Endoscopic insertion component and endoscope

Abstract

Provided are an endoscopic insertion component (200) and an endoscope. The endoscopic insertion component (200) comprises: a tube body (210) and a head end seat (220) connected to a distal end of the tube body (210), the head end seat (220) being provided with a first through hole (221) and a second through hole (222) arranged in a proximal-to-distal direction; a first channel tube (231) and a second channel tube (232), the first channel tube (231) and the second channel tube (232) being arranged in the tube body (210), the first channel tube (231) being in communication with the first through hole (221) to form a first working channel, and the second channel tube (232) being in communication with the second through hole (222) to form a second working channel; a laser transmission optical fiber (400) mounted in the second working channel, a distal end of the laser transmission optical fiber (400) being configured to be exposed at a distal end opening of the second working channel so as to output a laser beam to the exterior at the distal end of the second through hole (222); and an imaging element (241) arranged on the head end seat (220) and configured for capturing images of an object located on an outer side of the head end seat (220). The present application mainly solves the technical problem of the inconvenient operation of endoscopes that require the use of laser transmission optical fibers (400).

Description

Endoscope insertion components and endoscope Technical Field

[0001] This application relates to the field of endoscopy technology. Background Technology

[0002] With the rapid development of science and technology and medical techniques, minimally invasive or non-invasive medical examinations and treatments using endoscopes have become widely adopted. For example, in the lithotripsy procedure for kidney stones, the operator can use the flexible tip of a ureteroscope to locate the stone, then insert a laser transmission fiber through the working channel of the endoscope into the kidney to target the stone, and use laser energy to break it up. During the procedure, saline solution is usually infused into the kidney through the working channel of the endoscope, and finally, under the action of a negative pressure suction sheath, the broken stones are suctioned out of the body using the water flow.

[0003] However, in clinical use, traditional ureteroscopes require the laser transmission fiber to be inserted into the kidney through the working channel on the endoscope, which is inconvenient for the operator and increases the operation time. Summary of the Invention

[0004] This application primarily addresses the technical problem of inconvenience in operating endoscopes that require the use of laser transmission optical fibers.

[0005] In one aspect, one embodiment provides an insertion component for an endoscope.

[0006] The insertion components of the endoscope include:

[0007] The tube body is used to connect to the operating handle of the endoscope;

[0008] A head end seat is connected to the distal end of the tube body, and the head end seat is provided with a first through hole and a second through hole arranged in the proximal-distal direction;

[0009] A first channel tube and a second channel tube are disposed inside the tube body; the first channel tube communicates with the first through hole to form a first working channel, and the second channel tube communicates with the second through hole to form a second working channel;

[0010] A laser transmission fiber is installed in the second working channel, and the distal end of the laser transmission fiber is exposed at the distal opening of the second working channel to output laser to the distal outside of the second through hole.

[0011] And an imaging element, which is disposed on the headstock and is used to capture images of objects located outside the headstock.

[0012] Secondly, one implementation provides an endoscope.

[0013] Endoscopes, including:

[0014] The insertion component described in any of the above items;

[0015] The device includes an operating handle connected to the proximal end of the insertion component. The operating handle includes a housing with a first port and a second port. The proximal end of the first channel tube is connected to the first port, and the proximal end of the laser transmission fiber is connected to the second port. The second port is used to connect the laser transmission fiber to the laser device host for introducing laser light into the laser transmission fiber.

[0016] In one embodiment, when the laser transmission fiber is movably positioned along the extension direction of the second working channel, the operating handle includes a fiber optic drive device connected to the housing, the fiber optic drive device comprising:

[0017] A device base, which is fixed to the housing, and a movable chamber is provided inside the device base;

[0018] An optical fiber mounting base is provided for fixing a laser transmission optical fiber whose position is to be adjusted, so as to drive the laser transmission optical fiber to reciprocate; the optical fiber mounting base is disposed in the movable cavity and can move along the reciprocating direction of the laser transmission optical fiber.

[0019] And an operating component, which is rotatably fitted over the device base; a helical transmission structure is provided between the operating component and the optical fiber fixing base, which is used to cause the optical fiber fixing base to move along the reciprocating direction when the operating component rotates.

[0020] The near end of the laser transmission optical fiber is fixedly connected to the optical fiber mounting base.

[0021] The beneficial effects of this application are:

[0022] According to the endoscope insertion component in the above embodiments, the headstock is provided with a first through hole and a second through hole, and the insertion component is provided with a first channel tube communicating with the first through hole to form a first working channel, and a second channel tube communicating with the second through hole to form a second working channel. The first channel tube and the second channel tube can be led through the tube body to the operating handle and connected to the corresponding port on the operating handle to meet different usage requirements; the insertion component also includes a laser transmission fiber installed in the second working channel, realizing the pre-installation of the laser transmission fiber, eliminating the need to insert the laser transmission fiber on-site during clinical use, saving time in inserting the laser transmission fiber into the endoscope on-site, and making operation more convenient. Attached Figure Description

[0023] Figure 1 is a perspective view of an embodiment of the endoscope in this application;

[0024] Figure 2 is a partial enlarged view of the distal end of the inserted component in Figure 1;

[0025] Figure 3 is a schematic diagram of the installation structure of the laser transmission fiber in Figure 2;

[0026] Figure 4 is a schematic diagram of the laser transmission fiber in Figure 2 when it does not extend beyond the head end;

[0027] Figure 5 is a schematic diagram of the connection relationship between the channel tube and the head end seat from one view.

