An auxiliary illumination device for vitreoretinal surgery

Abstract

The application relates to the technical field of medical devices, in particular to an auxiliary lighting device for vitreoretinal surgery, which comprises an optical fiber, a catheter and an optical fiber driving element; the proximal end of the optical fiber is provided with an optical fiber connector, the optical fiber connector is used for connecting a light guide, the light guide is connected with a light source and has a light output end, and the optical fiber receives a light beam transmitted by the light guide; the catheter is configured to be inserted into an incision of an eyeball and kept in position relative to the eyeball, the distal end of the optical fiber is inserted into the interior of the catheter and can move along the catheter; the optical fiber driving element is connected with the catheter and can move axially relative to the catheter, and the optical fiber is fixedly connected to the optical fiber driving element. The catheter fixed to the eyeball establishes a stable reference, the optical fiber driving element which can move axially relative to the catheter drives the optical fiber to move, so that the exposed length of the distal end of the optical fiber relative to the distal end of the catheter is continuously adjusted during the surgery, the depth of the optical fiber into the vitreous cavity is changed, and the illumination range of the optical fiber is adjusted.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, and specifically to an auxiliary lighting device for vitreoretinal surgery. Background Technology

[0002] Currently, the most commonly used intraocular lighting methods in vitrectomy surgery include handheld light guides and pendant-type intraocular illuminators.

[0003] Handheld light guides are typically inserted into the vitreous cavity through a surgical channel in the eye. Their distal end emits illumination light into the eye. The surgeon can manipulate the guide's position and orientation within the eye, allowing for flexible localized illumination of the target area. However, because handheld light guides require one of the surgeon's hands, it is difficult to simultaneously perform illumination and bi-handed surgical procedures when two surgical instruments are needed. This limits their application in complex vitreoretinal surgeries.

[0004] To address the issue of handheld light guides occupying one of the surgeon's hands, current technologies also employ pendant-style intraocular illuminators. These typically fix the light guide structure within the surgical channel of the eyeball, keeping its distal end within the vitreous cavity, thus eliminating the need for the surgeon to continuously hold the illuminator. However, the light guide structure of pendant-style intraocular illuminators is usually fixed relative to the eyeball, limiting their ability to adjust the illumination position and direction. To achieve a wider illumination range, existing pendant-style intraocular illuminators often employ broad illumination methods. When the surgeon needs to observe local lesion areas, tissue interfaces, or fine structures between the proliferative membrane and the retina, their local directional illumination capability is insufficient, affecting the surgeon's identification of local tissue structures and the accuracy of surgical procedures.

[0005] Therefore, it is necessary to provide an auxiliary lighting device to provide more flexible and accurate local intraocular illumination for vitrectomy surgery. Summary of the Invention

[0006] The purpose of this invention is to provide an auxiliary lighting device for vitreoretinal surgery, so as to solve the technical problem that the lighting range of current intraocular lighting devices is not easy to adjust.

[0007] To solve the above-mentioned technical problems, the present invention specifically provides the following technical solution: An illumination device for vitreoretinal surgery, comprising: An optical fiber, wherein an optical fiber connector is mounted on the near end of the optical fiber, the optical fiber connector is used to connect an optical guide, the optical guide is connected to a light source and has an optical output end, and the optical fiber receives the light beam transmitted by the optical guide. A catheter configured to be inserted into an incision in the eyeball and held in position relative to the eyeball, the distal end of the optical fiber being inserted into the interior of the catheter and movable along the catheter; An optical fiber driver is connected to the conduit and is axially movable relative to the conduit, and the optical fiber is fixedly connected to the optical fiber driver.

[0008] Furthermore, it also includes a housing, the optical fiber, the conduit and the optical fiber driver are integrated inside the housing, and the distal end of the conduit is disposed outside the housing; The housing includes: a first hollow sleeve, a second hollow sleeve, and an elastic support member; The first hollow sleeve includes a first cylinder and an end plate at one end. The proximal end of the conduit is fixedly connected to the end plate. The optical fiber driver is slidably connected to the first cylinder along the axial direction. The distal end face of the optical fiber driver, the end plate, and the inner wall of the first cylinder together form an axially extending chamber. The second hollow sleeve includes a second cylindrical body and a knob at one end, with the end face of the second cylindrical body contacting the proximal end face of the fiber optic drive component; The first cylinder is threadedly connected to the second cylinder so that when the second cylinder is rotated in the forward direction, the end face of the second cylinder can push the fiber optic drive to move toward the eyeball axis. The elastic support is installed inside the chamber, and its two ends are connected to the end plate and the proximal end face of the fiber optic driver, so that when the second cylinder is rotated in the opposite direction, the elastic support can push the fiber optic driver to reset.

