Photocoagulation treatment tip

Abstract

The utility model relates to medical equipment technical field discloses a kind of photocoagulation treatment tips, including laser handle, the left side of the laser handle is provided with laser working tip, the inside integration of the laser working tip has laser fiber coupling connector, the right end of the laser fiber coupling connector is fixedly connected with FC connector, the outer surface of the FC connector is connected with the FC interface of laser handle left end, the left end of the laser working tip is horseshoe shape as a whole, and the end inner wall is foot sole type structure, the outer surface of the upper and lower sides of the horseshoe shape left end of the laser working tip is etched with diamond-shaped antiskid pattern, the device is separated from laser handle design by laser working tip, and laser working tip can be quickly plugged and replaced, laser handle can be reused, cooperate standardization interface, adapt mainstream host computer such as Iridex semiconductor laser and do not need to transform equipment, both avoid the problem of traditional integrated type not reusable, high cost, and solve the problem of poor compatibility of split type interface, high energy loss.

Description

Technical Field

[0001] This utility model relates to the field of medical equipment technology, and more specifically, to photocoagulation therapy tips. Background Technology

[0002] Medical devices refer to instruments, equipment, appliances, in vitro diagnostic reagents and calibrators, materials, and other similar or related items that are used directly or indirectly on the human body, including the necessary computer software. Their core functions are to prevent, diagnose, treat, monitor, and alleviate diseases, and they must meet requirements for safety, effectiveness, and reliability. In the field of ophthalmology, glaucoma, as a group of diseases characterized by optic nerve atrophy and visual field defects, has pathologically elevated intraocular pressure as a major risk factor. Ciliary body photocoagulation therapy devices are core instruments that reduce aqueous humor production by inhibiting ciliary body secretion. It is suitable for refractory glaucoma (such as neovascular glaucoma, traumatic glaucoma, etc.) where intraocular pressure remains at an extremely high level and conventional drug and surgical treatments are ineffective. The photocoagulation treatment equipment currently used in clinical practice usually consists of a laser host, an energy transmission component and a working tip. The working tip is the core execution component that comes into direct contact with the eye. Its principle is to destroy the epithelial cells of the ciliary body with a laser, reduce the production of aqueous humor, and thus lower the intraocular pressure. Existing technology usually uses 400μm or 600μm optical fibers, with the tip of the optical fiber making micro-contact with the sclera. The laser energy passes through the sclera via the optical fiber and acts on the ciliary body.

[0003] Although ciliary body photocoagulation has become an important treatment for refractory glaucoma, current clinical applications of photocoagulation working tips still have certain technical shortcomings. Firstly, positioning accuracy is insufficient. Existing working tips lack standardized positioning structures, relying on the surgeon's experience to measure or visually judge the distance between the fiber and the limbus (which should be maintained at approximately 3mm). In practice, positioning errors often exceed ±1mm, leading to laser energy deviation. Too close a distance can easily cause scleral burns, while too far a distance fails to effectively destroy ciliary body epithelial cells, thus affecting the reduction of aqueous humor. Secondly, energy control is unbalanced. Current working tips transmit the laser directly to the eye through the air. Due to the difference in refractive indices between air and tissue (air refractive index ≈ 1.0, eye tissue refractive index ≈ 1.33), excessively high energy density can easily occur (leading to conjunctival thermal damage). The problems include: (1) damage (or insufficient penetration depth, acting only on the surface tissue), and the inability to achieve uniform energy distribution through micro-beam expansion; (2) poor operational stability, as the contact area between the existing working tip and the sclera is mostly a smooth surface, which is prone to slippage during surgery due to eyelid movement or slight hand tremors, especially in the absence of auxiliary fixation structures. After a single irradiation, the position needs to be readjusted, prolonging the operation time (an average increase of 15-20 minutes), and increasing the risk of excessive tissue damage due to repeated irradiation. In addition, some working tips adopt an integrated design, which makes it impossible to quickly replace sterilization parts, posing a risk of cross-infection. On the other hand, split-design products generally have problems such as poor interface compatibility and high energy conduction loss rate (more than 8%), making it difficult to adapt to mainstream laser hosts (such as Iridex semiconductor lasers). Utility Model Content

[0004] (a) Technical problems to be solved In view of the above situation and to overcome the defects of the prior art, this utility model provides a photocoagulation therapy tip, which aims to solve the problems in the background art.

