Surgical microscope system and surgical microscope

Abstract

A surgical microscope system and a surgical microscope. The surgical microscope system includes a microscope imaging module (01) and an illumination module (02). The microscope imaging module (01) includes an objective lens (11) provided along the principal optical axis (L1), a dichroic beam splitter (12), a variable magnification unit (13), a beam splitter (14), a lens barrel (15), and an eyepiece lens group (16). The illumination module (02) includes a coaxial illumination unit (21) and an angled illumination unit (22). The coaxial illumination unit (21) includes a first light source (211) and a first field stop (212). The first field stop (212) is disposed between the first light source (211) and the dichroic beam splitter (12). The coaxial illumination light rays emitted from the first light source (211) pass through the first field stop (212), are reflected by the dichroic beam splitter (12), pass through the objective lens (11), and reach the surface to be observed (M) along the direction of the principal optical axis (L1), forming a first light spot. The angled illumination light rays emitted from the angled illumination unit (22) are reflected by the dichroic beam splitter (12), pass through the objective lens (11), and reach the surface to be observed (M) along a direction forming a predetermined angle with respect to the principal optical axis (L1), forming a second light spot. The size of the first light spot is adjustable.

Description

Technical Field

[0001] This application claims priority based on Chinese Patent Application No. 202211587632.3 filed with the Chinese Patent Office on December 12, 2022, and incorporates all the contents of the said application by reference into this application.

[0002] The present disclosure relates to the fields of optical technology and surgical microscope technology, and relates to, for example, a surgical microscope system and a surgical microscope applicable to an ophthalmic surgery scenario.

Background Art

[0003] Conventional surgical microscopes have relatively simple functions, and the reference data and images provided for surgeons during surgery are not rich and sufficient. Therefore, it is very difficult for an ophthalmologist to observe the fine parts of a patient's eye using a conventional surgical microscope during ophthalmic surgery.

Summary of the Invention

Problems to be Solved by the Invention

[0004] For example, vitreoretinal surgery in ophthalmic surgery basically relates to vitrectomy (removing the vitreous from the posterior chamber to access the retina), and in order to succeed in vitrectomy, it is necessary to completely remove the vitreous from the posterior chamber, including removing a very difficult area near the bottom of the vitreous. Since the vitreous has a transparent property, it is very difficult to perform vitrectomy only with a conventional surgical microscope.

Means for Solving the Problems

[0005] The present disclosure provides a surgical microscope system and a surgical microscope applicable to, for example, an ophthalmic surgery scenario.

[0006] A first aspect of the present disclosure provides a surgical microscope system comprising a microscope imaging module and an illumination module. The microscope imaging module includes an objective lens provided along the principal optical axis, a dichroic beam splitter, a variable magnification unit, a beam splitter, a lens barrel, and an eyepiece lens group. The light rays radiated from the surface of the object to be observed pass through the objective lens, the dichroic beam splitter, and the variable magnification unit in sequence, and then are split into a first beam and a second beam by the beam splitter. The first beam passes through the lens barrel and the eyepiece lens group in sequence along the principal optical axis and is configured to be observed by an observer. The microscope imaging module further includes an image acquisition unit located in the propagation path of the second beam and configured to acquire a surgical image. The first beam and the second beam have different propagation directions. The illumination module includes a coaxial illumination unit and an angled illumination unit. Both the coaxial illumination unit and the angled illumination unit are located on the side of the dichroic beam splitter facing the objective lens. The coaxial illumination unit includes a first light source and a first field stop. The first field stop is disposed between the first light source and the dichroic beam splitter. The coaxial illumination light rays radiated from the first light source pass through the first field stop, are reflected by the dichroic beam splitter, pass through the objective lens, and reach the surface of the object to be observed along the direction of the principal optical axis, forming a first light spot. The angled illumination light rays radiated from the angled illumination unit are reflected by the dichroic beam splitter, pass through the objective lens, and reach the surface of the object to be observed along a direction forming a predetermined angle with respect to the principal optical axis, forming a second light spot. The size of the first light spot is adjustable.

[0007] The second aspect of the present disclosure further provides a surgical microscope including the surgical microscope system according to any one of the embodiments of the first aspect of the present disclosure.

Brief Description of the Drawings

[0008]

Figure 1

Figure 2

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DETAILED DESCRIPTION OF THE INVENTION

[0009] Hereinafter, with reference to the accompanying drawings in the embodiments of the present disclosure, the technical content of the present disclosure will be described in a specific embodiment. The described embodiments are part of the embodiments of the present disclosure.

[0010] In some embodiments, in order to solve the problem that the functions of a conventional surgical microscope are relatively simple, OCT imaging is further provided for ophthalmic surgery. However, in this embodiment, OCT imaging is only applicable before surgery and cannot be provided during surgery in combination with a surgical microscope, so there are limitations in assisting ophthalmologists.