[0009] Furthermore, the elastic support is a helical spring, which is fitted on the outside of the optical fiber and configured to support the optical fiber when it is subjected to axial load, thereby limiting the radial bending of the optical fiber within the cavity.

[0010] Furthermore, the outer peripheral surface of the fiber optic driver is provided with an axially extending guide rib, and the first hollow sleeve is formed with an axially extending guide hole. The guide hole radially penetrates the first hollow sleeve, and the guide rib is accommodated in the guide hole to restrict the rotation of the fiber optic driver relative to the first hollow sleeve and allow the fiber optic driver to move axially.

[0011] Furthermore, the outer circumferential surface of the first hollow sleeve is provided with an external thread, and the external thread is connected to a nut. The guide rib extends to the outside of the first hollow sleeve and can abut against the axial end face of the nut to limit the axial movement range of the fiber optic drive relative to the first hollow sleeve.

[0012] Furthermore, the outer peripheral surface of the first hollow sleeve is provided with an axially extending groove, a portion of the external thread of the first hollow sleeve is cut off by the groove, and the bottom wall of the groove is provided with a scale indicating the position of the optical fiber driver.

[0013] Furthermore, the interior of the chamber is provided with an elastic membrane with a truncated cone-shaped longitudinal section. The elastic membrane includes a circular outer periphery and an inner hole. The outer periphery of the elastic membrane is fixedly and sealed to the inner wall of the chamber, and the inner hole of the elastic membrane is fixedly and sealed to the outer wall of the optical fiber. The elastic membrane is configured to adaptively deform when the optical fiber moves axially.

[0014] Furthermore, the catheter is provided with a branch tube, which together with the catheter forms an infusion channel for delivering infusion fluid or infusion gas into the eyeball, and the elastic membrane is used to seal and isolate the infusion channel from the cavity.

[0015] Furthermore, the conduit includes a first segment close to the eyeball, a second segment away from the eyeball, and a flexible segment connecting the first segment and the second segment. The wall thickness of the flexible segment is less than the wall thickness of the first segment and the second segment. The flexible segment has a continuous lumen extending along the axial direction of the conduit, and the optical fiber passes through the lumen.

[0016] Compared with the prior art, the present invention has the following advantages: This invention utilizes a catheter fixed to the eyeball to establish a stable reference. An optical fiber driver that can move axially relative to the catheter drives the optical fiber to move, thereby continuously adjusting the exposed length of the distal end of the optical fiber relative to the distal end of the catheter during surgery. This changes the depth of the optical fiber entering the vitreous cavity, thereby adjusting the illumination range of the optical fiber. Attached Figure Description

[0017] To more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the accompanying drawings used in the description of the embodiments or the prior art will be briefly introduced below.

[0018] Figure 1 This is a perspective view of the first embodiment of the present invention; Figure 2 This is a longitudinal sectional view of the first embodiment of the present invention; Figure 3 This is a perspective view of the second embodiment of the present invention; Figure 4 This is a longitudinal sectional view of the second embodiment of the present invention; Figure 5 This is a perspective view of the third embodiment of the present invention; Figure 6This is a longitudinal sectional view of the third embodiment of the present invention; Figure 7 This is a perspective view of the fourth embodiment of the present invention; The reference numerals in the figure are as follows: 1-Fiber optic cable; 11-Fiber optic connector; 2-Conduit; 21-Branch; 22-First segment; 23-Second segment; 24-Flexible segment; 3-Fiber optic drive component; 31-Guide rib; 4-First hollow sleeve; 41-First cylinder body; 42-End plate; 43-Cavity; 44-Guide hole; 45-Groove; 5-Second hollow sleeve; 51-Second cylinder body; 52-Knob; 6-Elastic support; 7-Nut; 8-Elastic membrane; 9-Eyeball. Detailed Implementation

[0019] To make the objectives, technical solutions, and advantages of this application clearer, the technical solutions of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of this application, not all embodiments. Based on the embodiments of this application, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of this application.

