Integrated ophthalmic laser treatment system

Abstract

The invention relates to the technical field of ophthalmological treatment equipment, and discloses an integrated ophthalmological laser treatment system, which comprises a laser treatment light path, an optical steering module and an operating microscope, the laser treatment light path is used for outputting preset treatment laser to perform laser treatment on the eye tissue, outputting first illumination light to the eye tissue to obtain a first imaging light beam, and outputting the first imaging light beam to the optical steering module; the optical steering module is used for shaping the first imaging light beam and transmitting the first imaging light beam to the operating microscope; and the operating microscope is used for switching and outputting the received first imaging light beam and a second imaging light beam of the eye tissue acquired by the operating microscope. According to the invention, one operation microscope can provide corresponding visual imaging according to the requirements of the operation stage, seamless connection in the operation process is realized, the operation process is optimized, and the operation efficiency and safety are improved.

Description

Technical Field

[0001] The present invention relates to the technical field of ophthalmic treatment equipment, and in particular to an integrated ophthalmic laser treatment system. Background Art

[0002] Currently, laser eye treatment surgery includes three main processes: preoperative alignment, refractive treatment and postoperative lens removal.

[0003] During preoperative alignment, existing technologies mostly use real-time screen images to help doctors align the patient's eyes with the treatment system. When operating via a screen, the doctor's gaze needs to switch between the surgical area and the screen, which can lead to difficulties in eye-hand coordination and increase the complexity of the operation. Therefore, screen display technology is not conducive to surgical education and training because it cannot provide the same visual and tactile feedback as actual operation. Compared with binocular vision, it has the following disadvantages:

[0004] Binocular vision enables depth perception through parallax between the left and right eyes, allowing doctors to perceive objects in three-dimensional space. However, screen displays cannot simulate this parallax and typically provide two-dimensional images lacking depth information. This makes it difficult for doctors to perceive the true three-dimensional structure and depth of tissues, affecting surgical precision.

[0005] In laser eye surgery, surgeons prefer to use surgical microscopes because of the stereoscopic vision they provide. Stereoscopic vision is crucial for precise manipulation during surgery. Surgeons need to accurately judge tissue depth, distance, and spatial relationships to avoid damaging surrounding structures. Stereoscopic vision enables surgeons to perceive objects in three dimensions, which is particularly important for the delicate manipulations required during ophthalmic surgery. However, there is currently a lack of systems that can provide the visual imaging required during the various stages of laser eye surgery. Summary of the Invention

[0006] In view of this, the present invention provides an integrated ophthalmic laser treatment system to solve or partially solve the technical problem in the prior art that the visual imaging required for different surgical stages during laser ophthalmic treatment surgery cannot be provided.

[0007] The technical solutions proposed by the present invention are as follows:

[0008] The present invention provides an integrated ophthalmic laser treatment system, comprising: a laser treatment optical path, an optical steering module and a surgical microscope;

[0009] The laser treatment optical path is used to output a preset treatment laser to perform laser treatment on the eye tissue, output a first illumination light to the eye tissue to obtain a first imaging beam, and output the first imaging beam to the optical steering module;

[0010] The optical steering module is used to shape the first imaging beam and transmit the first imaging beam to the surgical microscope;

[0011] The surgical microscope includes a device for switching and outputting the received first imaging beam and the second imaging beam of the eye tissue acquired by the surgical microscope itself.

[0012] Optionally, the surgical microscope includes a microscopic imaging optical path, a first electrically-controlled baffle, a second electrically-controlled baffle, a beam splitter group and an eyepiece group; the microscopic imaging optical path is used to output a second illumination light to the eye tissue to obtain a second imaging beam, and output the second imaging beam of the eye tissue to the beam splitter group; the first electrically-controlled baffle has a first state of not blocking the first imaging beam, and a second state of blocking the first imaging beam; the second electrically-controlled baffle has a third state of not blocking the second imaging beam, and a fourth state of blocking the second imaging beam; the beam splitter group is used to output the received first imaging beam or second imaging beam along a first direction to the eyepiece group.

[0013] Optionally, the optical steering module includes a first light source, a first beam splitter and an optical steering system; the first light source is used to output a first alignment light to the first beam splitter; the first beam splitter is used to transmit the first alignment light to the laser treatment light path, transmit the first alignment light to the eye tissue through the laser treatment light path, and reflect the first imaging light beam obtained by outputting the first illumination light to the eye tissue by the laser treatment light path to the optical steering system; the optical steering system is used to shape the first imaging light beam and transmit the first imaging light beam to the surgical microscope.

[0014] Optionally, the optical steering system includes a chromatic aberration calibration lens group, a marking dividing plate and a beam expanding lens group, which are sequentially arranged along the transmission direction of the first imaging light beam.

