity, the tube may utilize hinged supports, such as a snake-bone design, consisting of multiple annular joints that mechanically link to achieve multi-directional bending. Alternatively, a coil spring or braided mesh, such as a mesh or spiral structure made of stainless steel or nickel-titanium alloy (memory metal), provides axial rigidity and compressive strength while allowing radial bending. The structural designs, components, materials, and processes used to achieve and maintain this bending performance are widely used in today's flexible endoscopes, such as ureteroscopes and choledochoscopes, and are conventional techniques. Therefore, this manual will not describe them in detail.

[0052] The endoscope body 300 of this embodiment comprises at least the aforementioned endoscope tube 310, handle 320, and image and illumination light branching body 334. Functions implemented include illumination of the lesion, viewing direction, and field of view; real-time monitoring of the intraoperative laser effect on the lesion, which is dynamically displayed on the display device of the image host; flushing of the surgical site of the lesion, including continuous flushing to obtain a clear field of view and control temperature; and during surgery, the endoscope tube enters the human body, adsorbs the lesion, and performs laser surgery. The handle is used to control and operate the endoscope body, and simultaneously advance and retract and fix the laser fiber. A laser source is connected externally through the fiber inlet, and the fiber application end is positioned at the adsorbed lesion and the adsorption port through the fiber channel and fiber channel port. The suction tube of the anti-clogging adsorption laser surgery endoscope is quickly connected through the suction source interface; and an external flushing source, such as a hanging water or irrigation pump, is connected through the flushing inlet. The above is the concept and scope of the independent endoscope body 300 of this embodiment of the anti-clogging adsorption laser surgery endoscope.

[0053] The above-mentioned independent endoscope body 300 is basically designed to be inseparable, but it does not exclude the detachability of components such as the flushing inlet 519, and the endoscope body 300 must be a detachable component when including the plug 370.

[0054] The endoscope body of the anti-clogging adsorption laser surgical endoscope embodiment can adopt a combinable structure, which is convenient for combining the common endoscope unit or endoscope barrel on the market with the direct adsorption sheath and its connecting unit to form the endoscope body 300 of the anti-clogging adsorption laser surgical endoscope. The detailed structure and scheme can be found in Chinese invention patent ZL202110278696.4, and the patent name is "Direct Adsorption Laser Surgical Endoscope".

[0055] One embodiment of the adsorption port 11 of the anti-blocking lithotripsy laser catheter is designed as a curved surface that is concave into the suction channel. Figure 11 The surface or plane shown is called the adsorption port surface, which has more than two adsorption holes or openings. The problem to be solved is to ensure that the size of the crushed stone particles that can enter the adsorption channel will not cause blockage in the attraction channel regardless of the installation position of the attraction switch 700 and the cyclic closing and opening operations. At the same time, it is also necessary to achieve the adsorption of stones on the adsorption port 11 and the efficient stone crushing, and further the crushed stones can be cleaned and attracted in time, that is, there is sufficient cleaning ability and stone crushing rate. Figure 11Although the adsorption port surface is a concave curved surface, no matter the adsorption port surface is an inclined surface (the dotted line in the figure shows an inclined adsorption port surface) or a concave surface, its inclined surface angle or curved surface sagging size must satisfy the laser window for the adsorption port surface range or the stones thereon without a dead angle for laser lithotripsy, because stones in the dead angle cannot be effectively crushed by the laser, even if the position of the stone is constantly reset. The above-mentioned adsorption port surface or inclined surface angle, or concave size, is related to the divergence angle of the laser window 221, the optical fiber performance such as digital aperture, core diameter, and the inner diameter of the suction channel. The embodiment of the curved surface design has a better adsorption effect and stone crushing effect for smaller stones or smaller stones than the flat surface design. The adsorption port surface is provided with adsorption holes, Figure 11 The lower left view (direction G) shows an embodiment in which the suction port has three suction holes, such as 11.1, 11.2, and 11.3. The lower right view (direction G) shows an embodiment in which the suction port has two suction holes, 11.1 and 11.2. Each suction hole is at least smaller than the minimum inner diameter of the suction channel 110. The specific dimensions are determined through testing or optimization to ensure that the suction channel is not blocked and that the stone is adequately cleared during lithotripsy. Typical opening diameters are 1 / 2 or 1 / 3 of the inner diameter of the suction channel, but these dimensions are not limited. Furthermore, these dimensions are related to the lithotripsy laser repetition rate (or the number of laser pulses per unit time), laser pulse energy, and laser operating mode, such as pulverization or agglomeration (generally referring to the lithotripsy rate and particle size). Laser parameter settings that favor pulverization are preferred. The key points of designing the suction port surface and the suction hole opening diameter are summarized as follows: the opening size is related to the inner diameter of the suction channel 110, the lithotripsy rate of laser lithotripsy is related to the lithotripsy particle size, and the diameter of one of the openings on the suction port surface must be able to facilitate the passage of the guide wire. Figure 4 As shown, part of the edge of the suction port is on the side of the suction channel and the other part is on the end face of the suction channel, or the edge of the suction port is completely on the side of the suction channel, or the edge of the suction port is completely on the end face of the suction channel.