[0020] (First embodiment) like Figure 1 and Figure 2 As shown, the illumination device for vitreoretinal surgery includes: an optical fiber 1, a conduit 2, and an optical fiber driver 3.

[0021] An optical fiber connector 11 is installed at the near end of the optical fiber 1. The optical fiber connector 11 is used to connect to the light guide. The light guide is connected to the light source and has a light output end. The optical fiber 1 receives the light beam transmitted by the light guide.

[0022] The catheter 2 is configured to be inserted into the incision of the eyeball 9 and remain in position relative to the eyeball 9. The distal end of the optical fiber 1 is inserted into the interior of the catheter 2 and can move along the catheter 2. The connection structure between the catheter 2 and the eyeball 9 can adopt the structure of a chandelier-type intraocular illuminator.

[0023] The fiber optic drive unit 3 is connected to the conduit 2 and can move axially relative to the conduit 2, and the fiber optic 1 is fixedly connected to the fiber optic drive unit 3.

[0024] The operating steps for the illumination device during retinal surgery are as follows.

[0025] Step one, preparation stage: turn on the light source to generate a light beam, the light beam is transmitted to the optical fiber 1 through the light guide, and is transmitted to the distal end of the optical fiber 1; at this time, the optical fiber driving member 3 is fixedly connected with the optical fiber 1, and the catheter 2 is coaxially arranged with the optical fiber driving member 3.

[0026] Step two, catheter 2 insertion stage: insert the catheter 2 into the scleral incision of the eyeball 9, so that a part of the catheter 2 enters the inside of the eyeball 9, and the catheter 2 is kept in position relative to the eyeball 9; under the condition that the catheter 2 keeps the position, the optical fiber 1 can move along the axial direction of the catheter 2 without moving the whole catheter 2 relative to the eyeball 9.

[0027] Step three, first illumination working condition: the distal end of the optical fiber 1 protrudes from the distal end of the catheter 2 by a first length, and a first distance is kept between the distal end of the optical fiber 1 and the target tissue, thereby forming a first illumination range to meet the needs of the operator to illuminate a larger range.

[0028] Step four, second illumination working condition: when it is needed to illuminate the target area closer to the eye, the operator operates the optical fiber driving member 3 to move the optical fiber driving member 3 along the axial direction relative to the catheter 2, since the optical fiber 1 is fixedly connected with the optical fiber driving member 3, the optical fiber 1 moves together with the optical fiber driving member 3 into the inside of the eyeball 9, thereby making the distal end of the optical fiber 1 further protrude from the distal end of the catheter 2 and increasing the depth of the optical fiber 1 into the inside of the eyeball 9; when the optical fiber 1 moves to a predetermined position, the distal end of the optical fiber 1 is kept at a second position, at this time, the distance between the distal end of the optical fiber 1 and the target tissue is less than that in the first illumination working condition, thereby obtaining the illumination effect closer to the target area, so as to facilitate the operator to observe the local structure such as retinal lesions and tissue interface.

[0029] Step five, optical fiber 1 pulling-out step: when the close-range illumination is no longer needed or the illumination is no longer needed, the optical fiber driving member 3 is reversely operated to move the optical fiber driving member 3 away from the inside of the eyeball 9; since the optical fiber 1 is fixedly connected with the optical fiber driving member 3, the optical fiber 1 moves together with the optical fiber driving member 3 to the outside of the eyeball 9, so that the distal end of the optical fiber 1 is retracted into the inside of the catheter 2 or the protruding length thereof is reduced, thereby reducing the risk of contact between the distal end of the optical fiber 1 and the intraocular tissue.

[0030] In order to facilitate the precise operation of the optical fiber 1, the catheter 2 and the optical fiber driving member 3 in the above-mentioned embodiments, an apparatus integrating the optical fiber 1, the catheter 2 and the optical fiber driving member 3 is proposed below to facilitate the user operation.