[0011] In some embodiments, the operating microscope applied to ophthalmic surgery has an illumination module including a coaxial illumination unit and an angled illumination unit. The angled illumination unit, also referred to as the field illumination unit, can provide illumination at different angles during the use of the operating microscope to provide ambient illumination light required for the entire surgical site. The coaxial illumination unit, also referred to as the 0° illumination unit, can provide background illumination light for the surgical area, which is restricted by the pupil area of the lens itself and has a decisive meaning for cataract surgery, thus ensuring the basic requirements of an optimal illumination system in cataract surgery. That is, the background illumination light of the surgical area needs to have a uniform red light reflection, and at the same time, a good contrast of the red light reflection is required. The coaxial illumination unit can preferably meet this requirement. However, in some embodiments related to the related art, the size of the fundus spot (also referred to as the fundus light spot) by the coaxial illumination unit cannot be adjusted.

[0012] By the way, in cataract surgery, if there are only very small diseases in the patient's fundus or the fundus is generally small at home (for example, when the patient is a child, the fundus is generally small), a closer fundus spot can provide better contrast. Furthermore, in cataract surgery, in the case of relatively thick cataracts, the "red light reflection" may be too dark. Therefore, increasing the brightness of the fundus by increasing the size of the fundus spot is extremely beneficial for cataract surgery.

[0013] Furthermore, in some embodiments of the related art, the coaxial illumination unit and the angled illumination unit in the illumination module of the operating microscope applied to ophthalmic surgery cannot be operated simultaneously and can only be operated individually.

[0014] However, in ophthalmic surgery, there may be a need to expand the visual field to facilitate the surgery or for the assistant to assist the surgeon in processing the peripheral part of the eyeball. In such cases, it is necessary to operate the coaxial illumination unit and the angled illumination unit simultaneously.

[0015] Thus, in order to better accommodate the needs of surgery, particularly ophthalmic surgery, in some embodiments of the present disclosure, an OCT imaging module is added to the surgical microscope so that OCT imaging can be used not only before ophthalmic surgery but also during ophthalmic surgery. In some other embodiments of the present disclosure, furthermore, the illumination module in the surgical microscope is improved so that the size of the light spot formed on the fundus by the coaxial illumination unit can be adjusted. In some other embodiments of the present disclosure, furthermore, the illumination module in the surgical microscope is improved so that the coaxial illumination unit and the angled illumination unit can be operated not only individually but also simultaneously.

[0016] FIG. 1 is a schematic diagram of a surgical microscope system applied to ophthalmic surgery according to an embodiment of the present disclosure. As shown in FIG. 1, an embodiment of the present invention provides a surgical microscope system applicable during medical ophthalmic surgery, and the surgical display mirror system includes a microscope imaging module 01 and an illumination module 02. The microscope imaging module 01 includes an objective lens 11 provided from an object plane to an image plane along a main optical axis L1, a dichroic beam splitter 12, a variable magnification unit 13, a beam splitter 14, a lens barrel 15, and an eyepiece lens group 16. The light rays emitted from the observed object surface M pass through the objective lens 11, the dichroic beam splitter 12, and the variable magnification unit 13 in sequence, and then are split into a first beam S3 and a second beam S4 by the beam splitter 14. The first beam S3 passes through the lens barrel 15 and the eyepiece lens group 16 in sequence along the main optical axis L1 and is arranged to be observed by an observer. The microscope imaging module 01 further includes an image acquisition unit 17 located on the propagation path of the second beam S4 to acquire a surgical image. The first beam S3 and the second beam S4 have different propagation directions. The illumination module 02 includes a coaxial illumination unit 21 and an angled illumination unit 22. Both the coaxial illumination unit 21 and the angled illumination unit 22 are located on the side facing the objective lens 11 of the dichroic beam splitter 12. The coaxial illumination unit 21 includes a first light source 211, a first field stop 212, and a first illumination lens group 214. The first field stop 212 is arranged between the first light source 211 and the dichroic beam splitter 12 and between the first light source 211 and the first illumination lens group 214. When the coaxial illumination unit 21 further includes a fundus function lens 213, the first field stop 212 is arranged between the fundus function lens 213 and the first illumination lens group 214.The coaxial illumination light beam S1 emitted from the first light source 211 passes through the first field stop 212 and the first illumination lens group 214, is reflected by the dichroic beam splitter 12, then passes through the objective lens 11, reaches the surface M to be observed along the direction of the principal optical axis L1, forms a first light spot (fundus spot) with an adjustable size, and the angular illumination light beam S2 emitted from the angular illumination unit 22 is reflected by the dichroic beam splitter 12, then passes through the objective lens 11, and reaches the surface M to be observed along the direction forming a predetermined angle (for example, 5° - 7°) with respect to the principal optical axis L1, forming a second light spot.

[0017] In an embodiment of the present disclosure, the microscope imaging module 01 is arranged to magnify and image the eye to be observed, the illumination module 02 is arranged to provide illumination in the optical path of the surgical microscope system, and the surface M to be observed may be the object surface where the retina of the eye to be observed is located. With the principal optical axis L1 of the microscope imaging module 01 as a reference, the microscope imaging module 01 includes an objective lens 11, a dichroic beam splitter 12, a variable magnification unit 13, a beam splitter 14, a first reflection mirror 18, a lens barrel 15, and an eyepiece lens group 16 that are sequentially provided from the object surface to the image surface along the principal optical axis L1. The variable magnification unit 13 may be arranged to adjust the size of the display image of the surface M to be observed observed by the eyepiece lens group 16. The illumination module 02 is arranged in the display mirror system to use both coaxial illumination and / or angular illumination for the eye to be observed. Coaxial illumination means that the illumination light beam is parallel to the principal optical axis L1, and angular illumination means that the illumination light beam forms an angle with the principal optical axis L1. For example, the angle can be 5° - 7°.