[0015] Optionally, the chromatic aberration correction lens assembly is an image-space telecentric lens assembly.

[0016] Optionally, the chromatic aberration correction lens group includes a first lens group, a second lens group and a third lens group arranged in sequence along the transmission direction of the first imaging light beam, the first lens group includes a first cemented lens and a second cemented lens, the second lens group includes a third cemented lens and a first biconcave lens, and the third lens group includes a first biconvex lens, a fourth cemented lens, a fifth cemented lens and a first bimeniscus lens.

[0017] Optionally, the beam expander group includes a fourth lens group and a fifth lens group arranged in sequence along the transmission direction of the first imaging light beam, the fourth lens group includes a first positive meniscus lens and a sixth cemented lens, and the second lens group includes a first negative meniscus lens, a second biconvex lens and a second biconcave lens.

[0018] Optionally, the optical steering system further includes an amplifying lens, which is arranged in front of the chromatic aberration calibration lens group along the transmission direction of the first imaging light beam.

[0019] Optionally, the laser treatment optical path includes a second light source, a laser monitoring module, a fourth light source and a laser three-dimensional scanning and focusing module;

[0020] The second light source is used to output therapeutic laser;

[0021] The laser monitoring module is used to monitor the spectral parameters of the therapeutic laser;

[0022] The fourth light source is used to output a first illumination light toward the eye tissue to obtain a first imaging light beam on the surface of the eye tissue;

[0023] The laser three-dimensional scanning and focusing module includes an optical Z-axis scanner, an optical X / Y-axis scanner, a dichroic mirror and a focusing objective lens arranged in sequence along the transmission direction of the therapeutic laser. The optical Z-axis scanner and the optical X / Y-axis scanner are respectively used to adjust the focal depth position and horizontal position of the focused radiation focus of the therapeutic laser in the eye tissue. The dichroic mirror is used to reflect the therapeutic laser emitted by the optical X / Y-axis scanner to the focusing objective lens. The focusing objective lens is used to focus the therapeutic laser on the eye tissue, wherein the first imaging light beam of the eye tissue is transmitted to the optical steering module through the focusing objective lens and the dichroic mirror in sequence.

[0024] Optionally, the surgical microscope also includes an imaging unit, and the microscopic imaging optical path includes a third light source, a microscope objective and a magnification lens group; the third light source is used to output a second illumination light to the eye tissue to obtain a second imaging beam on the surface of the eye tissue; the microscope objective is used to transmit the second imaging beam to the magnification lens group; the magnification lens group is used to adjust the magnification of the second imaging beam and transmit the second imaging beam to the beam splitter group; the beam splitter group is also used to output the received first imaging beam or second imaging beam along a second direction to the imaging unit, and the imaging unit generates a corresponding image based on the first imaging beam or the second imaging beam.

[0025] The present invention has the following beneficial effects:

[0026] The integrated ophthalmic laser treatment system of the present invention connects the laser treatment light path and the surgical microscope through an optical steering module. During the preoperative alignment stage, the optical steering module is used to output the first imaging light beam of the eye tissue located below the laser treatment light path to the surgical microscope for imaging, thereby assisting the doctor in aligning the patient's eye with the treatment system. Refractive treatment is then performed through the laser treatment light path. After the refractive treatment, the patient's eye tissue is moved below the surgical microscope. At this time, the surgical microscope outputs the second imaging light beam of the eye tissue obtained by itself, thereby enabling a surgical microscope to provide corresponding visual imaging according to the needs of the surgical stage, thereby achieving seamless connection during the operation, optimizing the surgical process, and improving surgical efficiency and safety. BRIEF DESCRIPTION OF THE DRAWINGS

[0027] In order to more clearly express the technical solutions of the embodiments of the present invention, the following briefly introduces the drawings required for describing the embodiments. Obviously, the drawings described below are only some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying any creative work.

[0028] Figure 1 Schematic diagram of the structure of the integrated ophthalmic laser treatment system according to an embodiment of the present invention;

[0029] Figure 2 This is a schematic diagram of the structure of the laser treatment light path in an embodiment of the present invention;

[0030] Figure 3 Schematic diagram of the structure of the surgical microscope in an embodiment of the present invention;

[0031] Figure 4 Schematic diagram of the structure of the optical steering system in an embodiment of the present invention;

[0032] Figure 5 Schematic diagram of the structure of the chromatic aberration calibration lens assembly in an embodiment of the present invention;

[0033] Figure 6 Schematic diagram of the structure of the beam expander assembly in an embodiment of the present invention;

[0034] Figure 7 Schematic diagram of the state of the electric control baffle before the operation according to an embodiment of the present invention;