[0028] Figure 6 is a schematic diagram of the connection relationship between the channel tube and the head end seat from another perspective;

[0029] Figure 7 is a schematic diagram of the proximal structure of the headstock;

[0030] Figure 8 is a frontal projection view of the far end of the headstock;

[0031] Figure 9 is a schematic diagram of the fiber optic drive device in Figure 1;

[0032] Figure 10 is a cross-sectional view of Figure 9;

[0033] Figure 11 is an exploded view of Figure 9;

[0034] Figure 12 is a schematic diagram of the assembly relationship between the fiber optic fixing base and the device base in Figure 11;

[0035] Figure 13 is a schematic diagram of the fiber optic mounting base;

[0036] Figure 14 is a structural schematic diagram of the operating component;

[0037] Figure 15 is an exploded view of another embodiment of the fiber optic drive device;

[0038] Figure 16 is a schematic diagram of the assembly relationship between the spiral sleeve, the optical fiber fixing seat and the device base in Figure 15.

[0039] Figure 17 is a perspective view of another embodiment of the endoscope in this application.

[0040] List of feature names corresponding to the labels in the figure:

[0041] 100. Operating handle; 110. Housing; 121. First port; 122. Second port;

[0042] 200. Insert component;

[0043] 210. Pipe body; 211. Bending section; 212. Main body section;

[0044] 220. Head end seat; 221. First through hole; 222. Second through hole; 2221. Distal hole section; 2222. Proximal hole section; 223. Mounting hole; 224. Sealing ring;

[0045] 231. First channel pipe; 232. Second channel pipe;

[0046] 241. Imaging element; 242. Illumination element;

[0047] 300. Fiber optic drive device;

[0048] 310. Device base; 311. Movable chamber; 312. Mounting port; 313. Cavity bottom wall; 3131. Fiber optic perforation; 314. Snap-fit ​​groove; 3151. Housing connection end; 3152. Outer end; 316. Limiting protrusion; 317. Annular groove; 318. Through groove;

[0049] 320. Fiber optic mounting bracket; 321. Base body; 322. Drive pin; 3231. First connecting end; 3232. Second connecting end; 324. Fiber optic ferrule; 325. Connector hole; 326. Indicator scale;

[0050] 330. Operating component; 331. Axial limiting surface; 332. Limiting groove;

[0051] 333, Operating body; 3331, Center hole; 3332, Anti-rotation protrusion; 334, Spiral sleeve; 3341, Anti-rotation groove; 335, Drive groove;

[0052] 340. Damping ring;

[0053] 400, Laser transmission fiber; 410, Inner core; 420, Outer sheath. Detailed Implementation

[0054] The present application will now be described in further detail with reference to the accompanying drawings and specific embodiments. Similar elements in different embodiments are referred to by related similar element reference numerals. In the following embodiments, many details are described to facilitate a better understanding of the present application. However, those skilled in the art will readily recognize that some features may be omitted in different situations, or may be replaced by other elements, materials, or methods. In some cases, certain operations related to the present application are not shown or described in the specification. This is to avoid obscuring the core parts of the present application with excessive description. For those skilled in the art, detailed description of these related operations is not necessary; they can fully understand the related operations based on the description in the specification and general technical knowledge in the art.

[0055] Furthermore, the features, operations, or characteristics described in the specification can be combined in any suitable manner to form various embodiments. At the same time, the steps or actions in the method description can be rearranged or adjusted in a manner obvious to those skilled in the art. Therefore, the various orders in the specification and drawings are only for the clear description of a particular embodiment and do not imply a necessary order, unless otherwise stated that a particular order must be followed.

[0056] The serial numbers assigned to components in this document, such as "first" and "second," are used only to distinguish the described objects and have no sequential or technical meaning. The terms "connection" and "linkage" used in this application, unless otherwise specified, include both direct and indirect connections (linkages).

[0057] In the embodiments of this application, the insertion component of the endoscope is provided with a first working channel and a second working channel. The first working channel can be used to introduce perfusion fluid, and the second working channel can be used to install a laser transmission fiber. It is not necessary to temporarily insert the laser transmission fiber into the endoscope during clinical use, which makes it more convenient to use, simplifies the operator's surgical procedure, and shortens the operation time.

[0058] Meanwhile, the laser transmission fiber does not occupy space in the fluid infusion channel, and will not affect the endoscope's infusion capacity. This helps to ensure the water output at the distal end of the endoscope and improve the efficiency of stone removal during surgery.

[0059] Examples of endoscopes in this application:

[0060] Please refer to Figure 1. In one embodiment, the endoscope includes an operating handle 100 and an insertion component 200 connected to the operating handle 100. The insertion component 200 includes a tube body 210 for connecting to the operating handle 100 of the endoscope, a head end seat 220 connected to the distal end of the tube body 210, and a first channel tube 231 and a second channel tube 232 passing through the tube body 210 (see Figures 5 and 6).