[0018] Exemplarily, as shown in FIG. 1, both the coaxial illumination unit 21 and the angled illumination unit 22 may be arranged on the side facing the objective lens 11 of the dichroic beam splitter 12. The first light source 211 may be a white light source and is arranged to emit coaxial illumination light rays S1. A first field stop 212 is provided between the first light source 211 and the dichroic beam splitter 12. By setting the central optical axis of the coaxial illumination light rays S1 emitted from the first light source 211 to be irradiated onto the overlapping region between the dichroic beam splitter 12 and the principal optical axis L1, the coaxial illumination light rays S1 are reflected by the dichroic beam splitter 12 and then propagate along the principal optical axis L1, pass through the objective lens 11, reach the surface M to be observed, and form a first light spot. According to the size of the fundus of different patients and / or the size of the lesion area in the fundus, in order to meet different illumination needs, the size of the first light spot can be adjusted by adjusting the size of the light-transmitting hole of the first field stop 212.

[0019] In the embodiments of the present disclosure, since the size of the light spot formed on the fundus by the coaxial illumination unit is adjustable, in cataract surgery, when there is only a very small disease in the patient's fundus or when the patient's fundus is relatively small, the surgery can be facilitated by making the fundus spot smaller to obtain better contrast. In cataract surgery, when the "red light reflex" is too dark due to the relatively thick cataract, the cataract surgery can be facilitated by adjusting the fundus spot larger to increase the brightness of the fundus.

[0020] In an embodiment of the present disclosure, the angular illumination light beam S2 emitted from the angular illumination unit 22 is irradiated so as to deviate from the overlapping region between the dichroic beam splitter 12 and the principal optical axis L1. After being reflected by the dichroic beam splitter 12, it passes through the objective lens 11 and reaches the surface M to be observed along a direction forming a predetermined angle with the principal optical axis L1, forming a second light spot. In an embodiment of the present disclosure, by adjusting the position and orientation of the angular illumination unit 22, the propagation direction of the angular illumination light beam S2 after being reflected by the dichroic beam splitter 12 and passing through the objective lens 11, and the propagation direction of the coaxial illumination light beam S1 after being reflected by the dichroic beam splitter 12 and passing through the objective lens 11, the angle therebetween can be set to 5° to 7°. Thereby, the diameter of the field illumination light spot is increased so as to illuminate the eye to be observed in a large field of view, and the illumination needs for ophthalmic surgery can be satisfied.

[0021] In an embodiment of the present disclosure, the eyepiece lens group 16 may be a 10 - magnification lens group composed of a single lens and a double - cemented lens group. The surgical microscope consists of two imaging eyepieces for the left and right eyes, and the two imaging eyepieces for the left and right eyes are symmetrically arranged. The microscope imaging module 01 further includes a first reflection mirror 18. As shown in FIG. 1, the first reflection mirror 18 is located between the beam splitter 14 and the lens barrel 15 and may be arranged to adjust the propagation direction of the light beam in order to meet the observation needs of an observer (for example, an ophthalmologist).

[0022] A part of the light rays reflected by the observed surface M enters the display mirror system from the objective lens 11 along the direction of the principal optical axis L1, passes through the dichroic beam splitter 12 and the variable magnification unit 13 in sequence, and then is split into a first beam S3 and a second beam S4 by the beam splitter 14. The first beam S3 passes through the first reflection mirror 18, the lens barrel 15, and the eyepiece lens group 16 along the principal optical axis L1 in sequence, allowing the surgeon to observe the patient's eye. The second beam S4 reaches the image acquisition unit 17 along the other propagation direction, generating a surgical image within the field of view of the surgical display mirror for intraoperative observation and postoperative archiving. When the angle between the dichroic beam splitter 12 and the principal optical axis L1 is an acute angle α, and the coaxial illumination unit 21 and the angled illumination unit 22 are fixedly arranged, by adjusting the magnitude of α, the contact surface between the angled illumination light ray S2 and the dichroic beam splitter 12 is changed, so that the magnitude of the angle between the angled illumination light ray S2 refracted by the objective lens 11 and the principal optical axis L1 can be adjusted. Exemplarily, by increasing the angle α, the diameter of the second light spot can be increased, and the field of view range of the angled illumination can be widened. By decreasing the angle α, the diameter of the second light spot can be decreased, and the field of view range of the angled illumination can be narrowed. By adjusting the field of view range of the angled illumination, the requirements for the surgical field of view range can be met.

[0023] According to an embodiment of the present disclosure, in a surgical microscope system, the fundus spot (for example, the above-mentioned first light spot) formed by the coaxial illumination unit of the illumination module is set as an adjustable light spot, which can meet different ophthalmic surgical scenarios and reduce the difficulty of ophthalmic surgery. In a surgical microscope system, by changing the tilt angle of the dichroic beam splitter with respect to the system principal optical axis, the size of the field illumination light spot (for example, the above-mentioned second light spot) formed by the angled illumination unit in the illumination module can be adjusted. Therefore, in order to facilitate the surgery, according to different ophthalmic surgical scenarios, a field illumination range that meets different surgical requirements can be obtained.