[0056] One embodiment of the anti-blocking adsorption laser surgical endoscope is to use the ultrasonic wave currently widely used in industry and medicine to assist in breaking or vibrating the stones in the suction channel to achieve the purpose of dredging the blockage or preventing the occurrence of blockage. The ultrasonic wave achieves the above-mentioned anti-blocking function by vibrating parallel and perpendicular to the axis of the suction channel 110. Figure 12As shown in FIG. In an embodiment of the ultrasonic instrument, transducer 901 is a hollow cylinder mounted on horns 902 and 903 tightly mounted in the suction channel. Transducer 901 is connected to ultrasonic source 910 via cable 911 and converts the electrical signal it outputs into ultrasonic waves. The transducer is configured to resonate and convert electrical energy into mechanical vibrations, typically generating ultrasonic waves with a frequency range of 23,000 to 25,000 Hz. Horns 902 and 903 then efficiently couple the ultrasonic waves generated by transducer 901 to the suction channel 110, generating longitudinal and transverse mechanical vibrations of appropriate intensity and amplitude, thereby breaking up the sharp corners of stones that may cause blockage and adjusting the position of the stones. Taking the installation location of the ultrasonic component 900 and the suction switch 700 on the handle 320 of an anti-clogging adsorption laser surgical endoscope as an example, the ultrasonic component 900 is installed after the bifurcation between the optical fiber channel 210 and the suction channel 110 of the endoscope body 300, and the installation point is close to the installation location of the suction switch 700 in the suction channel 110. The amplitude transformers 902 and 903 concentrate the mechanical vibration in the suction channel between the cross section 125 in the figure and the suction port 11. A tapered catheter structure is located between the position where the suction switch slide 751 is inserted into the suction channel 110 and the suction channel cross section 125. This increases the suction channel diameter to prevent further blockage of broken stones in the non-ultrasound area. Unlike the size restrictions of the endoscope tube section, the suction channel section 125 is smaller, because the smaller the minimally invasive channel diameter and the outer diameter of the endoscope tube, the less invasive and more minimally invasive the surgery. Under the action of the attraction switch's deflection block 753, the slider 751 of the attraction switch converts the movement of the switch push rods 761 and 764 parallel to the axis of the attraction channel into movement of the slider 751 perpendicular to the axis of the attraction channel, allowing the slider 751 to enter and exit the channel. Component 752 is designed to ensure that the suction channel 110 remains airtight despite the entry of the slider 751 of the attraction switch 700. Component 752 is typically a sealing ring, and the surface of the slider 751 should be smooth. Component 762 restricts the switch push rods 761 and 764 to movement parallel to the axis of the attraction channel, while component 755 restricts the slider 751 to movement perpendicular to the axis of the attraction channel. When there is no external force applied (i.e., when the attraction switch 700 is closed to the attraction channel, i.e., when the slider 751 is within the attraction channel), these springs are deformed when an external force is applied to the trigger 765. In this embodiment, the ultrasonic device 900 and the attraction switch 700 are both mounted on the handle 320. There are various standard products of ultrasonic transducer 901 and amplitude transformer 902 and 903 on the market for reference, which will not be described in detail in this manual.