[0061] Those skilled in the art should know that the terms "proximal" and "distal" used in this article are conventional terms in the medical field. For the instrument to be operated, the proximal end is the end closer to the operator, and the distal end is the end farther away from the operator, which is usually the end that enters the patient's body first. The proximal and distal ends can be referred to the orientation shown in the figure.

[0062] Those skilled in the art will understand that the operating handle 100 can be held by the operator to operate the endoscope. In some embodiments, it can be used to adjust the depth of insertion of the tube 210 into the patient, to bend the tube 210, to adjust the imaging parameters, etc., and different ports can be provided to allow cables, optical fibers, pipes, etc. in the tube 210 to be led out to the outside.

[0063] The tube body 210 may include a bending section 211 located at the far end and a main body section 212 connected between the bending section 211 and the operating handle 100. The bending section 211 can enable the head end seat 220 to swing, and the main body section 212 can support and drive the bending section 211 and the head end seat 220.

[0064] Those skilled in the art will understand that, for an endoscope, the insertion component 200 may further include an imaging element 241 and an illumination element 242, which are disposed on the headstock 220. The imaging element 241 is used to image objects located outside the headstock 220, and the illumination element 242 illuminates objects outside the headstock 220 so that the imaging element 241 can image them. As an example, the illumination element 242 may be an LED light.

[0065] In one specific embodiment, referring to Figures 2 to 8, mounting holes 223 for mounting imaging element 241 and illumination element 242 can be provided on the distal end face of the head end seat 220. The imaging element 241 and illumination element 242 can be fixed in the mounting holes 223. The mounting holes 223 for the imaging element 241 and the illumination element 242 can be a single integral hole or separate holes.

[0066] For parts of the operating handle 100 that are not directly related to the improvements in this application, as well as the specific structures of parts such as the tube body 210 and the imaging element 241, reference can be made to existing structures in related technologies, and will not be repeated here. The installation structure of the laser transmission fiber 400 will be introduced first below.

[0067] In some current endoscopes, considering the small diameter of the insertion component 200, only one working channel is often provided. This working channel can extend from the corresponding port on the operating handle 100 to the distal end face of the headstock 220. Through this working channel, liquid can be transported to the outside of the headstock 220 for infusion, and a laser transmission fiber 400 can also be inserted. In the embodiment of this application, the headstock 220 is provided with a first through hole 221 and a second through hole 222 arranged in the proximal-distal direction. A first channel tube 231 disposed in the tube body 210 communicates with the first through hole 221 to form a first working channel. A second channel tube 232 disposed in the tube body 210 communicates with the second through hole 222 to form a second working channel. The laser transmission fiber 400 is installed in the second working channel during the manufacture of the endoscope. The distal end of the laser transmission fiber 400 is exposed at the distal opening of the second working channel to output laser to the distal outside of the second through hole 222.

[0068] It should be noted that the distal end of the laser transmission fiber 400 can be exposed by extending beyond the second working channel, by being flush with the distal opening of the second working channel, or by being retracted into the distal opening of the second working channel, as long as it can output laser light to the distal outer side of the second through hole 222 to satisfy the purpose of laser emission. For example, in some embodiments, the endoscope can be a ureteroscope, in which case the laser transmission fiber 400 only needs to meet the requirement of breaking up stones.

[0069] The shape and position of the first through hole 221 and the second through hole 222 are not limited, as long as they meet the usage requirements. For example, both the first through hole 221 and the second through hole 222 can be circular holes as shown in the figure. In some embodiments, the head end seat 220 has a first side and a second side in a direction perpendicular to the proximal and distal directions of the head end seat 220. Referring to Figure 8, the imaging element 241 is disposed on the first side of the head end seat 220, and the first through hole 221 and the second through hole 222 are disposed on the second side of the head end seat 220. The diameter of the first through hole 221 is larger than that of the second through hole 222, and the first through hole 221 is closer to the center of the head end seat 220 than the second through hole 222. Since the diameter of the laser transmission fiber 400 is relatively small, the arrangement of the first through hole 221 and the second through hole 222 can effectively utilize the radial space on the head end seat 220 and avoid affecting the diameter of the insertion component 200 due to the separate setting of a working channel for installing the laser transmission fiber 400.

[0070] To facilitate the connection between the first channel tube 231 and the first through hole 221, the first through hole 221 can be a stepped hole with a proximal diameter larger than the distal diameter, and the first channel tube 231 can be inserted into the larger diameter position on the proximal side of the first through hole 221. Similarly, the second through hole 222 can also be a stepped hole with a proximal diameter larger than the distal diameter, and the second channel tube 232 can be inserted into the larger diameter position on the proximal side of the second through hole 222.

[0071] In some embodiments, the laser transmission fiber 400 includes an inner core 410 and an outer sheath 420, which ensures the structural strength of the laser transmission fiber 400 and helps to prevent damage when the laser transmission fiber 400 is pushed distally or pulled proximally. The inner core 410 may include an extension extending distally from the outer sheath 420, which helps to avoid interfering with the smooth emission of laser light from the distal end face of the laser transmission fiber 400. In some embodiments, the distal end face of the laser transmission fiber 400 may be a plane perpendicular to the extension direction of the laser transmission fiber 400, which helps to prevent distal damage and penetration into the patient's intracavitary mucosa.