[0024] Figures 2 to 4 are schematic diagrams of three types of first field stops according to embodiments of the present disclosure.

[0025] In an embodiment of the present disclosure, the first field stop 212 is provided with a plurality of light-transmitting holes O of different sizes, and different light-transmitting holes O of the first field stop 212 can be selected to form first light spots of different sizes.

[0026] In an embodiment of the present disclosure, since the first field stop 212 is provided with a plurality of light-transmitting holes O of different diameters, for different surgical scenarios, in order to adjust the size of the fundus spot of the subject to be examined, by selecting light-transmitting holes O of different diameters, the intensity (brightness) and uniformity of the "red light reflex" can be affected. The red light reflex test is used to examine abnormalities in the posterior part of the eye and turbidity of the visual axis, such as cataracts and corneal opacities. The larger the diameter of the fundus spot formed by illumination, the more uniform and brighter the "red light reflex". On the contrary, the smaller the diameter of the fundus spot formed by illumination, the better the contrast of the "red light reflex". When the surgical microscope system needs to use only coaxial illumination, turn on the first light source 211, select a light-transmitting hole O with an appropriate diameter according to the size of the patient's fundus, and the coaxial illumination light beam S1 emitted from the first light source 211 passes through the light-transmitting hole O and is then reflected by the dichroic beam splitter 12, passes through the objective lens 11, reaches the eye to be observed, forms a first light spot of a size corresponding to the fundus, and can perform the function of controlling the size of the illumination light spot on the fundus.

[0027] In an embodiment of the present disclosure, the first field stop 212 can have various forms. In one possible embodiment, as shown in FIG. 2, the first field stop 212 may be a first disk-shaped stop 2121. The centers of a plurality of light-transmitting holes O with different sizes provided in the first disk-shaped stop 2121 are all located on the same circumference centered on the center of the first disk-shaped stop 2121. After rotating the first field stop 212 to move any one of its light-transmitting holes O to the coaxial illumination optical path, the principal axis of the coaxial illumination light beam S1 emitted from the first light source 211 can be perpendicular to the plane where the light-transmitting hole O is located and accurately pass through the center of the light-transmitting hole O, thereby achieving the purpose of accurate positioning and easy adjustment.

[0028] Exemplarily, as shown in FIG. 2, light-transmitting holes O with different diameters are provided in each of the four quadrants of the circular first field stop 212. The centers of the four light-transmitting holes O are distributed in the ∠45° direction in the corresponding quadrants and are also located on the same circumference centered on the center of the first field stop 212. During use, the first field stop 212 can rotate 45°, 135°, 225°, and 270° around an axis perpendicular to the surface of the first field stop 212 and passing through the center of the first field stop 212 so as to move different light-transmitting holes O to the coaxial illumination optical path. After moving any one of the light-transmitting holes O of the first field stop 212 to the coaxial illumination optical path, the principal axis of the coaxial illumination light beam S1 emitted from the first light source 211 can be perpendicular to the plane where the light-transmitting hole O is located and accurately pass through the center of the light-transmitting hole O. The user can select the size of the light-transmitting hole O of the first field stop 212 according to the size of the patient's fundus, which is beneficial to improving the contrast of microscope imaging.

[0029] Alternatively, in another possible embodiment, as shown in FIG. 3, the first field stop 212 may be a rectangular stop 2122. The centers of a plurality of light-transmitting holes O with different sizes provided in the rectangular stop 2122 are located on the same straight line. By pushing the first field stop 212, after moving any one of the light-transmitting holes O to the coaxial illumination optical path, the main optical axis of the coaxial illumination light beam S1 emitted from the first light source 211 is perpendicular to the plane where the light-transmitting hole O is located, and accurately passes through the center of the light-transmitting hole O, so that the purpose of accurate positioning and easy adjustment can be achieved.

[0030] Exemplarily, the rectangular first field stop 212 shown in FIG. 3 is provided with four light-transmitting holes O with different sizes in sequence along its long side direction. During use, by pushing the first field stop 212 along the long side direction of the first field stop 212, the light-transmitting hole O that meets the surgical needs can be pushed into the coaxial illumination optical path. In this embodiment, after moving any one of the light-transmitting holes O of the rectangular first field stop 212 to the coaxial illumination optical path, the main optical axis of the coaxial illumination light beam S1 emitted from the first light source 211 is perpendicular to the plane where the light-transmitting hole O is located, and can accurately pass through the center of the light-transmitting hole O. The user can select the size of the light-transmitting hole O of the first field stop 212 according to the size of the patient's fundus, which is beneficial to improving the contrast of microscope imaging.