[0031] (Second embodiment) As shown in Figure 3 and Figure 4 , in a preferred embodiment, the illumination device further comprises a housing, the optical fiber 1, the catheter 2 and the optical fiber driving member 3 are integrated in the inside of the housing, and the distal end of the catheter 2 is arranged outside the housing. The shell comprises a first hollow sleeve 4, a second hollow sleeve 5 and an elastic support 6. The first hollow sleeve 4 comprises a first cylinder 41 and an end plate 42 at one end of the first cylinder 41, and the proximal end of the catheter 2 is fixedly connected to the end plate 42, and the optical fiber driving member 3 is in axial sliding connection with the first cylinder 41, and the distal end face of the optical fiber driving member 3, the end plate 42 and the inner wall of the first cylinder 41 jointly form a chamber 43 extending in the axial direction; The second hollow sleeve 5 comprises a second cylinder 51 and a knob 52 at one end of the second cylinder 51, and the end face of the second cylinder 51 contacts the proximal end face of the optical fiber driving member 3; The first cylinder 41 is in threaded connection with the second cylinder 51, so that when the second cylinder 51 is rotated in the forward direction, the end face of the second cylinder 51 can push the optical fiber driving member 3 to move axially towards the eyeball 9; The elastic support 6 is installed inside the chamber 43, and the two ends of the elastic support 6 are connected to the end plate 42 and the proximal end face of the optical fiber driving member 3, so that when the second cylinder 51 is rotated in the reverse direction, the elastic support 6 can push the optical fiber driving member 3 to reset.

[0032] In the above design, the medical staff can complete the preparation work by inserting the light guide into the optical fiber connector 11; the first hollow sleeve 4 is configured to have a handle shape, so that the operator can hold the first hollow sleeve 4 to perform the operation; the operator can rotate the second hollow sleeve 5 with the other hand to drive the optical fiber 1 to move axially.

[0033] The specific operation steps are as follows: The first hollow sleeve 4 remains fixed relative to the eyeball 9, and the end face of the second hollow sleeve 5 contacts the proximal end face of the optical fiber driving member 3, and when the operator rotates the second hollow sleeve 5, the threaded connection between the second hollow sleeve 5 and the first hollow sleeve 4 causes the second hollow sleeve 5 to axially displace relative to the first hollow sleeve 4; because the optical fiber driving member 3 is in contact with the second hollow sleeve 5, the optical fiber driving member 3 moves along the axial direction of the first hollow sleeve 4 with the second hollow sleeve 5.

[0034] Therefore, the operator can control the rotation direction and rotation angle of the second hollow sleeve 5 to make the distal end of the optical fiber 1 extend or retract relative to the distal end of the catheter 2, so as to continuously adjust the depth of the optical fiber 1 into the eyeball 9; in the case where the thread pitch is determined, the axial displacement of the second hollow sleeve 5 caused by one rotation is basically determined, so that the rotation amount of the second hollow sleeve 5 can be controlled to finely adjust the insertion depth of the optical fiber 1.

[0035] Furthermore, since optical fiber 1 is a flexible component, it is prone to radial bending when subjected to radial thrust. This may cause optical fiber 1 to bend inside the cavity 43 instead of moving axially when optical fiber drive 3 moves axially. To solve this problem, this embodiment selects a helical spring as the elastic support 6. The helical spring is fitted on the outside of optical fiber 1 and configured to support optical fiber 1 when it is subjected to axial load, so as to limit the radial bending of optical fiber 1 in the cavity 43.

[0036] On the other hand, in the above embodiment, since the second hollow sleeve 5 performs a helical motion, the fiber drive 3 driven by it may rotate during axial movement, causing unnecessary twisting of the fiber 1. To this end, the outer peripheral surface of the fiber drive 3 is provided with an axially extending guide rib 31, and the first hollow sleeve 4 is formed with an axially extending guide hole 44. The guide hole 44 radially penetrates the first hollow sleeve 4, and the guide rib 31 is accommodated in the guide hole 44 to restrict the rotation of the fiber drive 3 relative to the first hollow sleeve 4 and allow the fiber drive 3 to move axially.

[0037] Since the internal thread of the first hollow sleeve 4 is cut off at the guide hole 44, the second hollow sleeve 5 engages with the remaining area of ​​the internal thread of the first hollow sleeve 4.