[0072] The laser transmission fiber 400 can be fixedly installed in the second working channel or movably installed in the second working channel. For example, the distal end of the laser transmission fiber 400 can be directly fixed in the second working channel by means of bonding, interference fit, etc. If there is a need for telescopic adjustment of the laser transmission fiber 400, the gap and friction between the laser transmission fiber 400 and the second working channel can be controlled to ensure the movable adjustment of the laser transmission fiber 400.

[0073] Since the insertion component 200 may be in a liquid environment, such as an infusion environment, after being inserted into the patient's body, a sealing structure may be provided between the outer peripheral surface of the laser transmission fiber 400 and the inner wall of the second working channel in some embodiments to prevent liquid leakage from the gap between the laser transmission fiber 400 and the second working channel. When the laser transmission fiber 400 is fixed within the second working channel, the sealing structure can be a sealing ring, sealant, etc. When the laser transmission fiber 400 moves within the second working channel, the sealing structure is a dynamic sealing structure, such as the sealing ring 224 shown in Figure 3. It should be noted that the sealing structure can be located at the position corresponding to the laser transmission fiber 400 and the headstock 220, or it can be located at other positions, such as the position corresponding to the second channel tube 232.

[0074] To achieve the installation of the sealing ring 224, in one specific embodiment, referring to Figure 7, the second through hole 222 is a stepped hole, including a distal hole segment 2221 and a proximal hole segment 2222 arranged sequentially from the distal end to the proximal end. The diameter of the proximal hole segment 2222 is larger than that of the distal hole segment 2221, and an annular step is formed between the distal hole segment 2221 and the proximal hole segment 2222. The second channel tube 232 can be inserted into the proximal hole segment 2222, and the sealing ring 224 is disposed between the annular step here and the distal end face of the second channel tube 232. Since the diameter of the second through hole 222 matches the laser transmission fiber 400, the space is very small. If a sealing ring groove is set on the hole wall of the second through hole 222, it will be difficult to install the sealing ring 224. However, the above structure can easily achieve axial positioning of the sealing ring 224, preventing the sealing ring 224 from coming out of the head end seat 220. The sealing ring 224 is made of elastic material and can elastically abut against the wall of the second through hole 222 and the outer peripheral surface of the laser transmission fiber 400. It maintains the seal by relying on the compression deformation generated by the abutment to prevent liquid from passing through.

[0075] Referring to Figure 1, the operating handle 100 has a first port 121 and a second port 122. The proximal end of the first channel tube 231 is connected to the first port 121, and the proximal end of the laser transmission fiber 400 is connected to the second port 122. The second port 122 is used to connect the laser transmission fiber 400 to the laser equipment host and to guide laser light into the laser transmission fiber 400. Those skilled in the art will understand that the specific form of the first port 121 is not limited, as long as it meets the usage requirements; for example, it can be a Luer connector used to connect to an infusion device. The second port 122 can take any form that enables fiber optic connection.

[0076] When manufacturing endoscopes, the laser transmission fiber optic cable 400 can be pre-installed in the endoscope before use due to the separate second working channel. When in use, the laser transmission fiber optic cable 400 only needs to be connected to the laser equipment host, which can save the time of threading the fiber optic cable on site and improve surgical efficiency.

[0077] In some embodiments, when the laser transmission fiber 400 is fixed in the second working channel, the second port 122 can be a fixed port for the near end of the laser transmission fiber 400 to be fixedly connected, as shown in Figure 17; when the laser transmission fiber 400 is movably disposed in the second working channel, the second port 122 can be a movable port disposed on the fiber drive device 300. In some other embodiments, the fiber drive device 300 can be omitted, and the laser transmission fiber 400 can be manually driven to extend or retract by the operator; or, the fiber drive device 300 can be replaced with other structural forms that can drive the laser transmission fiber 400 to extend or retract. For example, a push button that moves in a straight line can be provided on the housing 110 of the operating handle 100, and the near end of the laser transmission fiber 400 is connected to the push button, and the push button drives the laser transmission fiber 400 to extend or retract.

[0078] The fiber optic drive device 300 will be further described below.

[0079] The fiber optic drive device 300 is connected to the housing 110 of the operating handle 100 for easy operation. Referring to Figures 9 to 11, the fiber optic drive device 300 may include a device base 310, a fiber optic fixing seat 320, and an operating element 330. The device base 310 is fixed to the housing 110, serving as the mounting base for the fiber optic drive device 300. The fiber optic fixing seat 320 provides a fixed connection for the laser transmission fiber 400 whose position needs to be adjusted, thereby driving the laser transmission fiber 400 to reciprocate. The operating element 330 is rotatably fitted over the device base 310. A helical transmission structure is provided between the operating element 330 and the fiber optic fixing seat 320. This helical transmission structure converts the rotation of the operating element 330 into linear motion of the fiber optic fixing seat 320. When the operating element 330 rotates, the fiber optic fixing seat 320 moves along the reciprocating direction, thereby achieving the extension and retraction adjustment of the laser transmission fiber 400, for example, adjusting it to the extended state shown in Figure 2 and the non-extended state shown in Figure 4. The extension and retraction lengths can be determined as needed.