[0057] In order to achieve the transmission of ultrasound in the suction channel, the material of the suction channel 110 usually has the performance of efficiently transmitting ultrasound and has a certain hardness to break and crush stones. Medical stainless tubes are usually used. This material is currently widely used in medical endoscopes.

[0058] The anti-clogging adsorption laser surgical endoscope is a complete system and performs its functions, but this system can be disassembled into the endoscope body 300, the suction tube 180, and the suction switch 160. Before use, the suction tube is connected to the endoscope body by a quick-connect method, and the suction switch is quickly connected to the suction tube to form a complete anti-clogging adsorption laser surgical endoscope as a whole and perform its functions. Its detachable and quick-connect design allows the anti-clogging adsorption laser surgical endoscope to be disassembled into independent components after surgery, and each component is sterilized independently to improve sterilization efficiency and facilitate reuse. The endoscope body, suction tube, and suction switch of the anti-clogging adsorption laser surgical endoscope can be produced separately as independent components and then installed as an anti-clogging adsorption laser surgical endoscope when used. These independent components also fall within the scope of protection of the claims of the present invention.

[0059] The endoscope tube of the anti-clogging adsorption laser surgical endoscope needs to enter the human body or animal body during surgery. Different lesions or different surgical methods require installation of some embodiments. Figure 8 The endoscope shown is plugged and then inserted into the body, which increases the smoothness of insertion and reduces insertion damage. Some embodiments require that a guide wire be inserted into the body to the lesion first, and then the suction channel of the anti-clogging adsorption laser surgery endoscope is passed through the guide wire and the anti-clogging adsorption laser surgery endoscope is pushed along the guide wire to the lesion. After the anti-clogging adsorption laser surgery endoscope is pushed to the surgical lesion, before the operation begins, it is necessary to follow Figure 13 The optical fiber is installed at the position of the optical fiber application end 221 shown, and the optical fiber or the optical fiber application end 221 is fixed in position relative to the endoscope by the optical fiber delivery component 260-1. During the operation, the optical fiber application end retracts relative to the adsorption hole due to ablation or damage, and the optical fiber application end can be pushed forward during the operation through the optical fiber delivery button 260. In order to reduce the damage to the surgical cavity in the body or the damage to the optical fiber application end caused by the optical fiber application end 221 when it is inserted into the body, the optical fiber application end can be pushed out from the optical fiber channel port 21 after the anti-blocking adsorption laser surgical endoscope is pushed to the lesion. Figure 13 Position shown.

[0060] Adsorption laser endoscopic treatment of human urinary stones or other urinary lesions is performed by installing a laser optical fiber on an anti-blocking adsorption laser surgical endoscope and connecting it to an external laser source and an external suction source. Intraoperative flushing fluid such as normal saline is connected to the endoscope flushing inlet. An endoscope such as a ureteronephroscope, a cystoscope, etc. is inserted through a natural cavity of the human body such as the urethra, or an endoscope such as a percutaneous nephroscope is inserted through an artificial channel. The adsorption port is placed close to the stone under the field of view of the endoscope, the suction switch is turned on and the laser is emitted. The adsorption port is continuously connected and disconnected from the suction source so that the position of the stone and the adsorption port is reset to obtain a continuous laser lithotripsy effect. The broken stones are attracted away from the lesions to achieve synchronization of laser lithotripsy and adsorption stone removal. The surgical haze generated by laser excitation is attracted and disappears in the suction channel.