[0031] Alternatively, in another possible embodiment, as shown in FIG. 4, the first field stop 212 may include a plurality of second disc-shaped stops 2123. The plurality of second disc-shaped stops 2123 are provided in a folded manner. Each of the second disc-shaped stops 2123 is provided with one light-transmitting hole O. Different second disc-shaped stops 2123 are provided with light-transmitting holes O with different sizes. In the folded state, the centers of the plurality of light-transmitting holes O corresponding to the plurality of second disc-shaped stops 2123 are located on the same axis.

[0032] Exemplarily, as shown in FIG. 4, each second disc-shaped aperture 2123 is provided with one light-transmitting hole O, the sizes of the plurality of light-transmitting holes O are different, the plurality of second disc-shaped apertures 2123 are provided in a folded manner, and the centers of the plurality of light-transmitting holes O corresponding to the plurality of second disc-shaped apertures 2123 are located on the same axis in the folded state. During use, the second disc-shaped aperture 2123 required for the operation is selected from the first field stop 212, the selected second disc-shaped aperture 2123 is moved to the coaxial illumination optical path, and the unselected second disc-shaped apertures 2123 are folded to reduce the space occupation. After operating the first field stop 212 to move any one of the light-transmitting holes O to the coaxial illumination optical path, the main optical axis of the coaxial illumination light beam S1 emitted from the first light source 211 is made perpendicular to the plane where the light-transmitting hole O is located and accurately passes through the center of the light-transmitting hole O, so that the purpose of accurate positioning and easy adjustment can be achieved. The user can select the size of the light-transmitting hole O of the first field stop 212 according to the size of the patient's fundus, which is beneficial to improving the contrast of microscope imaging.

[0033] Continuing to refer to FIG. 1, a first lens group 151 and a second lens group 152 are provided in the lens barrel 15. The first lens group 151 including the meniscus lens is located at the end close to the eyepiece lens group 16 of the lens barrel 15, and the second lens group 152 including the cemented lens is located on the side close to the variable magnification unit 13 of the lens barrel 15.

[0034] Exemplarily, the first lens group 151 and the second lens group 152 are respectively provided at both ends of the lens barrel 15. The first lens group 151 provided at the end close to the eyepiece lens group 16 is a meniscus lens. The meniscus lens may be a negative meniscus lens with the convex surface facing the eyepiece lens group 16, and can converge the light rays emitted from the variable magnification unit 13 to reduce the spherical aberration of the imaging optical path of the microscope. Further, the design of the meniscus lens contributes to reducing the numerical aperture (NA) of the variable magnification unit 13 and the lens barrel 15, reducing the size of the entire device, and further reducing the proportion of the surgical microscope occupying the surgical space. The second lens group 152 provided at the end close to the variable magnification unit 13 employs a cemented lens, eliminates the reflection loss on both surfaces of the lens, prevents total internal reflection in the air gap, and can easily correct the off-axis image quality and the axial chromatic aberration. Exemplarily, the focal length of the second lens group 152 can be set to 170 mm so as to contribute to compressing the light rays entering the eyepiece lens group 16.

[0035] NA is the product of the sine of half of the aperture angle (2β) of the medium between the lens and the object to be observed and the refractive index (n), and is expressed by the formula NA = n * sinβ. The aperture angle is also referred to as the "angular aperture" and is the angle formed by the object point on the optical axis of the lens and the effective diameter of the lens in front of the objective lens. The larger the aperture angle, the larger the light beam incident on the lens, which is proportional to the effective diameter of the lens and inversely proportional to the distance from the focus.

[0036] FIG. 5 is a schematic diagram of a fundus function lens according to an embodiment of the present disclosure.

[0037] As shown in FIG. 5, the coaxial illumination unit 21 further includes a fundus function lens 213. The fundus function lens 213 includes a light-transmitting portion P1 and a light-shielding portion P2. The light-transmitting portion P1 is arranged to surround the light-shielding portion P2. The fundus function lens 213 is provided between the first light source 211 and the first field stop 212, and the light-shielding portion P2 is located on the optical axis of the coaxial illumination light beam S1 emitted from the first light source 212. The light transmittance of the light-shielding portion P2 is T1, the light transmittance of the light-transmitting portion P1 is T2, T1 < 1%, and T2 > 99%.

[0038] Exemplarily, the first light source 211 can employ a white light source. A fundus function lens 213 is provided between the first light source 211 and the first field stop 212, and it is possible to avoid damaging the observed eye due to the white light source being too strong. In this embodiment, the fundus function lens 213 can employ a flat lens designed in a circular shape. At the center of the fundus function lens 213, a light-shielding portion P2 with an adjustable size according to factors such as the intensity of the light source, the coaxial illumination field of view, and the observer's physical sensation regarding light stimulation is arranged. For example, at the center of the fundus function lens 213, a black light-absorbing material with a diameter of 1 mm is coded. This black-painted area is enlarged to a diameter of about 15 mm on the fundus by the illumination lens. The transmittance T1 of the black-painted area is less than 1%. The light-transmitting portion P1 is arranged along the periphery of the light-shielding portion P2, and the transmittance T2 of the light-transmitting portion P1 is greater than 99%. In the embodiment of the present disclosure, by arranging the above-mentioned fundus function lens 213, in addition to ensuring coaxial illumination, it is possible to protect the observer's pupil from damage caused by strong light. The technical solution of this embodiment is particularly suitable for child and young patients and can avoid damage to the eye pupils caused by strong light.