[0035] Figure 8 Schematic diagram of the state of the electric control baffle when the lens is taken out after surgery in an embodiment of the present invention;

[0036] Description of reference numerals:

[0037] 100, laser treatment optical path; 101, second light source; 102, laser monitoring module; 103, laser 3D scanning and focusing module; 104, fourth light source; 1031, optical Z-axis scanner; 1032, optical X / Y-axis scanner; 1033, dichroic mirror; 1034, focusing objective lens; 200, optical steering module; 201, first light source; 202, first beam splitter; 203, optical steering system; 2031, multiplier lens; 2032, chromatic aberration calibration lens group; 2033, marking dividing plate; 2034, beam expander lens group; a1, first lens group; a2, second lens group; a3, third lens group; a11, first cemented lens; a12, second cemented lens; a21, third cemented lens; a22, first biconcave lens; a31, first biconvex lens; a32, fourth cemented lens; a33, fifth cemented lens; a34, first bimeniscus lens; b1, fourth lens group; b2, fifth lens group; b11, first positive meniscus lens; b12, sixth cemented lens; b21, first negative meniscus lens; b22, second biconvex lens; b23, second biconcave lens; 300, surgical microscope; 301, microscopic imaging optical path; 302, first electrically controlled baffle; 303, second electrically controlled baffle; 304, beam splitter group; 305, eyepiece group; 306, imaging unit; 3011, third light source; 3012, zoom lens group; 3013, microscope objective; 3051, first lens; 3052, second lens; 3061, optical lens; 3062, camera. DETAILED DESCRIPTION

[0038] The technical solution of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the embodiments described are only some embodiments of the present invention, not all embodiments. All other embodiments obtained by ordinary technicians in this field based on the embodiments of the present invention without making any creative efforts shall fall within the scope of protection of the present invention.

[0039] In the description of the present invention, it should be noted that the terms "first", "second", etc. are only used for descriptive purposes and cannot be understood as indicating or implying relative importance.

[0040] In the description of the present invention, it should be noted that, unless otherwise expressly specified or limited, the terms "connected" and "connection" should be understood in a broad sense. For example, it can mean a fixed connection, a detachable connection, or an integral connection; it can mean a mechanical connection or an electrical connection; it can mean a direct connection or an indirect connection through an intermediate medium; it can mean internal communication between two components; it can mean a wireless connection or a wired connection. For those skilled in the art, the specific meanings of the above terms in the present invention can be understood according to the specific circumstances.

[0041] In addition, the technical features involved in the different embodiments of the present invention described below can be combined with each other as long as they do not conflict with each other.

[0042] Binocular vision provides a more natural stereoscopic visual experience, helping to improve surgical precision and safety. Therefore, despite the convenience of screen display technology in some areas, binocular vision remains a crucial reference standard in ophthalmic surgery. However, current laser therapy systems use screen imaging for laser alignment and require lens removal after laser treatment. The lack of binocular vision reduces surgical efficiency and safety.

[0043] In view of this, an embodiment of the present invention provides an integrated ophthalmic laser treatment system suitable for ophthalmic laser surgery, particularly suitable for ophthalmic surgery that requires precise control of three-dimensional scanning of the focused radiation focus to treat the cornea.

[0044] like Figure 1 、 Figure 2 and Figure 3 As shown, the integrated ophthalmic laser treatment system according to an embodiment of the present invention includes: a laser treatment optical path 100 , an optical steering module 200 and a surgical microscope 300 .

[0045] The laser treatment optical path 100 is used to output a preset treatment laser to perform laser treatment on the eye tissue, and output a first illumination light to the eye tissue to obtain a first imaging beam on the surface of the eye tissue, and output the first imaging beam to the optical steering module 200.

[0046] The optical steering module 200 is used to shape the first imaging beam and transmit the first imaging beam to the surgical microscope 300 .

[0047] The surgical microscope 300 is used to switch and output the received first imaging light beam and the second imaging light beam of the eye tissue acquired by the surgical microscope 300 itself.

[0048] The laser treatment light path 100 and the surgical microscope 300 are connected through the optical steering module 200. In the preoperative alignment stage, the optical steering module 200 is used to output the first imaging beam of the eye tissue located below the laser treatment light path 100 to the surgical microscope 300 for imaging, thereby assisting the doctor in aligning the patient's eye with the treatment system. Then, refractive treatment is performed through the laser treatment light path 100. After the refractive treatment, the patient's eye tissue is moved to the bottom of the surgical microscope 300. At this time, the surgical microscope 300 outputs the second imaging beam of the eye tissue obtained by itself, so that one surgical microscope 300 can provide corresponding visual imaging according to the needs of the surgical stage, thereby achieving seamless connection during the operation, optimizing the surgical process, and improving surgical efficiency and safety.