[0061] For adsorption laser endoscopic treatment of hepatobiliary stones (digestive tract), a non-blocking adsorption laser surgical endoscope is equipped with a laser fiber and connected to an external laser source and suction source. During surgery, a flushing fluid, such as saline, is connected to the endoscope's flushing port. The non-blocking adsorption laser surgical endoscope, such as a duodenoscope (including a mother-and-child endoscope), is inserted through a surgical channel created by the body's natural cavity and partial organ or tissue incision, or through an artificial channel, such as a percutaneous transhepatic cholangioscope, choledochoscope, or a conventional laparoscope combined with a choledochoscope. Under the endoscopic field of view, the adsorption port is positioned close to the stone, the suction switch is turned on, and the laser is emitted. The adsorption port is continuously connected and disconnected from the suction source, repositioning the stone relative to the adsorption port to achieve a continuous laser lithotripsy effect. The fragmented stone is drawn away from the lesion, achieving simultaneous laser lithotripsy and adsorption stone removal. The surgical haze generated by the laser excitation is drawn away and disappears within the suction channel. Alternatively, for quicksand-like hepatobiliary stones smaller than the adsorption port, direct and continuous aspiration can be performed out of the body.

[0062] In the adsorption laser endoscopic treatment of animal stones, the anti-blocking adsorption laser surgical endoscope is installed with a laser optical fiber and connected to an external laser source and an external suction source. Intraoperative flushing fluid such as saline is connected to the endoscope flushing port, and the endoscope is inserted through the animal's natural cavity or an artificial surgical channel. The adsorption port is placed close to the stone under the field of view of the endoscope, the suction switch is turned on and the laser is emitted. The adsorption port is continuously connected and disconnected from the suction source so that the position of the stone and the adsorption port is reset to obtain a continuous laser lithotripsy effect. The broken stones are attracted away from the lesions to achieve synchronization of laser lithotripsy and adsorption stone removal. The surgical haze generated by laser excitation is attracted and disappears in the suction channel.

Claims

1. An anti-clogging adsorption laser surgical endoscope is composed of at least an endoscope body, a suction tube and a suction switch, wherein the endoscope body at least includes a camera and an image transmission channel, an illumination light channel, a flushing channel, an optical fiber channel and a suction channel, a proximal end of the optical fiber channel is designed with an optical fiber interface, and a proximal end of the suction channel is designed with a suction source interface for connecting the suction switch, the suction tube and an external suction source, and the suction channel has an adsorption port at the front end of the endoscope tube, a part of the opening of the adsorption port is opened on the side of the suction channel and the other part is opened on the end face of the suction channel, or is completely opened on the side of the suction channel, or is completely opened on the end face of the suction channel, and its technical feature is that the attraction switch is designed to be installed outside the endoscope body, and the force generated on the stone-breaking fluid in the suction channel of the endoscope body when the attraction switch is continuously turned off and on is parallel to the axial direction of the suction channel.

2. The anti-clogging adsorption laser surgical endoscope according to claim 1 is technically characterized in that the suction switch is either installed on the suction tube of an external suction source, or installed on the suction source externally connected to the suction tube and used together with the suction source, and the opening and closing of the suction switch is realized either manually or by program control.

3. An anti-clogging adsorption laser surgical endoscope is composed of at least an endoscope body, a suction tube and a suction switch, wherein the endoscope body at least includes a camera and an image transmission channel, an illumination light channel, a flushing channel, an optical fiber channel and a suction channel, a optical fiber interface is designed at the proximal end of the optical fiber channel, a suction source interface is designed at the proximal end of the suction channel for connecting the suction switch, the suction tube and an external suction source, and the suction channel has an adsorption port at the front end of the endoscope tube, and its technical feature is that the adsorption port is an adsorption port surface with at least two openings, and the adsorption port surface is either flat or curved, and the angle of the oblique plane or the size of the curved surface depression is related to the optical fiber digital aperture and the laser window divergence angle, the optical fiber core diameter and the inner diameter of the suction channel, the opening size is related to the inner diameter of the suction channel, the laser lithotripsy rate and the crushed stone particle size, and the edge position of the adsorption port surface is partly on the side of the suction channel and partly on the end face of the suction channel, or completely on the side of the suction channel, or completely on the end face of the suction channel.