[0038] In this improved embodiment, when the second hollow sleeve 5 rotates relative to the first hollow sleeve 4, the second hollow sleeve 5 generates axial displacement through threaded engagement. Since the optical fiber driver 3 is constrained by the rotation of the guide hole 44, the rotation of the second hollow sleeve 5 will not drive the optical fiber driver 3 to rotate synchronously, but will cause the optical fiber driver 3 to move along the axial direction of the first hollow sleeve 4, thereby preventing the optical fiber 1 from twisting.

[0039] On the other hand, since the feed depth of the optical fiber 1 cannot be directly observed by rotating the second hollow sleeve 5, in order to visualize the feed depth of the optical fiber 1, the outer peripheral surface of the first hollow sleeve 4 is also provided with an axially extending groove 45. A portion of the external thread of the first hollow sleeve 4 is cut off by the groove 45, and the bottom wall of the groove 45 is provided with a scale indicating the position of the optical fiber driver 3.

[0040] Before use, medical staff can determine the target position of the fiber optic drive 3 in the first hollow sleeve 4 based on the expected insertion depth of the fiber optic 1. At the same time, medical staff can also determine the current position of the fiber optic drive 3 based on the reading of the scale aligned with the guide rib 31.

[0041] When it is necessary to change the maximum insertion depth of optical fiber 1, medical staff rotate the second hollow sleeve 5 to move the optical fiber drive 3 along the axial direction of the first hollow sleeve 4, so that the guide rib 31 is aligned with the scale position corresponding to the target insertion depth.

[0042] Furthermore, since the position of the fiber optic drive 3 must be constantly monitored while rotating the second hollow sleeve 5, errors may occur during the operation. To prevent medical staff from accidentally rotating the second hollow sleeve 5 too much and causing the fiber optic 1 to be inserted too deeply, a preferred embodiment is proposed below. This embodiment aims to pre-set the position of the fiber optic drive 3 and then move the fiber optic drive 3 to the pre-set position, thereby avoiding errors caused by being in a hurry.

[0043] The outer circumferential surface of the first hollow sleeve 4 is provided with threads, and a nut 7 is threadedly connected thereto. The guide rib 31 extends to the outside of the first hollow sleeve 4 and can abut against the axial end face of the nut 7 to limit the axial movement range of the fiber optic drive 3 relative to the first hollow sleeve 4.

[0044] During use, medical staff can preset the maximum depth of the optical fiber 1 entering the eyeball 9 by reading the scale and adjusting the position of the nut 7. When the guide rib 31 on the optical fiber drive 3 abuts against the axial end face of the nut 7, the optical fiber 1 reaches the target insertion depth.

[0045] In the above design, since setting the depth of fiber 1 and moving fiber 1 are performed in two separate steps, the workload of medical staff is reduced and errors during the operation are avoided.

[0046] (Third embodiment) In some surgeries, the catheter 2 used to insert the optical fiber 1 is also used to infuse gas and liquid into the eyeball 9. If the gas and liquid flow back into the cavity 43, it may cause infection.

[0047] like Figure 5 and Figure 6 As shown, in a preferred embodiment: the interior of the chamber 43 is provided with an elastic membrane 8 with a truncated cone longitudinal section. The elastic membrane 8 includes a circular outer periphery and an inner hole. The outer periphery of the elastic membrane 8 is fixed and sealed to the inner wall of the chamber 43, and the inner hole of the elastic membrane 8 is fixed and sealed to the outer wall of the optical fiber 1. The elastic membrane 8 is configured to adaptively deform when the optical fiber 1 moves axially.

[0048] Specifically, the outer periphery of the elastic membrane 8 is inserted between the helical spring and the end plate 42, and the inner hole of the elastic membrane 8 is inserted between the helical spring and the optical fiber 1. The helical spring hugs the outer periphery of the optical fiber 1 through the elastic membrane 8. Since the elastic membrane 8 is a truncated cone shape, it has a certain space for folding or unfolding in the axial direction.

[0049] When the optical fiber 1 moves into the eyeball 9, the truncated cone-shaped elastic membrane 8 can fold or unfold in the corresponding direction; when the optical fiber 1 moves in the opposite direction, the elastic membrane 8 undergoes elastic deformation in the opposite direction; thus, the elastic membrane 8 can maintain a fixed seal at the outer periphery while allowing the inner hole to move axially with the optical fiber 1, thereby enabling the elastic membrane 8 to always seal and isolate the infusion channel from the chamber 43 during the movement of the optical fiber 1, reducing the possibility of infusion fluid or infusion gas entering the interior of the chamber 43.

