Intraocular lighting device

Abstract

The intraocular lighting device comprises a light source and an optical fiber, one end of the optical fiber is connected with the light source, the other end of the optical fiber is used for extending into the eye to illuminate the interior of the eye, the end, extending into the eye, of the optical fiber comprises an annular area and a central area, the annular area is of an annular structure, the central area is of a circular structure, and the central area is adjacent to the annular area. The central area is located in the center of the annular area, the light transmittance of the central area is lower than that of the annular area, the central area is used for corresponding to the intraocular macular area, and the annular area is used for corresponding to the area outside the intraocular macular area. By reducing the light transmittance of the central area, the illumination intensity on the macular area during the operation is reduced, so that the light damage is reduced, meanwhile, the surrounding illumination intensity is not changed, and a sufficient illumination range is provided for an operator to facilitate the operation.

Description

Technical Field

[0001] This utility model relates to the field of medical device technology, and in particular to an intraocular lighting device. Background Technology

[0002] Illumination optical fibers (or simply illumination fibers) are commonly used instruments in retinal surgery. They are primarily used to provide intraocular illumination during intraocular surgeries such as retinal and vitreoretinal surgeries, allowing surgeons to clearly see the surgical field and perform procedures more effectively. An optical fiber is a light-conducting medium made of glass or plastic fiber that utilizes the principle of total internal reflection to achieve long-distance illumination. Invention patent CN201080009714.9 details how to use optical coupling elements to couple light onto an optical fiber and guide it into the eye.

[0003] However, the design of intraocular lighting devices must take into account the issue of retinal light damage. During intraocular surgery, light rays travel through optical fibers, bypassing the cornea and lens, and directly illuminate the inside of the eye, which can easily damage the retina. In particular, when the light is directly focused on the macula, it may affect the integrity of cell membranes by disrupting unsaturated fatty acids and inducing the production of free radicals.

[0004] The light intensity of the central and peripheral areas of existing illumination optical fibers is the same, which causes some light damage to the macula during macular surgery due to direct irradiation. Therefore, an illumination optical fiber is proposed to reduce the phototoxicity of macular surgery by reducing the light transmittance of the central area. Utility Model Content

[0005] In view of this, the purpose of this utility model is to provide an intraocular illumination device, which aims to solve the technical problem that the light intensity of the central and peripheral areas of the existing illumination optical fiber is the same, which causes certain light damage to the macula when directly irradiating the macula during macular surgery.

[0006] This invention provides an intraocular lighting device, including a light source and an optical fiber. One end of the optical fiber is connected to the light source, and the other end extends into the eye to illuminate the eye. The end of the optical fiber extending into the eye includes an annular region and a central region. The annular region has an annular structure, and the central region has a circular structure. The central region is adjacent to the annular region and located in the center of the annular region. The light transmittance of the central region is lower than that of the annular region. The central region corresponds to the macula in the eye, and the annular region corresponds to the area outside the macula in the eye.

[0007] Furthermore, the central area is a first lens, and the annular area is a second lens, wherein the transmittance of the first lens is lower than that of the second lens.

[0008] Furthermore, both the first lens and the second lens are plane mirrors, and the first lens and the second lens are disposed on the end face of the optical fiber.

[0009] Furthermore, both the first lens and the second lens are curved mirrors, and the first lens and the second lens are disposed on the end face of the optical fiber.

[0010] Furthermore, it also includes an operating handle, which is sleeved on the peripheral sidewall of the optical fiber. The operating handle is provided with an axial adjustment component, which is used to adjust the relative position of the operating handle and the optical fiber in the axial direction.

[0011] Furthermore, the axial adjustment assembly includes a first helical gear, a first reduction gear set, a first upper roller, and a first lower roller. The first helical gear is rotatably connected to the operating handle. The operating handle has a first window, through which a portion of the peripheral side surface of the first helical gear extends beyond the operating handle. The first upper roller and the first lower roller are both rotatably connected to the operating handle. The first upper roller and the first lower roller abut against the peripheral sidewall of the optical fiber and are symmetrically arranged about the central axis of the optical fiber. The first helical gear meshes with the power input end of the first reduction gear set, and the first upper roller meshes with the power output end of the first reduction gear set to drive the optical fiber to move in the axial direction.