4. The anti-clogging adsorption laser surgical endoscope according to claim 3 is technically characterized in that at least one of its adsorption holes is used for passing a guide wire.

5. The anti-clogging adsorption laser surgical endoscope according to claim 1 or 3, wherein the endoscope tube is either rigid and inflexible or flexible and bendable.

6. An anti-clogging adsorption laser surgical endoscope is composed of at least an endoscope body, a suction tube, and a suction switch, wherein the endoscope body at least includes a camera and an image transmission channel, an illumination light channel, a flushing channel, an optical fiber channel and a suction channel, and an ultrasonic component. The proximal end of the optical fiber channel is designed with an optical fiber interface, and the proximal end of the suction channel is designed with a suction source interface for connecting to an external suction source. The suction channel has an adsorption port at the front end of the endoscope tube, and a part of the opening of the adsorption port is opened on the side of the suction channel and the other part is opened on the end face of the suction channel, or is completely opened on the side of the suction channel, or is completely opened on the end face of the suction channel. The suction channel is designed with a suction switch, and the ultrasonic component is connected to an external ultrasonic source. Its technical feature is that an ultrasonic component is installed on the suction channel, and the ultrasonic component is installed on the suction channel after the bifurcation of the optical fiber channel and the suction channel and before the suction switch. The suction channel generates mechanical vibration under the action of ultrasound, which prevents the stones that are blocked in the suction channel from rupturing and realizes the function of clearing the blockage.

7. The anti-clogging adsorption laser surgical endoscope according to claim 6 is technically characterized in that the ultrasonic components are an ultrasonic transducer and a transformer, a conical channel is formed between the suction channel at the ultrasonic transformer installation location and the suction channel at the suction switch installation location, and the suction channel diameter at the suction switch is larger than the suction channel diameter at the transformer installation location.

8. The anti-clogging adsorption laser surgical endoscope according to claim 3 or 6 is technically characterized in that the opening and closing of the attraction switch can be realized manually or by program control.

9. The anti-clogging adsorption laser surgical endoscope according to claim 1, 3, or 6, wherein the suction channel and the optical fiber channel are either tangent to each other or overlapped with each other.

10. The anti-clogging adsorption laser surgical endoscope according to claim 1, 3, or 6, wherein the optical fiber channel contained in the endoscope body is designed with an optical fiber delivery button.

11. The anti-clogging adsorption laser surgical endoscope according to claim 1, 3, or 6 is technically characterized in that the endoscope body is either an inseparable whole or a separate component and is designed with a quick-connect installation structure to enable the components to be assembled into one.

12. A method for producing the anti-clogging adsorption laser surgical endoscope according to claim 1, 3, or 6, characterized in that The endoscope body and the suction switch are each an independent component, and each component may be produced independently.

13. A method for ensuring continuous laser lithotripsy during surgery using an anti-clogging adsorption laser surgical endoscope as described in claim 1, 3, or 6, wherein the method comprises the following technical features: the suction switch is opened and closed during laser lithotripsy and this process is repeated continuously, so that the suction port is repeatedly opened and disconnected from the external suction source.

14. A method for treating stones with an anti-clogging adsorption laser surgical endoscope as described in claim 1, or 3, or 6, the technical feature of which is that an anti-clogging adsorption laser surgical endoscope is inserted during surgery through a natural cavity of a human or animal, or an artificial surgical channel, and the anti-clogging adsorption laser surgical endoscope is externally connected to a video recording host and an illumination light source, and an external laser source is connected through a laser optical fiber, and a suction source interface is externally connected to a suction source, and an external flushing fluid is connected. During surgery, the flushing fluid flows through the endoscope and the lesion where the operation is performed, and the adsorption port is brought close to the stone under the field of view of the endoscope, and the suction channel is connected to the suction source and emits a laser. The adsorption port is continuously connected and disconnected from the suction source so that the position of the stone and the adsorption port is reset to obtain a continuous laser lithotripsy effect, and the surgical haze generated by the stone crushing and laser excitation is attracted away from the lesion to achieve synchronization of laser lithotripsy and adsorption stone removal.

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