[0005] (II) Technical Solution To achieve the above objectives, this application provides the following technical solution: a photocoagulation therapy tip, comprising a laser handle, a laser working tip disposed on the left side of the laser handle, a laser fiber optic coupling connector integrated inside the laser working tip, an FC connector fixedly connected to the right end of the laser fiber optic coupling connector, the outer surface of the FC connector engaging with the FC interface at the left end of the laser handle, the left end of the laser working tip being horseshoe-shaped in general, and the inner wall of this end having a foot-shaped structure, the outer surfaces of the upper and lower sides of the horseshoe-shaped left end of the laser working tip being etched with diamond-shaped anti-slip patterns, an annular groove being formed at the lower center of the foot-shaped inner wall of the laser working tip, the light output hole of the laser working tip being located in the central area of ​​the annular groove, and the fiber end of the laser fiber optic coupling connector penetrating to the laser working tip near the light output hole.

[0006] The present invention is further configured such that the laser fiber coupling connector is located 3mm from the horseshoe-shaped edge of the laser working tip and 2mm from the side.

[0007] The present invention is further configured such that the diameter of the annular groove is 2mm and the depth is 0.5mm.

[0008] The present invention is further configured such that the distance between the fiber end face of the laser fiber coupling connector and the contact surface of the laser working tip horseshoe is 0.5mm, and the distance between the fiber end face of the laser fiber coupling connector and the bottom surface of the annular groove is 0.3mm.

[0009] The present invention is further configured such that the optical fiber of the laser fiber coupling connector is 600μm, and the distance between the working end face of the optical fiber of the laser fiber coupling connector and the plane of the laser working tip exit hole is 0.5mm.

[0010] The present invention is further configured such that the interior of the annular groove can be filled with a high refractive index coupling agent, and the refractive index of the high refractive index coupling agent needs to be ≥1.45.

[0011] The present invention is further configured such that the laser working tip is made of medical-grade silicone with a Shore hardness of 50A, and the FC connector is made of metal.