[0012] Furthermore, the operating handle has a first recess and a second recess on its peripheral sidewall, the first recess being used to place the middle finger and the second recess being used to place the thumb.

[0013] Beneficial Effects: This utility model provides an intraocular lighting device, including a light source and an optical fiber. One end of the optical fiber is connected to the light source, and the other end extends into the eye for intraocular illumination. The end of the optical fiber extending into the eye includes an annular region and a central region. The annular region has a ring structure, and the central region has a circular structure. The central region is adjacent to the annular region and located at the center of the annular region. The light transmittance of the central region is lower than that of the annular region. The central region corresponds to the macular region within the eye, and the annular region corresponds to the area outside the macular region. This application reduces the light intensity on the macular region during surgery by lowering the light transmittance of the central region, thereby reducing light damage, while not changing the peripheral light intensity, providing the surgeon with sufficient illumination for surgical operations. Attached Figure Description

[0014] Figure 1 This is a schematic diagram of the overall structure of the intraocular lighting device of this utility model;

[0015] Figure 2 This is a schematic diagram of the axial adjustment assembly.

[0016] Figure 3 This is a schematic diagram of the internal structure of the operating handle;

[0017] Figure 4 This is a schematic diagram of the external structure of the operating handle;

[0018] Figure 5 This is a schematic diagram of a structure where both the first and second lenses are plane mirrors.

[0019] Figure 6 This is a schematic diagram of a structure where both the first and second lenses are curved mirrors.

[0020] Figure 7 This is a rendering of the intraocular lighting device of this utility model.

[0021] In the diagram: 1. Light source; 2. Optical fiber; 3. Central area; 4. Annular area; 5. Operating handle; 51. First window; 52. Guide channel; 53. First recess; 54. Second recess; 55. Through hole; 6. Axial adjustment assembly; 61. First helical gear; 62. First reduction gear group; 63. First upper roller; 64. First lower roller; 8. Dark area; 9. Bright area. Detailed Implementation

[0022] The technical solutions of the present utility model will be clearly and completely described below with reference to the accompanying drawings of the embodiments. All other embodiments obtained by those skilled in the art based on the embodiments of the present utility model without creative effort are within the scope of protection of the present utility model.

[0023] Please see Figures 1 to 7 This utility model provides an intraocular lighting device, including a light source 1 and an optical fiber 2. One end of the optical fiber 2 is connected to the light source 1, and the other end is used to extend into the eye for intraocular illumination. The end of the optical fiber 2 extending into the eye includes an annular region 4 and a central region 3. The annular region 4 has an annular structure, and the central region 3 has a circular structure. The central region 3 is adjacent to the annular region 4 and is located in the center of the annular region 4. The light transmittance of the central region 3 is lower than that of the annular region 4. The central region 3 is used to correspond to the macular region of the eye, and the annular region 4 is used to correspond to the area outside the macular region of the eye.

[0024] like Figure 7 As shown, the area of ​​the central region 3 should account for 30% of the total area of ​​the central region 3 and the annular region 4. By partially blocking the light transmission of the central region 3, the light transmittance is reduced, thus reducing the amount of light passing through and consequently lowering the light intensity in the central region 3, thereby reducing light damage to the macula during surgery. Partial light transmission blocking of the central region 3 can be achieved by altering the surface roughness of the material (e.g., frosted glass) or by applying a special coating (e.g., a film coating) to increase light scattering and reflection, thereby reducing light transmittance. Figure 7 The dark area 8 corresponds to the effect of light entering the eye in the central area 3, and the bright area 9 corresponds to the effect of light entering the eye in the annular area 4.

[0025] Specifically, the central area 3 is the first lens, and the annular area 4 is the second lens. The transmittance of the first lens is lower than that of the second lens. In this embodiment, the transmittance can be reduced by increasing light scattering and reflection through changing the surface roughness of the first lens (e.g., frosted glass) or by applying a special coating (e.g., a film coating). For safety and usability reasons, the processed surfaces of the first and second lenses should face the end face of the optical fiber 2 (to avoid contact with the vitreous cavity fluid, to fill the unevenness of the frosted surface to reduce diffuse reflection; or to ensure that the coating layer contacts the fundus tissue), ensuring that the lens surface away from the illumination optical fiber 2 is smooth. To avoid a decrease in the transmission efficiency of light energy transmitted from the optical fiber 2 to the first and second lenses, the processed surfaces of the first and second lenses should be parallel to the end face of the illumination optical fiber 2.