[0049] In some embodiments, the surgical microscope 300 includes a microscopic imaging optical path 301, a first electrically-controlled baffle 302, a second electrically-controlled baffle 303, a beam splitter group 304 and an eyepiece lens group 305. The microscopic imaging optical path 301 is used to output a second illumination light to the eye tissue to obtain a second imaging beam, and output the second imaging beam of the eye tissue to the beam splitter group 304. The first electrically-controlled baffle 302 has a first state of not blocking the first imaging beam, and a second state of blocking the first imaging beam. The second electrically-controlled baffle 303 has a third state of not blocking the second imaging beam, and a fourth state of blocking the second imaging beam. The beam splitter group 304 is used to output the received first imaging beam or second imaging beam along a first direction to the eyepiece lens group 305.

[0050] Specifically, the microscopic imaging optical path 301 is located below the beam splitter assembly 304, and the optical steering module 200 is located to the left of the beam splitter assembly 304. The beam splitter assembly 304 includes two partially transmissive and partially reflective beam splitters, both of which are tilted upward at 45 degrees from left to right. Correspondingly, two eyepiece lens assemblies 305 are also provided to accommodate human eyes, each eyepiece lens assembly 305 including a first lens 3051 and a second lens 3052.

[0051] The first electrically controlled baffle 302 is located to the left of the beam splitter assembly 304, and the second electrically controlled baffle 303 is located below the beam splitter assembly 304. The first electrically controlled baffle 302 and the second electrically controlled baffle 303 are both controlled by a controller to move to switch the states of the first electrically controlled baffle 302 and the second electrically controlled baffle 303. When the first electrically controlled baffle 302 is in the first state, the second baffle is in the fourth state. When the first electrically controlled baffle 302 is in the second state, the second electrically controlled baffle 303 is in the third state, thereby preventing interference between the first imaging beam and the second imaging beam.

[0052] The integrated ophthalmic laser treatment system of the embodiment of the present invention connects the laser treatment optical path 100 and the surgical microscope 300 through the optical steering module 200. In the preoperative alignment stage, the first electrically controlled baffle 302 is controlled to be in the first state and the second electrically controlled baffle 303 is controlled to be in the fourth state. The optical steering module 200 can be used to image the eye tissue below the laser treatment optical path 100 through the eyepiece lens group 305, thereby assisting the doctor in aligning the patient's eye with the treatment system. Then, refractive treatment is performed through the laser treatment optical path 100 while intraoperative observation is performed through the eyepiece lens group 305. After the refractive treatment, the patient's eye tissue is imaged. The patient's eye tissue is moved to the bottom of the eyepiece lens group 305, the first electrically controlled baffle 302 is controlled to the second state, and the second electrically controlled baffle 303 is controlled to the third state, and the surgical microscope 300 is used to assist in removing the corneal lens from the cornea. The optical path switching technology achieved by the optical steering module 200, the first electrically controlled baffle 302 and the second electrically controlled baffle 303 can enable a surgical microscope 300 to provide corresponding visual imaging according to the needs of the surgical stage, complete the preoperative alignment, laser treatment and postoperative lens removal processes, achieve seamless connection during the surgical process, optimize the surgical process, and improve surgical efficiency and safety.

[0053] In some embodiments, the laser treatment optical path 100 includes a second light source 101 , a laser monitoring module 102 , a laser three-dimensional scanning and focusing module 103 , and a fourth light source 104 ;

[0054] The second light source 101 is used to output therapeutic laser;

[0055] The laser monitoring module 102 is used to monitor the spectral parameters of the treatment laser;

[0056] The fourth light source 104 is configured to output a first illumination light to the eye tissue to obtain a first imaging light beam on the surface of the eye tissue;

[0057] The laser three-dimensional scanning and focusing module 103 includes an optical Z-axis scanner 1031, an optical X / Y-axis scanner 1032, a dichroic mirror 1033 and a focusing objective lens 1034, which are arranged in sequence along the transmission direction of the therapeutic laser. The optical Z-axis scanner 1031 and the optical X / Y-axis scanner 1032 are respectively used to adjust the focal depth position and horizontal position of the focused radiation focus of the therapeutic laser in the eye tissue. The dichroic mirror 1033 is used to reflect the therapeutic laser emitted by the optical X / Y-axis scanner 1032 to the focusing objective lens 1034. The focusing objective lens 1034 is used to focus the therapeutic laser on the eye tissue, wherein the first imaging light beam of the eye tissue is transmitted to the optical steering module 200 through the focusing objective lens 1034 and the dichroic mirror 1033 in sequence.