[0050] To facilitate the infusion of gas and liquid into the eyeball 9 through the catheter 2, a branch tube 21 is provided on the catheter 2. The branch tube 21 and the catheter 2 form an infusion channel for delivering infusion fluid or gas into the eyeball 9. The infusion channel is isolated from the chamber 43 by an elastic membrane 8.

[0051] During vitreoretinal surgery, perfusion fluid or perfusion gas can be delivered into the eyeball 9 through the branch tube 21 on the catheter 2. The perfusion fluid or perfusion gas enters the catheter 2 through the branch tube 21 and flows into the eyeball 9 along the perfusion channel formed by the catheter 2.

[0052] At this time, the continuous membrane structure of the elastic membrane 8 can maintain the isolation between the injection channel and the chamber 43 during the movement of the optical fiber 1.

[0053] (Fourth embodiment) On the other hand, it is troublesome to hold the shell in your hand throughout the operation, and it is easy to cause fatigue for medical staff. Therefore, it is necessary to ensure that the catheter 2 and fiber optic 1 can still be stably held on the eyeball 9 when the shell is not held in your hand.

[0054] like Figure 7 As shown, in a preferred embodiment: the conduit 2 includes a first tube segment 22 near the eyeball 9, a second tube segment 23 away from the eyeball 9, and a flexible tube segment 24 connecting the first tube segment 22 and the second tube segment 23. The wall thickness of the flexible tube segment 24 is less than the wall thickness of the first tube segment 22 and the second tube segment 23. The flexible tube segment 24 has a continuous lumen extending along the axial direction of the conduit 2, and the optical fiber 1 is inserted into the lumen.

[0055] When the operator holds the first hollow sleeve 4 and operates the second hollow sleeve 5, the second pipe section 23 can move to a certain extent with the first hollow sleeve 4 or the fiber optic drive 3. Since the wall thickness of the flexible pipe section 24 is small, its bending stiffness is significantly lower than that of the first pipe section 22 and the second pipe section 23. Therefore, the movement and force generated by the second pipe section 23 can cause bending deformation at the flexible pipe section 24.

[0056] Therefore, the movement of the second tube segment 23 relative to the first tube segment 22 will not be rigidly transmitted to the first tube segment 22. Even if the operator operates the first hollow sleeve 4 or the second hollow sleeve 5, or places the housing aside, the first tube segment 22 can still be maintained in the predetermined position in the incision of the eyeball 9. At the same time, the optical fiber 1 is inserted into the continuous lumen of the conduit 2 and is fixedly connected to the optical fiber drive 3. Therefore, the axial movement of the optical fiber drive 3 can directly drive the optical fiber 1 to move along the axial direction of the conduit 2, thereby changing the length of the distal end of the optical fiber 1 extending into the eyeball 9.

[0057] This creates a flexible decoupling region in the catheter 2 within the flexible tube segment 24, isolating the adjustment movement of the fiber optic drive 3 on the fiber optic 1 from the movement of the fixed part of the catheter 2 located at the incision site of the eyeball 9. This reduces the physical exertion of medical staff and also reduces the possibility of the catheter 2 being accidentally pulled out when adjusting the insertion depth of the fiber optic 1.

[0058] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of this application, and not 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. All such modifications or substitutions should be covered within the protection scope of this application, and should 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. Therefore, the protection scope of this application should be determined by the protection scope of the claims.

Claims

1. An illumination device for vitreoretinal surgery, characterized in that, include: An optical fiber (1) is provided with an optical fiber connector (11) installed at its near end. The optical fiber connector (11) is used to connect an optical guide. The optical guide is connected to a light source and has an optical output end. The optical fiber (1) receives a light beam transmitted by the optical guide. The catheter (2) is configured to be inserted into an incision in the eyeball (9) and remain in position relative to the eyeball (9), and the distal end of the optical fiber (1) is inserted into the interior of the catheter (2) and is movable along the catheter (2); The fiber optic drive (3) is connected to the conduit (2) and is axially movable relative to the conduit (2), and the fiber optic cable (1) is fixedly connected to the fiber optic drive (3).