[0012] (III) Beneficial Effects Compared with the prior art, the beneficial effects of this utility model are: 1. The separate design of the laser working tip and the laser handpiece enables quick insertion and removal of the laser working tip. The laser handpiece is reusable, requiring only a single replacement of the low-cost laser working tip, costing less than 500 yuan, which is 5%-10% of the cost of traditional integrated solutions. Combined with the standardized interface design, it is compatible with mainstream laser hosts, such as Iridex semiconductor lasers, without the need to modify existing equipment. It also avoids the problems of non-reusability of traditional integrated working tips and a single cost of nearly 10,000 yuan, significantly reducing the cost of surgical consumables. At the same time, it solves the problems of poor interface compatibility and high energy conduction loss that are common in split designs, ensuring stable laser energy conduction. 2. The horseshoe-shaped positioning structure allows for intuitive positioning with the horseshoe edge as the reference point. Surgeons do not need to use a ruler to measure; they can directly align the horseshoe edge with the limbus to ensure that the laser fiber maintains a fixed distance from the target area with a positioning accuracy of ±0.3mm. Combined with the foot-shaped inner wall angle fixing function, it avoids the problems of traditional working tips relying on surgeon experience for positioning and laser energy deviation caused by errors exceeding ±1mm. It prevents scleral burns caused by being too close and avoids situations where the ciliary body epithelial cells cannot be effectively destroyed due to being too far away. At the same time, it eliminates differences in surgeon experience, achieves standardized operation, and shortens the operation time. 3. By combining the annular groove with a high-refractive-index coupling agent, and with the double gaps of 0.3mm between the fiber end face of the laser fiber coupling connector and the bottom surface of the annular groove, and 0.5mm between the fiber end face and the horseshoe contact surface of the laser working tip, a plano-concave lens effect can be formed in the annular groove. This increases the divergence angle of the laser emission by 10%-15% and the penetration depth by 0.1-0.3mm, optimizing the laser energy distribution. The Gaussian distribution has a higher peak value at the center and faster attenuation at the edges. Furthermore, by combining this with the energy conduction characteristics of 600μm optical fiber, the problem of excessively high energy density or insufficient penetration depth caused by air conduction and refractive index differences in traditional working tip lasers is avoided. This reduces the risk of scleral surface burns and improves the efficiency of ciliary body destruction, achieving energy control balance. 4. The diamond-shaped anti-slip pattern on the surface of the medical-grade silicone laser tip, combined with the coupling agent filled in the annular groove, increases the friction between the laser tip and the sclera by ≥200%. At the same time, the horseshoe-shaped structure of the silicone material can naturally open the eyelid, avoiding the problems of the smooth surface of the traditional laser tip and its tendency to slip due to eyelid movement or hand tremors. This reduces the number of adjustments during the operation, eliminating the need for frequent adjustments to the position of the conjunctiva and eyelid. It avoids prolonging the operation time, shortening it by an average of more than 30%, and reduces the risk of excessive tissue damage caused by repeated irradiation. It also eliminates the interference of eyelid obstruction on the surgical field of vision, improving the stability of the operation. 5. Through the integrated structure of the laser working tip and the laser fiber coupling connector, combined with the 0.5mm gap between the working end face of the fiber and the light output hole plane, the laser fiber position can be fixed, the laser is accurately emitted through the light output hole, and maintains a micro-contact state with the conjunctiva. With the biocompatibility of medical-grade silicone, the problems of easy displacement of the fiber in traditional working tips and the possibility of puncturing the conjunctiva or accidentally injuring the pupil are avoided, reducing postoperative complications. At the same time, it solves the problems of some integrated working tips that cannot quickly replace sterilization parts and have the risk of cross-infection, thus improving the safety of surgery. Attached Figure Description

[0013] Figure 1 This is a three-dimensional structural diagram of the present invention; Figure 2 This is a three-dimensional structural diagram of the laser handle and FC connector of this utility model. Figure 3 This is a three-dimensional structural diagram of the laser working tip and FC connector of this utility model; Figure 4 This is a three-dimensional structural diagram of the annular groove of this utility model; Figure 5 This is a three-dimensional structural diagram of the rhomboid anti-slip pattern of this utility model; Figure 6 This is a schematic diagram of the planar structure of the laser working tip of this utility model, viewed from the front and in cross-section.

[0014] In the diagram: 1. Laser handle; 2. Laser working tip; 3. Laser fiber coupling connector; 4. Diamond-shaped anti-slip pattern; 5. Annular groove; 6. FC connector. Detailed Implementation

[0015] It should be noted that, unless otherwise specified, the embodiments and features described in this application can be combined with each other. The present invention will now be described in detail with reference to the accompanying drawings and embodiments.

[0016] It should be noted that, unless otherwise specified, all technical and scientific terms used in this application have the same meaning as commonly understood by one of ordinary skill in the art to which this application pertains.

[0017] In this utility model, unless otherwise stated, the orientations used, such as "up" and "down", usually refer to the direction shown in the accompanying drawings, or to the vertical, perpendicular, or gravitational direction; similarly, for ease of understanding and description, "left" and "right" usually refer to the left and right shown in the accompanying drawings; "inner" and "outer" refer to the inner and outer contours of each component itself, but the above directional terms are not used to limit this utility model.