[0058] Specifically, the laser treatment optical path 100 precisely treats the inner surface of transparent eye materials by focused radiation, and the laser treatment optical path 100 includes a device for generating radiation, namely, a second light source 101. The second light source 101 can emit short-pulse-width, high-energy treatment laser light to achieve precise cutting or treatment of transparent materials such as eye tissue.

[0059] The second light source 101 is preferably a femtosecond laser source. The femtosecond pulses emitted by the femtosecond laser source have a spectral center wavelength range of 1000 nm to 1200 nm, a spectral full width at half maximum (FWHM) of less than 100 nm, and a pulse width of 10 fs to 1000 fs. The pulse repetition frequency is between 100 kHz and 20 MHz. The laser monitoring module 102 monitors the spectral parameters of the femtosecond pulses emitted by the source.

[0060] The dichroic mirror 1033 is tilted downward by 45 degrees from left to right, and can reflect the treatment laser and transmit the first imaging laser.

[0061] The focusing objective 1034 is responsible for focusing the therapeutic laser radiation onto a very small focal spot and is designed with a specific numerical aperture and field of view size to ensure consistency and accuracy of the focal spot size throughout the treatment volume, thereby improving the accuracy of the treatment.

[0062] The focus position changing device is composed of the optical Z scanner and the galvanometer systems in the X, Y, and Z directions of the optical X / Y axis scanner 1032 .

[0063] The optical Z scanner includes a movable lens mounted on a high-speed displacement galvanometer mirror for adjusting the focal depth position of the focused radiation focus in the tissue.

[0064] The optical X / Y axis scanner 1032 includes an X / Y scanning mechanism for adjusting the horizontal movement of the focus point of the focused radiation in the tissue.

[0065] By the optical Z scanner and the optical X / Y axis scanner 1032 working together, the position of the laser focus can be accurately changed in three-dimensional space, thereby achieving accurate scanning and processing of the cornea.

[0066] This innovative approach, combining precision optical systems with high-speed, high-precision scanning, is particularly well-suited for ophthalmic surgeries requiring precisely controlled three-dimensional scanning of the focused radiation spot to treat the cornea.

[0067] In some embodiments, the optical steering module 200 includes a first light source 201, a first beam splitter 202 and an optical steering system 203; the first light source 201 is used to output a first alignment light to the first beam splitter 202; the first beam splitter 202 is used to transmit the first alignment light to the laser treatment optical path 100, transmit the first alignment light to the eye tissue through the laser treatment optical path 100, and reflect the first imaging light beam obtained by the laser treatment optical path 100 outputting the first illumination light to the eye tissue to the optical steering system 203; the optical steering system 203 is used to shape the first imaging light beam and transmit the first imaging light beam to the beam splitter group 304 in the surgical microscope 300.

[0068] Specifically, the first light source 201 is a laser diode (LD), and the first alignment light is outputted through the first light source 201 .

[0069] The first beam splitter 202 is arranged to tilt upward from left to right, and partially transmits and reflects the incident light beam, thereby transmitting the first illumination light and reflecting the first imaging light beam.

[0070] The optical steering system 203 assists the surgeon in precisely aligning the patient's ocular tissue with the focusing objective 1034 prior to surgery by transmitting the first imaging beam to the surgical microscope 300. After passing through the focusing objective 1034 and the dichroic mirror 1033, the first imaging beam from the ocular tissue surface is split by the first beam splitter 202. A larger portion of the first imaging beam is reflected by the first beam splitter 202 and then enters the optical steering system 203. The optical steering system 203 reshapes the first imaging beam and transmits it to the beam splitter assembly 304 within the surgical microscope 300 module.

[0071] The preferred optical structure of the optical steering system 203 is in the form of a Keplerian telescope.

[0072] The optical steering system 203 improves the quality and stability of the imaging light beam through shaping processing, providing a clearer imaging effect for the surgical microscope 300.

[0073] In some embodiments, as Figure 4 As shown, the optical steering system 203 includes a chromatic aberration calibration lens group 2032, a mark dividing plate 2033 and a beam expanding lens group 2034, which are sequentially arranged along the transmission direction of the first imaging light beam.

[0074] Specifically, the marking dividing plate 2033 is a transparent plate provided with marking symbols, for example, a cross dividing plate can be used.

[0075] The chromatic aberration correction lens group 2032 and the beam expansion lens group 2034 are used to correct the chromatic aberration and beam expansion of the first imaging beam respectively, so that the first imaging beam matches the clear aperture of the beam splitter group 304 in the surgical microscope 300 and the field of view number of the eyepiece lens group 305.

[0076] Furthermore, the optical steering system 203 further includes an amplifying lens 2031, which is disposed in front of the chromatic aberration calibration lens group 2032 along the transmission direction of the first imaging light beam. The amplifying lens 2031 reduces light beam loss during transmission and improves light beam transmittance.