[0039] Continuing to refer to FIG. 1, the angular illumination unit 22 includes a second light source 221, a second field stop 222, and a second illumination lens group 223. The second light source 221 is arranged to emit an angular illumination light beam S2. Referring back to FIG. 1, in the surgical microscope, the coaxial illumination unit 21 and the angled illumination unit 22 can be operated separately or simultaneously. The coaxial illumination unit 21 and the angled illumination unit 22 can perform on / off control using different activation switches or buttons.

[0040] In the embodiments of the present disclosure, in some surgical scenarios, the coaxial illumination (0° illumination) and the angled illumination (e.g., 5° - 7° field illumination) can operate individually, and the two coaxial illumination optical paths corresponding to the left and right eyes are symmetric with respect to the main optical axis of the surgical microscope system. In some other surgical scenarios, the coaxial illumination and the angled illumination can also operate simultaneously. In one embodiment, when the coaxial illumination unit 21 and the angled illumination unit 22 illuminate simultaneously, the light intensity ratio of the coaxial illumination to the angled illumination is 4:15, and the angle between the angled illumination light ray S2 refracted by the objective lens 11 and the coaxial illumination light ray S1 refracted by the objective lens 11 is 5° - 7°, which can achieve the effect of equalizing the energy of the light spot and improving the field of view range and illumination brightness.

[0041] FIG. 6 is a schematic diagram of a variable magnification unit according to an embodiment of the present disclosure.

[0042] As shown in FIG. 6, the variable magnification unit 13 includes a front fixed group 120, a variable magnification group 130, a compensation group 140, and a rear fixed group 150. The front fixed group 120, the variable magnification group 130, and the compensation group 140 are all cemented lenses. Exemplarily, the front fixed group 120 includes a third lens 121 and a fourth lens 122 provided in sequence along the main optical axis from the image side to the object side, the variable magnification group 130 includes a fifth lens 131 (negative refractive power) and a sixth lens 132 (negative refractive power) provided in sequence along the main optical axis from the image side to the object side, and the compensation group 140 includes a seventh lens 141 (negative refractive power) and an eighth lens 142 (negative refractive power) provided in sequence along the main optical axis from the image side to the object side. The rear fixed group 150 includes two lenses, a cemented lens 1501 and a meniscus lens 1502, provided in sequence along the main optical axis from the image side to the object side.

[0043] According to the embodiments of the present disclosure, the front fixed group 120 has a positive refractive power, the variable magnification group 130 has a negative refractive power, the compensation group 140 has a negative refractive power, and the rear fixed group 150 has a positive refractive power. Therefore, the variable magnification unit 13 has a positive-negative-positive structure. In the embodiments of the present disclosure, the variable magnification ratio of the variable magnification unit 13 may reach 1:6, the field of view of the variable magnification unit 13 changes in the range from 0° to 7.4°, and the pupil diameter of the variable magnification unit 13 may change in the range from 3.4 mm to 18 mm.

[0044] In the embodiments of the present disclosure, the compensation group 140 is arranged to compensate for the off-axis aberration generated during the zoom movement, effectively realizing the balance of the aberrations of the entire zoom, and ensuring the sharpness of the images in different focal length states. Through the cooperation of the variable magnification group 130 and the compensation group 140, continuous focusless variable magnification is realized. Due to the characteristics that the system variable magnification is large and the field of view range changes continuously, the continuous focusless variable magnification of the surgical microscope can be realized, and the discomfort of the observer (for example, the surgeon) caused by the jump of the field of view can be eliminated.

[0045] In the embodiments of the present disclosure, as shown in FIG. 1, the objective lens 11 includes a first lens 111 and a second lens 112 provided in an adhesive configuration. The surface of the lens close to the object surface is the object side surface, and the surface of the lens close to the image surface is the image side surface. The object side surface of the first lens 111 is a plane, the image side surface of the first lens 111 is a concave surface, the object side surface of the second lens 112 is a convex surface, the image side surface of the second lens 112 is a convex surface, the refractive index of the first lens 111 is n1, the refractive index of the second lens 112 is n2, the Abbe number of the first lens 111 is v1, the Abbe number of the second lens 112 is v2, and n1>n2 and v1<v2.

[0046] The refractive index is the ratio of the speed of light propagation in a vacuum to the speed of light propagation in a medium, and is mainly used to describe the refractive power of a material with respect to light. Different materials have different refractive indices, and the higher the refractive index of a material, the stronger the ability to refract incident light. The Abbe number is used to indicate the index of chromatic dispersion of a transparent medium. The greater the chromatic dispersion of the transparent medium, the smaller the Abbe number, and the smaller the chromatic dispersion, the larger the Abbe number.

[0047] When a white light source is used for imaging, chromatic dispersion occurs due to light of different colors having different refractive indices. Therefore, light of different colors has different propagation optical paths, and finally, aberration (referred to as chromatic aberration) due to the difference in the optical paths of light of different colors is presented. In an embodiment of the present disclosure, when the first lens 111 is a plano-concave lens and the second lens 112 is a convex-convex lens, and the first lens 111 and the second lens 112 are adhered, and the refractive index n1 of the first lens 111 is made larger than the refractive index n2 of the second lens 112, the incident light amount can be increased. However, at the same time, chromatic aberration is introduced. By making the Abbe number v1 of the first lens 111 smaller than the Abbe number v2 of the second lens 112, the chromatic dispersion effect can be reduced, and the effect of removing chromatic aberration can be achieved.