[0080] The following section will describe the specific structure of each component in one embodiment of the fiber optic drive device 300.

[0081] The device base 310 is fixed to the housing 110. The device base 310 can be a cylindrical structure, and its inner cavity forms a movable chamber 311. The movable chamber 311 can be an open chamber with an installation port 312 at one end. In one specific embodiment, as shown in Figures 10 and 11, the movable chamber 311 has an installation port 312 for inserting an optical fiber holder 320 and a bottom wall 313 opposite to the installation port 312. The optical fiber holder 320 can be inserted into and removed from the installation port 312. In some other embodiments, the installation port 312 of the movable chamber 311 can also be a closed structure, for example, by providing a cover to close the installation port 312 of the movable chamber 311.

[0082] The fixing method between the device base 310 and the housing 110 is not limited, such as bonding, snap-fitting, threaded connection, fastener connection, etc. In some embodiments, referring to Figures 9, 10, and 13, a snap-fit ​​groove 314 is provided on the outer peripheral surface of the device base 310. Correspondingly, a limiting protrusion adapted to the snap-fit ​​groove 314 can be provided on the housing 110. The limiting protrusion is embedded in the snap-fit ​​groove 314 to fix the device base 310. The snap-fit ​​groove 314 can be an arc-shaped groove extending along the outer peripheral surface of the device base 310. The number of arc-shaped grooves is not limited, for example, there can be two. The housing 110 can include a first outer shell and a second outer shell that are interlocked with each other. A limiting protrusion can be provided on the first outer shell and the second outer shell respectively. When assembling the endoscope, the first and second housings can clamp the distal end of the device base 310. The limiting protrusions on the inner surfaces of the first and second housings can be embedded in the two arc-shaped grooves on the device base 310, thereby preventing the device base 310 from detaching from the housing 110 and preventing the device base 310 from rotating.

[0083] In some embodiments, the snap-fit ​​groove 314 may be provided at the distal end of the device base 310. After the device base 310 is fixed to the housing 110, the proximal end of the device base 310 forms a protruding portion protruding outside the housing 110, and the operating member 330 may be provided on the protruding portion.

[0084] The device base 310 adopts the above-described assembly structure, which basically does not occupy additional space inside the housing 110. Minor modifications to the existing housing 110 are sufficient to meet the fixing requirements of the device base 310, which helps to save costs.

[0085] After the fiber optic mounting base 320 is installed in the movable chamber 311, it can be positioned by adapting its outer peripheral surface to the inner wall of the movable chamber 311, and can move along the reciprocating direction of the laser transmission fiber 400. Referring to Figures 10 and 11, in some embodiments, the fiber optic mounting base 320 has a first connecting end 3231 and a second connecting end 3232. The first connecting end 3231 and the second connecting end 3232 are located at opposite ends of the fiber optic mounting base 320. The first connecting end 3231 is used for connecting the laser transmission fiber 400, and the second connecting end 3232 is provided with a fiber optic interface for connecting the laser transmission fiber 400 to the laser equipment host, for introducing laser light into the laser transmission fiber 400.

[0086] In one specific embodiment, the fiber optic interface may include a fiber optic ferrule 324 and a connector hole 325. The laser transmission fiber optic cable 400 can be inserted into and fixed in the fiber optic ferrule 324, for example, by adhesive bonding. The connector hole 325 may have internal threads to facilitate connection with a corresponding fiber optic connector. The fiber optic ferrule 324 may adopt conventional structures and materials in the art, and the connector hole 325 may also adopt commonly used specifications in the art to match the appropriate connector.

[0087] The operating element 330 has a mounting hole, through which it is rotatably fitted onto the device base 310. In one specific embodiment, the operating element 330 can be a circular operating knob with a raised and recessed structure on its outer periphery to prevent slippage and facilitate convenient and effective rotation of the operating element 330 by the operator.

[0088] To prevent the operating component 330 from detaching from the device base 310, in one embodiment, referring to Figure 11, the device base 310 has a housing connection end 3151 connected to the housing 110 and an outer end 3152 away from the housing 110. A limiting protrusion 316 is provided on the outer peripheral surface of the outer end 3152 on the device base 310. The mounting hole of the operating component 330 is a stepped hole, forming an axial limiting surface 331. The axial limiting surface 331 and the limiting protrusion 316 form a positioning along the reciprocating movement direction of the laser transmission fiber 400. After the operating component 330 is installed on the device base 310, and the device base 310 is fixed to the housing 110, the operating component 330 can be positioned between the limiting protrusion 316 on the device base and the housing 110 of the operating handle 100.