[0077] Specifically, the first imaging light beam entering the optical steering system 203 first passes through the multiplier lens 2031 tilted at 45° to supplement the light, thereby reducing the light beam deflection introduced after passing through the dichroic mirror 1033, and then passes through the beam expander group 2034 composed of the chromatic aberration correction lens group 2032 and the beam expander group 2034 to realize the shaping of the light beam. A crosshair plate is installed on the real focal plane in the middle of the optical path of the chromatic aberration correction lens group and the beam expander group 2034, which can superimpose the crosshair image with the image formed under the focusing objective lens 1034 and transmit them to the beam splitter group 304 of the surgical microscope 300, thereby improving the positioning accuracy when used by the doctor.

[0078] At this point, the first electrically controlled baffle 302 moves upward, allowing the imaging beam focused on the ocular tissue surface by objective lens 1034 to be shaped by the beam steering system and then enter the microscope eyepiece through beam splitter assembly 304. The second electrically controlled baffle 303 blocks the second imaging light path to prevent stray light from interfering with the alignment of the ocular tissue with the treatment system. Beam splitter assembly 304 splits the first imaging beam into two independent optical paths. These two optical paths pass through the first lens 3051 and the second lens 3052 of the eyepiece assembly 305, respectively, to form an image in the doctor's eye.

[0079] The embodiment of the present invention enables direct observation of the eye tissue under the focusing objective lens 1034 through the eyepiece lens assembly 305 of the surgical microscope 300 before surgery, thereby assisting in the precise alignment of the patient's eye tissue and the focusing objective lens 1034 before surgery.

[0080] The optical path structure of the optical steering system 203 composed of the beam expander lens group 2034 and the chromatic aberration correction lens group adopts an inverted Kepler telescope optical system, that is, an optical path structure in which the beam expander lens group 2034 and the chromatic aberration correction lens group are both positive lens groups. A marking dividing plate 2033 is placed at the overlapping position of the real focal planes of the two groups of lenses. The beam expander lens group 2034 can project the image of the mark formed by the marking dividing plate 2033 into the eyepiece of the surgical microscope 300, thereby improving the accuracy of the alignment process.

[0081] To achieve high-quality stereoscopic vision, it is necessary to ensure the resolution, brightness uniformity, and color matching of the images formed by the beam splitter assembly 304 and entering the two sets of eyepiece lenses 305, ensuring the naturalness and accuracy of the final image. Meanwhile, the light beam formed by the focusing objective lens 1034 is shaped by the optical steering system 203 and then appropriately distributed by the beam splitter assembly into two independent visual imaging optical paths.

[0082] In some embodiments, the chromatic aberration correction lens assembly 2032 is an image-side telecentric lens assembly.

[0083] Specifically, if Figure 5 As shown, the chromatic aberration correction lens group 2032 includes a first lens group a1, a second lens group a2 and a third lens group a3 arranged in sequence along the transmission direction of the first imaging light beam, the first lens group a1 includes a first cemented lens a11 and a second cemented lens a12, the second lens group a2 includes a third cemented lens a21 and a first biconcave lens a22, and the third lens group a3 includes a first biconvex lens a31, a fourth cemented lens a32, a fifth cemented lens a33 and a first bimeniscus lens a34.

[0084] The chromatic aberration correction lens assembly 2032 includes a combination of multiple lens groups and cemented lenses. Through precise optical design and material selection, the chromatic aberration correction capability of the light beam is further optimized, while the transmission efficiency and imaging quality of the light beam are improved.

[0085] In one example, the design band of the focusing objective lens 1034 is the near-infrared band of 1050nm±50nm, so the design requirement of the chromatic aberration correction lens group is to correct the uncorrected chromatic aberration of the visible light band of the focusing objective lens 1034 (486nm-656nm) and achieve better imaging quality on the real image plane.

[0086] When not connected to the surgical microscope 300 , the optical steering system 203 can be connected to the camera 3062 and used alone as an imaging tube lens for observing the focusing lens 1034 , so as to observe the image below the focusing lens 1034 through the display.

[0087] When connected to surgical microscope 300, the chromatic aberration correction lens assembly has already corrected the chromatic aberration of the objective lens. This eliminates the need to consider chromatic aberration correction for the near-infrared band when splicing beam expander assembly 2034, thus reducing the design difficulty and complexity of the system. Furthermore, the chromatic aberration correction lens assembly utilizes an image-space telecentric optical path, simplifying the splicing of the two lens assemblies and the installation and commissioning of the crosshair plate.