[0048] In an embodiment of the present disclosure, as shown in FIG. 1, the illumination module 02 further includes a stray light absorption unit 23. The stray light absorption unit 23 is disposed on the opposite side of the dichroic beam splitter 12 from the coaxial illumination unit 21, and is disposed on the propagation path of the illumination light that passes through the dichroic beam splitter 12 among the coaxial illumination light rays S1.

[0049] In an embodiment of the present disclosure, the illumination module 02 further includes a stray light absorption unit 23 for preventing interference of stray light, and is mainly arranged to absorb the stray light of the propagated light that passes through the dichroic beam splitter 12 among the illumination light. Therefore, the stray light absorption unit 23 is provided on the opposite side of the dichroic beam splitter 12 from the coaxial illumination unit 21, and the coaxial illumination light beam S1 passing through the dichroic beam splitter 12 can be absorbed by the stray light absorption unit 23, so that the purpose of removing stray light can be achieved. Exemplarily, the stray light absorption unit 23 has an elliptical bowl structure with an inner part formed of a light-absorbing material, but a light-absorbing film may be coated on its inner surface. The curvature of the elliptical bowl is determined by the distance to the dichroic beam splitter 12 and the distance to the objective lens 11. In an embodiment of the present disclosure, the stray light absorption unit 23 may be designed as the outer wall of the mechanical frame of the objective lens 11.

[0050] FIG. 7 is a schematic optical path diagram of a scanning unit according to an embodiment of the present disclosure.

[0051] In an embodiment of the present disclosure, referring back to FIG. 1 and referring to FIG. 7, the surgical microscope system may further include an OCT imaging module 03 having a scanning unit 31 and an OCT image acquisition unit 32. The OCT image acquisition unit 32 is arranged on the main optical axis between the variable magnification unit 13 and the dichroic beam splitter 12, and the scanning unit 31 is arranged on the main optical axis between the dichroic beam splitter 12 and the objective lens 11.

[0052] In an embodiment of the present disclosure, the OCT imaging module 03 is arranged to acquire and display an OCT image of an eye to be observed. OCT is a common ophthalmic examination method, mainly used for examining the anterior segment and posterior segment (including the fundus) of the eyeball. In an embodiment of the present disclosure, the OCT imaging module 03 is provided in the optical path of the surgical display mirror system, and the scanning unit 31 and the coaxial illumination unit 21 are provided on the same side of the dichroic beam splitter 12, so that the scanning light beam S5 emitted from the scanning unit 31 is reflected by the dichroic beam splitter 12, and then its optical axis L2 coincides with the main optical axis L1. The scanning unit 31 further includes a galvo scanner 311, a focus lens 312, an OCT system light source 313, a second reflection mirror 314, a plurality of focusing lenses 315, a controller, and the like. The galvo scanner 311 is arranged to scan the eye to be examined, and the focus lens 312 is a negative lens configured to be able to finely adjust the axial direction. Through the cooperation of the galvo scanner 311 and the focus lens 312, OCT tomographic imaging of the surface M to be observed can be realized.

[0053] The OCT image acquisition unit 32 is provided on the principal optical axis between the dichroic beam splitter 12 and the variable magnification unit 13. The OCT image acquisition unit 32 is a high-speed Charge-coupled Device (CCD) camera. In one embodiment, the side of the dichroic beam splitter 12 facing the OCT image acquisition unit 32 is coated with a reflective film. Among the light rays from the observed surface M, the light rays transmitted through the dichroic beam splitter 12 are divided into two paths (the two paths of the light rays have different propagation directions). One of the light rays is reflected by the reflective film of the dichroic beam splitter 12 and incident on the OCT image acquisition unit 32 to form an OCT tomographic image, and the other light ray is directly incident on the variable magnification unit 13 along the direction of the principal optical axis L1 to form a microscopic image. Alternatively, in other embodiments, a beam splitter similar to the beam splitter 14 may be added between the dichroic beam splitter 12 and the variable magnification unit 13 so that the light rays transmitted through the dichroic beam splitter 12 among the light rays from the observed surface M are divided into two paths by the beam splitting unit (the two path light rays have different propagation directions). One of the light rays is incident on the OCT image acquisition unit 32 to form an OCT tomographic image, and the other light ray is directly incident on the variable magnification unit 13 along the direction of the principal optical axis L1 to form a microscopic image. According to the embodiments of the present disclosure, since the OCT image acquisition unit 32 is provided on the principal optical axis between the dichroic beam splitter 12 and the variable magnification unit 13, the size of the image displayed on the CCD screen of the OCT image acquisition unit 32 can change according to the change in the magnification of the surgical microscope. Since the observed surface M and the CCD image plane are conjugate planes, the OCT image displayed in real time on the CCD screen can coincide with the microscopic image of the observed surface M observed through the eyepiece lens group 16. Thereby, the OCT image displayed on the CCD screen by the OCT image acquisition unit 32 coincides with the imaging magnification of the observed surface M seen by the observer (for example, the surgeon) through the surgical microscope eyepiece lens group 16.In this way, the microscopic images observed by the surgeon through the eyepiece lens group 16 during the operation are consistent with the OCT images observed by the assistant through the above CCD screen, so intraoperative teaching can also be realized.