[0089] In some embodiments, referring to Figure 10, the bottom wall 313 of the movable chamber 311 is provided with an optical fiber through-hole 3131. The optical fiber through-hole 3131 is a stepped hole, including a small diameter section near the movable chamber 311 and a large diameter section away from the movable chamber 311. The large diameter section is used for the second channel tube 232 for inserting the laser transmission optical fiber 400 and fixed connection. The small diameter section is used for the laser transmission optical fiber 400 to pass through and connect with the optical fiber fixing seat 320. The transition part between the large diameter section and the small diameter section forms an annular step. The annular step is used to position the second channel tube 232 axially, which facilitates the laser transmission optical fiber 400 to be led out from the second channel tube 232. It can also easily realize the fixation of the proximal end of the second channel tube 232. The structure is compact and also helps to avoid the proximal end of the laser transmission optical fiber 400 extending too far out of the second channel tube 232 and bending when subjected to thrust.

[0090] In some embodiments, the fiber optic drive device 300 may further include a damping ring 340 (e.g., an O-ring). The damping ring 340 is disposed between the outer periphery of the device base 310 and the operating member 330. The damping ring 340 is used to increase the relative motion damping between the operating member 330 and the device base 310. When operating the operating member 330, the damping ring 340 can provide appropriate friction, improving the operator's feel. Simultaneously, during laser lithotripsy, the laser energy drives the laser transmission fiber 400 to move; the damping ring 340 effectively prevents the laser transmission fiber 400 from shifting axially. The number of damping rings 340 can be two or more, as shown in Figure 10, with two damping rings 340 respectively disposed at both axial ends of the operating member 330. In some embodiments, the damping ring 340 can be positioned on the device base 310 or the operating member 330 along the reciprocating movement direction of the laser transmission fiber 400. To achieve the positioning of the damping ring 340 along the aforementioned reciprocating movement direction, an annular groove 317 can be provided on the outer peripheral surface of the device base 310 or on the wall of the mounting hole of the operating member 330, and the damping ring 340 can be installed in the annular groove 317. In some other embodiments, the damping ring 340 can also be positioned by adhesive bonding or by friction.

[0091] Regarding the helical drive structure, please refer to Figures 10 and 11. In one specific embodiment, the fiber optic mounting base 320 includes a base body 321 and a drive pin 322 connected to the base body 321. The drive pin 322 protrudes from the outer peripheral surface of the base body 321. The device base 310 is provided with a through groove 318 that penetrates the cavity wall of the movable chamber 311, and the drive pin 322 passes through the through groove 318. The number of the through grooves 318 can be one or more, and correspondingly, the number of drive pins 322 can be one or more. Please refer to Figures 11 to 13. The through groove 318 can be a helical groove arranged around the outer peripheral surface of the device base 310. The helical drive structure includes a limiting groove 332 provided on the wall of the mounting hole. The limiting groove 332 extends along the reciprocating movement direction of the laser transmission fiber 400, and the end of the drive pin 322 is inserted into the limiting groove 332 and can move within the limiting groove 332. When installing the fiber optic mounting bracket 320, the bracket body 321 can be installed into the movable chamber 311 first, and then the drive pin 322 can be passed through the through groove 318 and connected to the bracket body 321.

[0092] When the operating component 330 is rotated, the limiting groove 332 can drive the fiber optic fixing seat 320 to rotate through the transmission pin 322. The through groove 318 is a spiral groove, so it can also drive the fiber optic fixing seat 320 to move along the reciprocating direction of the laser transmission fiber 400 through the transmission pin 322. This allows the fiber optic fixing seat 320 to rotate around its own axis while moving along the axial direction of the device base, that is, along the reciprocating direction of the laser transmission fiber 400. The laser transmission fiber 400 can move synchronously with the fiber optic fixing seat 320, controlling whether the laser transmission fiber 400 extends out of the second working channel and the amount of extension.

[0093] In some embodiments, the outer peripheral surface of the fiber optic mounting base 320 may be provided with indicator scales 326 arranged along its axial direction. When pushing the laser transmission fiber 400, the operator can use the indicator scales 326 on the outer peripheral surface of the fiber optic mounting base 320 to determine the length of the distal end face of the laser transmission fiber 400 extending out of the head end seat 220, which helps the operator to operate accurately and avoid the end face of the laser transmission fiber 400 from piercing the patient's tissue. The indicator scales 326 have at least one row on the outer cylindrical surface of the fiber optic mounting base 320. When there are two or more rows of indicator scales 326, each row of indicator scales 326 can be evenly arranged around the circumference of the fiber optic mounting base 320.

[0094] The above structure enables the extension and retraction of the laser transmission fiber 400. However, the laser transmission fiber 400 will also rotate during the extension and retraction movement, which may cause the laser transmission fiber 400 to be damaged under torque.

[0095] To avoid affecting the reliability of the endoscope due to the rotation of the laser transmission fiber 400, another specific embodiment is described in Figures 15 and 16. Unlike the embodiments shown in Figures 11 and 12, in this embodiment, the operating component 330 includes an operating body 333 and a spiral sleeve 334. The operating body 333 has a central hole 3331, and the spiral sleeve 334 is embedded within the central hole 3331. An anti-rotation structure is provided between the wall of the central hole 3331 and the outer peripheral surface of the spiral sleeve 334. Furthermore, the inner cavity of the spiral sleeve 334 forms an assembly hole, and the wall of the assembly hole has a spiral drive groove 335. The drive groove 335 penetrates the wall of the spiral sleeve 334 in a direction perpendicular to the axis of the spiral sleeve 334. The end of the transmission pin 322 is inserted into the drive groove 335 and can move within it. Simultaneously, the through groove 318 on the device base 310 is a straight groove extending along the reciprocating movement direction of the laser transmission fiber 400.