[0026] Reference Figure 5 In one feasible embodiment, both the first lens and the second lens are plane mirrors, and they are disposed on the end face of the optical fiber 2. In this embodiment, since both the first lens and the second lens are plane mirrors, the light in the optical fiber 2 will propagate to other media at the end after passing through the first lens and the second lens. The above-described embodiment of the plane mirror has a simple structure and is easy to manufacture and produce.

[0027] Reference Figure 6 In one feasible embodiment, both the first lens and the second lens are curved mirrors, and they are disposed on the end face of the optical fiber 2. In this embodiment, when both the first lens and the second lens are curved mirrors, the curved surface at the end changes the propagation direction and focusing characteristics of the light beam. Curved surface shapes include spherical and parabolic surfaces, which can help focus the light beam or guide the beam in a specific direction. The above-described implementation of curved mirrors can change the light propagation path, which is beneficial for improving the coupling efficiency or focusing accuracy of light within the optical fiber 2.

[0028] In one feasible embodiment, an operating handle 5 is further included. The operating handle 5 is sleeved on the peripheral sidewall of the optical fiber 2. The operating handle 5 is provided with an axial adjustment component 6, which is used to adjust the relative position of the operating handle 5 and the optical fiber 2 in the axial direction. After the end of the optical fiber 2 extends into the eye, it needs to be finely adjusted to illuminate the target area. In this embodiment, during surgical illumination, while the operating handle 5 remains stationary, the relative position of the operating handle 5 and the optical fiber 2 in the axial direction is adjusted by the axial adjustment component 6, thereby adjusting the length of the end of the optical fiber 2 extending into the eye.

[0029] Specifically, the axial adjustment assembly 6 includes a first helical tooth 61, a first reduction gear set 62, a first upper roller 63, and a first lower roller 64. The first helical tooth 61 is rotatably connected to the operating handle 5. The operating handle 5 has a first window 51, which allows a portion of the peripheral side surface of the first helical tooth 61 to extend outside the operating handle 5. The first upper roller 63 and the first lower roller 64 are both rotatably connected to the operating handle 5. The first upper roller 63 and the first lower roller 64 abut against the peripheral sidewall of the optical fiber 2 and are symmetrically arranged about the central axis of the optical fiber 2. The first helical tooth 61 meshes with the power input end of the first reduction gear set 62, and the first upper roller 63 meshes with the power output end of the first reduction gear set 62 to drive the optical fiber 2 to move in the axial direction. In this embodiment, the first upper roller 63 and the first lower roller 64 jointly clamp the optical fiber 2, providing clamping force for the optical fiber 2. Therefore, when the first helical gear 61 rotates, the friction between the first upper roller 63 and the first lower roller 64 and the optical fiber 2 can push the optical fiber 2 relative to the operating handle 5 to move. The first upper roller 63 acts as the driving wheel, and the first lower roller 64 acts as the driven wheel. The main function of the first reduction gear set 62 is to reduce the output speed of the first upper roller 63 and increase the output torque to meet the requirements for precise adjustment of the optical fiber 2. The first reduction gear set 62 consists of multiple pairs of meshing gears. It is worth noting that in this embodiment, the tangent directions of the first upper roller 63 and the first lower roller 64 are parallel to the central axis of the optical fiber 2. Therefore, when the first roller rotates, it can drive the optical fiber 2 to move along its axial direction. Furthermore, the operating handle 5 is provided with a guide channel 52, through which the optical fiber 2 passes. Simultaneously, the peripheral wall of the guide channel 52 has through holes 55 for the first upper roller 63 and the first lower roller 64 to enter. After the first upper roller 63 and the first lower roller 64 enter the through hole 55, they abut against the optical fiber 2.