[0088] In some embodiments, as Figure 6As shown, the beam expander group 2034 includes a fourth lens group b1 and a fifth lens group b2 arranged in sequence along the transmission direction of the first imaging light beam. The fourth lens group b1 includes a first positive meniscus lens b11 and a sixth cemented lens b12. The second lens group a2 includes a first negative meniscus lens b21, a second biconvex lens b22 and a second biconcave lens b23.

[0089] The beam expander group 2034 adopts a combination of a positive meniscus lens, a negative meniscus lens, a double convex lens and a double concave lens. By splicing the beam expander group 2034 and the chromatic aberration correction group, the first imaging light beam of the focusing objective lens 1034 can be shaped into a light beam that matches the aperture of the beam splitter group, and the field of view angle of the light beam matches the eyepiece group of the surgical microscope 300, so as to achieve the effect of observing a complete imaging field of view and uniform field brightness in the eyepiece group.

[0090] Optionally, the microscopic imaging optical path 301 includes a third light source 3011, a microscope objective 3013 and a magnification lens group 3012; the third light source 3011 is used to output a second illumination light to the eye tissue; the microscope objective 3013 is used to transmit the second imaging beam to the magnification lens group 3012; the magnification lens group 3012 is used to adjust the magnification of the second imaging beam and transmit the second imaging beam to the beam splitter group 304.

[0091] Specifically, if Figure 7 and Figure 8 As shown, after the ophthalmic laser ablation procedure is completed, that is, after the laser treatment is concluded, the operating table moves, positioning the patient's ocular tissue beneath the microscope objective 3013 of the surgical microscope 300. During the movement of the operating table, the first electrically controlled baffle 302 is controlled to move downward, blocking the first imaging light path. The second electrically controlled baffle 303 moves leftward to unblock the second imaging light path. Simultaneously, the third light source 3011 is activated. This allows a single microscope to provide visual imaging tailored to the needs of the surgical stage, achieving seamless functional integration throughout the surgical process. After the operating table has completed its movement, the zoom module can be adjusted to set the appropriate magnification of the surgical microscope 300. The microscope objective 3013 images the patient's ocular tissue after the ablation. After passing through the zoom module, the image enters the beam splitting module and then passes through the eyepiece assembly 305, resulting in an image formed in the surgeon's binocular vision. Binocular vision enhances the surgeon's visual depth perception, precisely assisting the surgeon in removing the corneal lens from the patient's cornea.

[0092] Furthermore, the surgical microscope 300 also includes an imaging unit 306, and the beam splitter group 304 is further used to output the received first imaging beam or second imaging beam to the imaging unit 306 along the second direction, and the imaging unit 306 generates a corresponding image based on the first imaging beam or the second imaging beam.

[0093] The imaging unit 306 includes an optical lens 3061 and a camera 3062. The optical lens 3061 focuses the first imaging beam or the second imaging beam onto the camera 3062. The image is formed by the camera 3062 and displayed on the screen, so that the surgical microscope 300 can not only observe eye tissue in real time, but also generate high-quality digital images, which is convenient for surgical records, remote consultation and postoperative analysis.

[0094] This embodiment of the present invention connects the laser treatment optical path 100 and the surgical microscope 300 via an optical steering module 200. This allows the surgeon to use the surgical microscope 300 to directly observe the patient's ocular tissue beneath the treatment system during preoperative alignment. The binocular stereoscopic vision technology provided by the surgical microscope 300 enables the surgeon to accurately perceive tissue depth, distance, and spatial relationships in three dimensions. This feature greatly assists the surgeon in achieving precise alignment between the patient's eye and the treatment system during surgery, improving both surgical accuracy and safety.

[0095] After the laser treatment procedure, the first and second electrically controlled baffles 302 and 303 are controlled to switch the optical path of the surgical microscope 300, based on the treatment software process or the operating table's travel position on the guide rails. The illumination light source is then controlled to fully illuminate the active optical path. The same surgical microscope 300 module is then used to assist the surgeon in removing the lens from the cornea and correcting myopia. This optical path switching technology provides the necessary visual imaging at different surgical stages, enabling seamless transitions throughout the procedure and optimizing the surgical workflow.

[0096] Although example embodiments and their advantages have been described in detail, those skilled in the art may make various changes, substitutions and modifications to these embodiments without departing from the spirit and scope of protection of the present invention, and such modifications and variations are all within the scope defined therein.

Claims

1. An integrated ophthalmic laser treatment system, characterized in that: include: Laser therapy optical path, optical steering module and surgical microscope; The laser treatment optical path is used to output a preset treatment laser to perform laser treatment on the eye tissue, output a first illumination light to the eye tissue to obtain the first imaging beam, and output the first imaging beam to the optical steering module; The optical steering module is used to shape the first imaging beam and transmit the first imaging beam to the surgical microscope; The surgical microscope is used for switching and outputting the received first imaging light beam and the second imaging light beam of the eye tissue acquired by the surgical microscope itself.