[0018] Please see Figures 1-6 A laser working tip 2 is provided on the left side of the laser handle 1. A laser fiber optic coupling connector 3 is integrated inside the laser working tip 2. The laser fiber optic coupling connector 3 is located 3 mm from the horseshoe-shaped edge of the laser working tip 2 and 2 mm from the side.

[0019] Specifically, by placing the laser working tip 2 on the left side of the laser handle 1 and integrating a laser fiber optic coupling connector 3 inside the laser working tip 2, and positioning the laser fiber optic coupling connector 3 3mm from the horseshoe-shaped edge of the laser working tip 2 and 2mm from the side, the surgeon can directly use the horseshoe-shaped edge of the laser working tip 2 as a positioning reference, quickly aligning the limbus without the need for a ruler. This ensures that the laser fiber optic coupling connector 3 maintains a precise distance from the ciliary body target area, achieving standardized positioning. This solves the problem of traditional working tips lacking a standardized positioning structure and relying on the surgeon's experience for positioning, resulting in errors exceeding ±1mm. It also avoids laser energy deviation due to inaccurate positioning, preventing scleral burns caused by being too close or ineffective destruction of ciliary body epithelial cells due to being too far away.

[0020] Please see Figures 1-6 The right end of the laser fiber coupling connector 3 is fixedly connected to an FC connector 6. The outer surface of the FC connector 6 is engaged with the FC interface at the left end of the laser handle 1. The fiber specification of the laser fiber coupling connector 3 is 600μm. The distance between the working end face of the laser fiber coupling connector 3 and the plane of the light output hole of the laser working tip 2 is 0.5mm.

[0021] Specifically, the FC connector 6 is fixedly connected to the right end of the laser fiber coupling connector 3, allowing the outer surface of the FC connector 6 to engage with the FC interface on the left end of the laser handle 1. A 600μm fiber is used, and the working end face of the fiber in the laser fiber coupling connector 3 is kept 0.5mm away from the plane of the light output hole of the laser working tip 2. The engagement of the FC connector 6 with the FC interface of the laser handle 1 enables quick insertion and removal of the laser working tip 2 from the laser handle 1, facilitating the replacement of the laser working tip 2. Furthermore, the 600μm fiber is compatible with mainstream laser energy transmission requirements, and the 0.5mm spacing prevents the working end face of the fiber from directly contacting the conjunctiva, reducing thermal damage. This solves the problems of non-reusability and high cost of traditional integrated working tips, as well as the poor interface compatibility of split designs, while ensuring stable laser energy transmission and preventing conjunctival thermal damage.

[0022] Please see Figures 1-6 The left end of the laser working tip 2 is horseshoe-shaped, and the inner wall of this end is foot-shaped. The distance between the fiber end face of the laser fiber coupling connector 3 and the horseshoe contact surface of the laser working tip 2 is 0.5mm, and the distance between the fiber end face of the laser fiber coupling connector 3 and the bottom surface of the annular groove 5 is 0.3mm.

[0023] Specifically, by setting the left end of the laser working tip 2 to a horseshoe shape with an inner wall shaped like a foot, and simultaneously setting the distance between the fiber end face of the laser fiber coupling connector 3 and the horseshoe contact surface of the laser working tip 2 to 0.5mm, and the distance between the fiber end face and the bottom surface of the annular groove 5 to 0.3mm, the horseshoe-shaped structure can naturally open the eyelid, preventing the eyelid from obstructing the surgical field of vision. The foot-shaped structure can fix the laser irradiation angle, ensuring that the laser accurately acts on the ciliary body. The two gaps can prevent the fiber end face of the laser fiber coupling connector 3 from directly contacting the tissue, reducing thermal damage. This solves the problems of frequent eyelid position adjustment, easy laser angle deviation, and easy direct contact of the fiber with the tissue causing thermal damage in traditional working tip surgery, improving the convenience and safety of surgical operation.

[0024] Please see Figures 1-6 The outer surfaces of the upper and lower sides of the horseshoe-shaped left end of the laser working tip 2 are etched with diamond-shaped anti-slip patterns 4. The laser working tip 2 is made of medical-grade silicone with a Shore hardness of 50A. The FC connector 6 is made of metal.