[0096] As shown in Figure 15, the anti-rotation structure between the wall of the central hole 3331 and the outer peripheral surface of the spiral sleeve 334 may include an anti-rotation groove 3341 disposed on the outer peripheral surface of the spiral sleeve 334, and an anti-rotation protrusion 3332 protruding from the inner wall of the central hole 3331. Both the anti-rotation groove 3341 and the anti-rotation protrusion 3332 may extend axially along the spiral sleeve 334. Setting the operating member 330 to include an operating body 333 and a spiral sleeve 334 facilitates the machining of a helical drive groove 335. Of course, in some other embodiments, under suitable machining conditions, the operating body 333 and the spiral sleeve 334 may also be an integral structure; additionally, other forms of anti-rotation structures may be used between the operating body 333 and the spiral sleeve 334, such as adhesive fixing structures, spline structures, key structures, etc.

[0097] When the operating component 330 is rotated, the spiral sleeve 334 rotates synchronously, while the fiber optic mounting base 320 can only move along the rotation axis of the operating component 330 by means of the linear through groove 318 and the transmission pin 322. Therefore, the drive groove 335 on the spiral sleeve 334 will drive the fiber optic mounting base 320 to move only along the reciprocating direction of the laser transmission fiber 400 through the transmission pin 322. The laser transmission fiber 400 can move synchronously with the fiber optic mounting base 320, controlling whether the laser transmission fiber 400 extends out of the second working channel and the amount of extension.

[0098] Overall, this application pre-installs a laser transmission fiber optic cable 400 on the endoscope, which can be used in conjunction with the fiber optic drive device 300. The operator can conveniently and accurately control the extension and retraction of the laser transmission fiber optic cable 400, which helps to simplify the surgical procedure, improve surgical efficiency, reduce medical risks, and enhance the operator's user experience.

[0099] It should be noted that, in some embodiments, those skilled in the art should know that the helical transmission structure can also be replaced with other structural forms. For example, a transmission pin can be provided on the operating component, and a helical groove can be provided on the outer peripheral surface of the optical fiber fixing seat. The transmission pin is inserted into the helical groove on the optical fiber fixing seat and can move in the helical groove. In this case, the transmission pin can also be provided on the near end side of the device base. In addition, the transmission pin and the helical groove can also be replaced with a suitable threaded structure.

[0100] Embodiments of the insertion component of the endoscope in this application:

[0101] The structure of the insertion component of the endoscope is the same as that of the insertion component 200 in the above-described embodiment of the endoscope, and will not be described again here.

[0102] The above examples illustrate this application only to aid understanding and are not intended to limit its scope. Those skilled in the art to which this application pertains can make various simple deductions, modifications, or substitutions based on the ideas presented.

Claims

1. An insertion component for an endoscope, characterized in that, include: The tube body is used to connect to the operating handle of the endoscope; A head end seat is connected to the distal end of the tube body, and the head end seat is provided with a first through hole and a second through hole arranged in the proximal-distal direction; A first channel tube and a second channel tube are disposed inside the tube body; the first channel tube communicates with the first through hole to form a first working channel, and the second channel tube communicates with the second through hole to form a second working channel; A laser transmission fiber is installed in the second working channel, and the distal end of the laser transmission fiber is exposed at the distal opening of the second working channel to output laser to the distal outside of the second through hole. And an imaging element, which is disposed on the headstock and is used to capture images of objects located outside the headstock.

2. The insertion member as claimed in claim 1, characterized in that, A sealing structure is provided between the outer peripheral surface of the laser transmission fiber and the inner wall of the second working channel.

3. The insertion member as claimed in claim 2, characterized in that, The laser transmission fiber is movably arranged along the extension direction of the second working channel, and the sealing structure is a dynamic sealing structure.

4. The insertion member as claimed in claim 3, characterized in that, The dynamic sealing structure is a sealing ring.

5. The insertion member as claimed in claim 4, characterized in that, The second through hole is a stepped hole, comprising a distal hole segment and a proximal hole segment arranged sequentially from the distal end to the proximal end. The diameter of the proximal hole segment is larger than that of the distal hole segment, and an annular step is formed between the distal hole segment and the proximal hole segment. The second channel tube is inserted into the proximal hole segment, and the sealing ring is disposed between the distal end face of the second channel tube and the annular step.

6. The insertion member as claimed in any one of claims 1 to 5, characterized in that, The distal end of the laser transmission fiber is fixed within the second working channel.

7. The insertion member as claimed in any one of claims 1 to 5, characterized in that, The laser transmission fiber includes an inner core and an outer sheath, the inner core including an extension extending from the distal end of the outer sheath.

8. The insertion member as claimed in any one of claims 1 to 5, characterized in that, The distal end face of the laser transmission fiber is a plane perpendicular to the extension direction of the laser transmission fiber.