[0030] In one feasible embodiment, the operating handle 5 has a first recess 53 and a second recess 54 on its peripheral sidewall. The first recess 53 is used to place the middle finger, and the second recess 54 is used to place the thumb. During illumination operation, one side of the operating handle 5 rests against the web of the thumb and index finger, the middle finger is placed in the first recess 53, and the thumb is placed in the second recess 54 to grip the operating handle 5. A first spiral tooth 61 is located between the first recess 53 and the second recess 54 to facilitate rotation of the first spiral tooth 61 by the index finger. Furthermore, the tangential direction of the first spiral tooth 61 is parallel to the central axis of the optical fiber 2, facilitating rotation of the first spiral tooth 61 by the index finger.

[0031] It will be apparent to those skilled in the art that this application is not limited to the details of the exemplary embodiments described above, and that this application can be implemented in other specific forms without departing from the spirit or essential characteristics of this application. Therefore, the embodiments should be considered illustrative and non-limiting in all respects, and the scope of this application is defined by the appended claims rather than the foregoing description. Thus, all variations falling within the meaning and scope of the equivalent elements of the claims are intended to be included within this application. No reference numerals in the claims should be construed as limiting the scope of the claims.

[0032] The above-described embodiments are only used to illustrate the technical solutions of this application, and are not intended to limit them. Although this application has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some of the technical features. Such modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the spirit and scope of the technical solutions of the embodiments of this application.

Claims

1. An intraocular illumination device, characterized by: The application relates to an intraocular illumination device, which comprises a light source (1) and an optical fiber (2), one end of the optical fiber (2) is connected with the light source (1), the other end is used for extending into the eye for intraocular illumination, the end of the optical fiber (2) extending into the eye comprises a ring-shaped area (4) and a central area (3), the ring-shaped area (4) is in a ring-shaped structure, the central area (3) is in a circular structure, the central area (3) is adjacent to the ring-shaped area (4) and is located in the center of the ring-shaped area (4), the light transmittance of the central area (3) is lower than that of the ring-shaped area (4), the central area (3) is used for corresponding to the macular area in the eye, and the ring-shaped area (4) is used for corresponding to the area outside the macular area in the eye.

2. The intraocular illumination device of claim 1, wherein: The central area (3) is a first lens, and the ring-shaped area (4) is a second lens, the light transmittance of the first lens is lower than that of the second lens.

3. The intraocular illumination device of claim 2, wherein: The first lens and the second lens are both plane mirrors, and the first lens and the second lens are arranged on the end face of the optical fiber (2).

4. The intraocular illumination device of claim 2, wherein: The first lens and the second lens are both curved mirrors, and the first lens and the second lens are arranged on the end face of the optical fiber (2).

5. The intraocular illumination device of claim 1, wherein: The application further comprises an operation handle (5), the operation handle (5) is sleeved on the peripheral wall of the optical fiber (2), an axial adjusting assembly (6) is arranged on the operation handle (5), and the axial adjusting assembly (6) is used for adjusting the relative position of the operation handle (5) and the optical fiber (2) in the axial direction.

6. The intraocular illumination device of claim 5, wherein: The axial adjusting assembly (6) comprises a first pinion (61), a first speed reduction gear set (62), a first upper roller (63) and a first lower roller (64), the first pinion (61) is rotationally connected to the operation handle (5), the operation handle (5) is provided with a first window (51), part of the peripheral surface of the first pinion (61) can extend out of the operation handle (5) through the first window (51), the first upper roller (63) and the first lower roller (64) are both rotationally connected to the operation handle (5), the first upper roller (63) and the first lower roller (64) are both in abutment with the peripheral wall of the optical fiber (2) and are symmetrically arranged about the central axis of the optical fiber (2), the first pinion (61) is in mesh with the power input end of the first speed reduction gear set (62), and the first upper roller (63) is in mesh with the power output end of the first speed reduction gear set (62) to drive the optical fiber (2) to move in the axial direction.

7. The intraocular illumination device of claim 5, wherein: The peripheral wall of the operation handle (5) is provided with a first recess (53) and a second recess (54), the first recess (53) is used for placing the middle finger, and the second recess (54) is used for placing the thumb.

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