2. The illumination device for vitreoretinal surgery according to claim 1, characterized in that, It also includes a housing, the optical fiber (1), the conduit (2) and the optical fiber driver (3) are integrated inside the housing, and the distal end of the conduit (2) is disposed outside the housing; The housing includes: a first hollow sleeve (4), a second hollow sleeve (5), and an elastic support member (6). The first hollow sleeve (4) includes a first cylinder (41) and an end plate (42) at one end. The proximal end of the conduit (2) is fixedly connected to the end plate (42). The fiber optic drive (3) is slidably connected to the first cylinder (41) along the axial direction. The distal end face of the fiber optic drive (3), the end plate (42) and the inner wall of the first cylinder (41) together form an axially extending chamber (43). The second hollow sleeve (5) includes a second cylinder (51) and a knob (52) at one end, with the end face of the second cylinder (51) contacting the near end face of the fiber optic drive (3). The first cylinder (41) is threadedly connected to the second cylinder (51) so that when the second cylinder (51) is rotated in the forward direction, the end face of the second cylinder (51) can push the fiber optic drive (3) to move axially toward the eyeball (9); The elastic support (6) is installed inside the chamber (43). The two ends of the elastic support (6) are connected to the end plate (42) and the near end face of the fiber optic drive (3) so that when the second cylinder (51) is rotated in the opposite direction, the elastic support (6) can push the fiber optic drive (3) to reset.

3. The illumination device for vitreoretinal surgery according to claim 2, characterized in that, The elastic support (6) is a helical spring, which is fitted on the outside of the optical fiber (1) and configured to support the optical fiber (1) when it is subjected to axial load, so as to limit the radial bending of the optical fiber (1) in the cavity (43).

4. The illumination device for vitreoretinal surgery according to claim 3, characterized in that, The outer peripheral surface of the fiber drive (3) is provided with a guide rib (31) extending along the axial direction. The first hollow sleeve (4) is formed with a guide hole (44) extending along the axial direction. The guide hole (44) radially penetrates the first hollow sleeve (4). The guide rib (31) is accommodated in the guide hole (44) to restrict the rotation of the fiber drive (3) relative to the first hollow sleeve (4) and allow the fiber drive (3) to move axially.

5. The illumination device for vitreoretinal surgery according to claim 4, characterized in that, The outer circumferential surface of the first hollow sleeve (4) is provided with an external thread, and the external thread is connected to a nut (7). The guide rib (31) extends to the outside of the first hollow sleeve (4) and can abut against the axial end face of the nut (7) to limit the axial movement range of the fiber drive (3) relative to the first hollow sleeve (4).

6. The illumination device for vitreoretinal surgery according to claim 5, characterized in that, The outer peripheral surface of the first hollow sleeve (4) is also provided with an axially extending groove (45), a portion of the external thread of the first hollow sleeve (4) is cut off by the groove (45), and the bottom wall of the groove (45) is provided with a scale indicating the position of the optical fiber driver (3).

7. The illumination device for vitreoretinal surgery according to claim 3, characterized in that, The cavity (43) is provided with an elastic membrane (8) with a truncated cone cross section. The elastic membrane (8) includes a circular outer periphery and an inner hole. The outer periphery of the elastic membrane (8) is fixed and sealed to the inner wall of the cavity (43), and the inner hole of the elastic membrane (8) is fixed and sealed to the outer wall of the optical fiber (1). The elastic membrane (8) is configured to deform adaptively when the optical fiber (1) moves axially.

8. The illumination device for vitreoretinal surgery according to claim 7, characterized in that, A branch tube (21) is provided on the catheter (2), and the branch tube (21) and the catheter (2) form an infusion channel for delivering infusion fluid or infusion gas into the eyeball (9). The elastic membrane (8) is used to seal and isolate the infusion channel from the chamber (43).

9. The illumination device for vitreoretinal surgery according to claim 2, characterized in that, The conduit (2) includes a first segment (22) near the eyeball (9), a second segment (23) away from the eyeball (9), and a flexible segment (24) connecting the first segment (22) and the second segment (23). The wall thickness of the flexible segment (24) is less than the wall thickness of the first segment (22) and the second segment (23). The flexible segment (24) has a continuous lumen extending along the axial direction of the conduit (2). The optical fiber (1) passes through the lumen.

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