9. The insertion member as claimed in any one of claims 1 to 5, characterized in that, In a direction perpendicular to the proximal-distal direction of the headstock, the headstock has a first side and a second side, the imaging element is disposed on the first side of the headstock, and the first through hole and the second through hole are disposed on the second side of the headstock; the diameter of the first through hole is larger than that of the second through hole, and the first through hole is closer to the center of the headstock than the second through hole.

10. An endoscope, characterized in that, include: The insertion component as described in any one of claims 1 to 9; The device includes an operating handle connected to the proximal end of the insertion component. The operating handle includes a housing with a first port and a second port. The proximal end of the first channel tube is connected to the first port, and the proximal end of the laser transmission fiber is connected to the second port. The second port is used to connect the laser transmission fiber to the laser device host for introducing laser light into the laser transmission fiber.

11. The endoscope as claimed in claim 10, characterized in that, When the laser transmission fiber is movably positioned along the extension direction of the second working channel, the operating handle includes a fiber optic drive device connected to the housing, the fiber optic drive device comprising: A device base, which is fixed to the housing, and a movable chamber is provided inside the device base; An optical fiber mounting base is provided for fixing a laser transmission optical fiber whose position is to be adjusted, so as to drive the laser transmission optical fiber to reciprocate; the optical fiber mounting base is disposed in the movable cavity and can move along the reciprocating direction of the laser transmission optical fiber. And an operating component, which is rotatably fitted over the device base; a helical transmission structure is provided between the operating component and the optical fiber fixing base, which is used to cause the optical fiber fixing base to move along the reciprocating direction when the operating component rotates. The near end of the laser transmission optical fiber is fixedly connected to the optical fiber mounting base.

12. The operating handle of the endoscope as described in claim 11, characterized in that, The device base has a protruding portion that extends beyond the housing, and the operating element is disposed on the protruding portion.

13. The operating handle of the endoscope as described in claim 11, characterized in that, The device base is provided with a positioning groove on its outer peripheral surface, and the housing is provided with a limiting protrusion that is adapted to the positioning groove. The limiting protrusion is embedded in the positioning groove to fix the device base.

14. The operating handle of the endoscope as described in any one of claims 11 to 13, characterized in that, The fiber optic drive device includes a damping ring disposed between the outer periphery of the device base and the operating member, the damping ring being used to increase the relative motion damping between the operating member and the device base.

15. The operating handle of the endoscope as described in any one of claims 11 to 13, characterized in that, The fiber optic mounting base has a first connecting end and a second connecting end, which are located at opposite ends of the fiber optic mounting base. The first connecting end is for connecting the laser transmission fiber, and the second connecting end is provided with a fiber optic interface. The fiber optic interface is for connecting the laser transmission fiber to the laser device host and for introducing laser into the laser transmission fiber.

16. The operating handle of the endoscope as described in any one of claims 11 to 13, characterized in that, The movable chamber has an installation port for inserting the optical fiber mounting base and a bottom wall opposite to the installation port. The bottom wall of the chamber has an optical fiber perforation, which is a stepped hole, including a small diameter section near the movable chamber and a large diameter section away from the movable chamber. The large diameter section is used for the fixed connection of the channel tube for inserting the laser transmission optical fiber, and the small diameter section is used for the laser transmission optical fiber to pass through and connect to the optical fiber mounting base. The transition between the large diameter section and the small diameter section forms an annular step, which is used to position the channel tube axially.

17. The operating handle of the endoscope as described in any one of claims 11 to 13, characterized in that, The operating component has an assembly hole, through which it is rotatably fitted onto the device base. The fiber optic mounting base includes a base body and a drive pin connected to the base body. The drive pin protrudes from the outer peripheral surface of the base body. The device base has a through groove penetrating the cavity wall of the movable chamber, through which the drive pin passes. The through groove is a spiral groove surrounding the outer peripheral surface of the device base. The spiral drive structure includes a limiting groove on the wall of the assembly hole, extending along the reciprocating direction of the laser transmission fiber. The end of the drive pin is inserted into the limiting groove and can move within it.

18. The operating handle of the endoscope as described in any one of claims 11 to 13, characterized in that, The operating component has an assembly hole, through which it is rotatably fitted onto the device base. The fiber optic mounting base includes a base body and a drive pin connected to the base body. The drive pin protrudes from the outer circumferential surface of the base body. The device base has a through groove penetrating the cavity wall of the movable chamber, through which the drive pin passes. The through groove is a straight groove extending along the reciprocating movement direction of the laser transmission fiber. The wall of the assembly hole has a spiral drive groove, and the end of the drive pin is inserted into the drive groove and can move within it.

19. The operating handle of the endoscope as described in claim 18, characterized in that, The operating component includes an operating body and a spiral sleeve. The operating body has a central hole, and the spiral sleeve is embedded in the central hole. An anti-rotation structure is provided between the hole wall of the central hole and the outer peripheral surface of the spiral sleeve. The inner cavity of the spiral sleeve forms the assembly hole, and the driving groove penetrates the cylinder wall of the spiral sleeve in a direction perpendicular to the axis of the spiral sleeve.

Images