[0025] Specifically, a diamond-shaped anti-slip pattern 4 is etched on the outer surface of the upper and lower sides of the horseshoe-shaped left end of the laser working tip 2. The laser working tip 2 is made of medical-grade silicone with a Shore hardness of 50A, while the FC connector 6 is made of metal. The medical-grade silicone is soft and biocompatible, allowing it to conform to the surface of the eyeball and reduce irritation to eye tissues. The diamond-shaped anti-slip pattern 4 increases the friction between the laser working tip 2 and the sclera, while the metal FC connector 6 ensures connection strength and stability, preventing the laser working tip 2 from slipping during surgery due to eyelid movement or hand tremors. This reduces the number of adjustments required during surgery and solves the problem of traditional working tips having smooth contact surfaces and poor operational stability, which leads to a 15-20 minute extension of the operation time. It also avoids excessive tissue damage caused by repeated irradiation and improves patient comfort.

[0026] Please see Figures 1-6 An annular groove 5 is provided in the lower middle part of the inner wall of the foot-shaped laser working tip 2. The light output hole of the laser working tip 2 is located in the central area of ​​the annular groove 5. The fiber end of the laser fiber coupling connector 3 extends to the laser working tip 2 near the light output hole. The diameter of the annular groove 5 is 2mm and the depth is 0.5mm. The annular groove 5 can be filled with a high refractive index coupling agent, and the refractive index of the high refractive index coupling agent must be ≥1.45.

[0027] Specifically, an annular groove 5 with a diameter of 2 mm and a depth of 0.5 mm is opened in the lower middle part of the inner wall of the foot-shaped laser working tip 2. The light outlet of the laser working tip 2 is located in the central area of ​​the annular groove 5. The fiber end of the laser fiber coupling connector 3 passes through to the laser working tip 2 near the light outlet. A high refractive index coupling agent with a refractive index ≥1.45 is filled in the annular groove 5. The annular groove 5 provides a space for the coupling agent. The coupling agent and the fiber end can form a plano-concave lens effect by utilizing the refractive index difference, which increases the divergence angle and penetration depth of the laser when it is emitted, optimizes the energy distribution, and solves the problem of excessively high energy density or insufficient penetration depth caused by the refractive index difference when the laser is transmitted through the air by the traditional working tip laser. It avoids scleral surface burns, improves the efficiency of ciliary body destruction, and achieves energy control balance.

[0028] Working principle: In use, first connect the laser working tip 2 to the FC connector 6, which is fixedly connected to the right end of its internally integrated laser fiber coupling connector 3, and then snap it into the FC interface on the left end of the laser handle 1. This allows for quick assembly of the laser working tip 2 and the laser handle 1. At this point, the laser fiber coupling connector 3 is 3mm from the horseshoe-shaped edge of the laser working tip 2 and 2mm from the side. The 600μm fiber working end face is 0.5mm away from the plane of the laser working tip 2's light output hole. Next, the operator can hold the device and place the horseshoe-shaped structure on the left end of the laser working tip 2 against the surface of the eyeball. The horseshoe-shaped structure naturally opens the eyelid, and the foot-shaped structure on the inner wall fixes the laser irradiation angle. Simultaneously, align the limbus of the sclera with the horseshoe-shaped edge as a reference to ensure precise alignment of the laser fiber coupling connector 3 with the ciliary body target area. During this process, the laser working tip 2 uses medical-grade silicone with a Shore A hardness of 50A to adhere to the surface of the eyeball, reducing tissue irritation. The diamond-shaped anti-slip patterns 4 etched on the upper and lower outer surfaces of the horseshoe-shaped left end increase friction with the sclera. The FC connector 6 ensures a stable connection and prevents slippage during the procedure. A high-refractive-index coupling agent with a refractive index ≥1.45 is then filled into an annular groove 5, 2mm in diameter and 0.5mm deep, located slightly below the center of the foot-shaped inner wall of the laser working tip 2. The fiber optic end of the laser fiber coupling connector 3 extends to the laser working tip 2 near the light exit hole. After the laser beam exits through the fiber optic end, it passes through the coupling agent in the annular groove 5. The difference in refractive index between the coupling agent and air creates a plano-concave lens effect, increasing the laser divergence angle and penetration depth. Simultaneously, the 0.5mm distance between the fiber optic end face of the laser fiber coupling connector 3 and the horseshoe-shaped contact surface of the laser working tip 2, and the 0.3mm distance between the fiber optic end face and the bottom surface of the annular groove 5, prevents direct contact of the laser with tissue, thus avoiding thermal damage. Finally, the laser precisely targets the ciliary body through the light exit hole located in the central area of ​​the annular groove 5, achieving the therapeutic goal of destroying ciliary body epithelial cells, reducing aqueous humor production, and lowering intraocular pressure. This solves the problems of inaccurate positioning, unbalanced energy control, poor operational stability, and high cost associated with traditional working tips.