2. The integrated ophthalmic laser treatment system according to claim 1, characterized in that: The surgical microscope comprises a microscopic imaging optical path, a first electrically controlled baffle, a second electrically controlled baffle, a beam splitter assembly and an eyepiece assembly; The microscopic imaging optical path is used to output a second illumination light to the eye tissue to obtain the second imaging beam, and output the second imaging beam of the eye tissue to the beam splitter group; The first electrically controlled baffle has a first state in which it does not block the first imaging light beam, and a second state in which it blocks the first imaging light beam; The second electrically controlled baffle has a third state in which it does not block the second imaging light beam, and a fourth state in which it blocks the second imaging light beam; The beam splitter group is used to output the received first imaging light beam or the second imaging light beam to the eyepiece group along a first direction.

3. The integrated ophthalmic laser treatment system according to claim 1, characterized in that: The optical steering module includes a first light source, a first beam splitter and an optical steering system; The first light source is used to output a first alignment light to the first beam splitter; The first beam splitter is used to transmit the first alignment light to the laser treatment optical path, transmit the first alignment light to the eye tissue through the laser treatment optical path, and reflect the first imaging light beam obtained by outputting the first illumination light to the eye tissue by the laser treatment optical path to the optical steering system; The optical steering system is used to shape the first imaging beam and transmit the first imaging beam to the surgical microscope.

4. The integrated ophthalmic laser treatment system according to claim 3, characterized in that: The optical steering system includes a chromatic aberration calibration lens group, a marking dividing plate and a beam expanding lens group which are sequentially arranged along the transmission direction of the first imaging light beam.

5. The integrated ophthalmic laser treatment system according to claim 4, characterized in that: The chromatic aberration correction lens group is an image-side telecentric lens group.

6. The integrated ophthalmic laser treatment system according to claim 5, characterized in that: The chromatic aberration correction lens group includes a first lens group, a second lens group and a third lens group arranged in sequence along the transmission direction of the first imaging light beam, the first lens group includes a first cemented lens and a second cemented lens, the second lens group includes a third cemented lens and a first biconcave lens, and the third lens group includes a first biconvex lens, a fourth cemented lens, a fifth cemented lens and a first bimeniscus lens.

7. The integrated ophthalmic laser treatment system according to claim 6, characterized in that: The collimator group includes a fourth lens group and a fifth lens group arranged in sequence along the transmission direction of the first imaging light beam, the fourth lens group includes a first positive meniscus lens and a sixth cemented lens, and the second lens group includes a first negative meniscus lens, a second biconvex lens and a second biconcave lens.

8. The integrated ophthalmic laser treatment system according to claim 4, characterized in that: The optical steering system further includes an amplifying lens, which is arranged in front of the chromatic aberration correction lens assembly along the transmission direction of the first imaging light beam.

9. The integrated ophthalmic laser treatment system according to claim 1, characterized in that: The laser treatment optical path includes a second light source, a laser monitoring module, a fourth light source and a laser three-dimensional scanning and focusing module; The second light source is used to output therapeutic laser; The laser monitoring module is used to monitor the spectral parameters of the therapeutic laser; The fourth light source is used to output a first illumination light to the eye tissue to obtain a first imaging light beam on the surface of the eye tissue; The laser three-dimensional scanning and focusing module includes an optical Z-axis scanner, an optical X / Y-axis scanner, a dichroic mirror and a focusing objective lens arranged in sequence along the transmission direction of the therapeutic laser. The optical Z-axis scanner and the optical X / Y-axis scanner are respectively used to adjust the focal depth position and horizontal position of the focused radiation focus of the therapeutic laser in the eye tissue. The dichroic mirror is used to reflect the therapeutic laser emitted by the optical X / Y-axis scanner to the focusing objective lens. The focusing objective lens is used to focus the therapeutic laser onto the eye tissue. The first imaging light beam of the eye tissue is transmitted to the optical steering module through the focusing objective lens and the dichroic mirror in sequence.

10. The integrated ophthalmic laser treatment system according to claim 2, characterized in that: The surgical microscope further comprises an imaging unit, and the microscopic imaging optical path comprises a third light source, a microscopic objective lens, and a zoom lens group; The third light source is used to output the second illumination light to the eye tissue to obtain a second imaging light beam on the surface of the eye tissue; The microscope objective lens is used to transmit the second imaging light beam to the zoom lens group; The zoom lens group is used to adjust the magnification of the second imaging light beam and transmit the second imaging light beam to the beam splitter group; The beam splitter group is further configured to output the received first imaging beam or the second imaging beam to the imaging unit along a second direction, and the imaging unit generates a corresponding image based on the first imaging beam or the second imaging beam.

Images