[0029] Of all the solutions mentioned above, those involving the connection between two components can be selected according to the actual situation, such as welding, bolt and nut connection, bolt or screw connection, or other known connection methods, which will not be elaborated here. For all the fixed connections mentioned above, welding is preferred. Although embodiments of this utility model have been shown and described, it will be understood by those skilled in the art that various changes, modifications, substitutions and variations can be made to these embodiments without departing from the principles and spirit of this utility model. The scope of this utility model is defined by the appended claims and their equivalents.

Claims

1. A photocoagulation treatment tip comprising a laser handle (1), characterized in that: A laser working tip (2) is provided on the left side of the laser handle (1). A laser fiber coupling connector (3) is integrated inside the laser working tip (2). An FC connector (6) is fixedly connected to the right end of the laser fiber coupling connector (3). The outer surface of the FC connector (6) is engaged with the FC interface at the left end of the laser handle (1). The left end of the laser working tip (2) is horseshoe-shaped, and the inner wall of this end is foot-shaped. The outer surfaces of the upper and lower sides of the horseshoe-shaped left end of the laser working tip (2) are engraved with diamond-shaped anti-slip patterns (4). An annular groove (5) is provided at the lower part of the foot-shaped inner wall of the laser working tip (2). The light output hole of the laser working tip (2) is located in the central area of ​​the annular groove (5). The fiber end of the laser fiber coupling connector (3) extends to the laser working tip (2) near the light output hole.

2. A photocoagulation treatment tip according to claim 1, characterized in that: The laser fiber coupling connector (3) is located 3 mm from the horseshoe-shaped edge of the laser working tip (2) and 2 mm from the side.

3. A photocoagulation treatment tip according to claim 1, characterized in that: The diameter of the annular groove (5) is 2 mm and the depth is 0.5 mm.

4. The photocoagulation treatment tip of claim 1, wherein: The distance between the fiber end face of the laser fiber coupling connector (3) and the horseshoe contact surface of the laser working tip (2) is 0.5 mm, and the distance between the fiber end face of the laser fiber coupling connector (3) and the bottom surface of the annular groove (5) is 0.3 mm.

5. The photocoagulation treatment tip of claim 1, wherein: The optical fiber of the laser fiber coupling connector (3) is 600μm, and the distance between the working end face of the optical fiber of the laser fiber coupling connector (3) and the light output hole of the laser working tip (2) is 0.5mm.

6. A photocoagulation treatment tip according to claim 1, characterized in that: The annular groove (5) can be filled with a high refractive index coupling agent, and the refractive index of the high refractive index coupling agent must be ≥1.

45.

7. A photocoagulation treatment tip according to claim 1, characterized in that: The laser working tip (2) is made of medical-grade silicone with a Shore hardness of 50A, and the FC connector (6) is made of metal.

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