[0054] According to the embodiments of the present disclosure, the microscopic images observed through the eyepiece lens group 16 of the surgical microscope, the surgical images acquired through the image acquisition unit 17, and the OCT images acquired through the OCT image acquisition unit 32 have the same image content and field of view. The microscopic images observed through the eyepiece lens group 16 and the OCT images acquired through the OCT image acquisition unit 32 and displayed on the CCD screen not only have the same image content and field of view but also have the same magnification. The surgical images acquired by the image acquisition unit 17 can be called for postoperative archive and analysis.

[0055] Based on the same inventive concept, the embodiments of the present disclosure further provide a surgical display mirror. The surgical microscope includes the surgical display mirror system according to the above embodiment. The surgical display mirror also has the effects of the surgical display mirror system in the above embodiment and can be understood by referring to the interpretation and description of the above surgical display mirror system, and the description will not be repeated below.

Description of Reference Numerals

[0056] L1 main optical axis, M observed surface, 01 microscope imaging module, 02 illumination module, 03 O - light coherence tomography (OCT) imaging module, 11 objective lens, 111 first lens, 112 second lens, 12 dichroic beam splitter, 13 variable magnification unit, 14 beam splitter, 15 barrel, 16 eyepiece lens group, 17 image acquisition unit, 18 first reflection mirror, S3 first beam, S4 second beam, 21 coaxial illumination unit, 211 first light source, 212 first field stop, 2121 first disk - shaped stop, 2122 rectangular stop, 2123 second disk - shaped stop, O light - transmitting hole, 213 fundus function lens, P1 light - transmitting part, P2 light - shielding part, 214 first illumination lens group, 22 angular illumination unit, 221 second light source, 222 second field stop, 223 second illumination lens group, 23 stray light absorption unit, 120 front fixed group, 121 third lens, 122 fourth lens, 130 variable magnification group, 131 fifth lens, 132 sixth lens, 140 compensation group, 141 seventh lens, 142 eighth lens, 150 rear fixed group, 151 first lens group, 152 second lens group, 1501 adhesive lens, 1502 meniscus lens, 31 scanning unit, 311 galvanometer scanner, 312 focus lens, 313 OCT system light source, 314 second reflection mirror, 315 focusing lens, 32 OCT image acquisition unit.

Claims

1. A surgical microscope system comprising a microscope imaging module (01) and an illumination module (02), wherein the microscope imaging module (01) includes an objective lens (11) provided along a principal optical axis (L1), a dichroic beam splitter (12), a variable magnification unit (13), a beam splitter (14), a lens barrel (15), and an eyepiece lens group (16). Light rays emitted from an object surface (M) sequentially pass through the objective lens (11), the dichroic beam splitter (12), and the variable magnification unit (13), and then are split by the beam splitter (14) into a first beam (S3) and a second beam (S4). The first beam (S3) sequentially passes through the lens barrel (15) and the eyepiece lens group (16) along the principal optical axis (L1) and is configured to be observed by an observer. The microscope imaging module (01) further includes an image acquisition unit (17) that is located on the propagation path of the second beam (S4) and is configured to acquire a surgical image. The first beam (S3) and the second beam (S4) have different propagation directions. The illumination module (02) includes a coaxial illumination unit (21) and an angled illumination unit (22). Both the coaxial illumination unit (21) and the angled illumination unit (22) are located on the side of the dichroic beam splitter (12) facing the objective lens (11). The coaxial illumination unit (21) includes a first light source (211) and a first field stop (212). The first field stop (212) is provided between the first light source (211) and the dichroic beam splitter (12). Coaxial illumination light rays emitted from the first light source (211) pass through the first field stop (212), are reflected by the dichroic beam splitter (12), pass through the objective lens (11), and reach the object surface (M) along the direction of the principal optical axis (L1) to form a first light spot. Angled illumination light rays emitted from the angled illumination unit (22) are reflected by the dichroic beam splitter (12), pass through the objective lens (11), and reach the object surface (M) along a direction forming a predetermined angle with respect to the principal optical axis (L1) to form a second light spot. The size of the first light spot is adjustable. A surgical microscope system.

2. The first field stop (212) is provided with a plurality of light-transmitting holes (O) having different sizes, and different light-transmitting holes (O) of the first field stop (212) are selected so as to be able to form first light spots having different sizes. The surgical microscope system according to claim 1.

3. The first field stop (212) is one first disk-shaped stop (2121), a rectangular stop (2122) in which the centers of a plurality of light-transmitting holes having different sizes are located on the same straight line, and at least one of a plurality of second disk-shaped stops (2123) provided in a folded state. The centers of the plurality of light-transmitting holes (O) having different sizes provided in the first disk-shaped stop (2121) are all located on the same circumference centered on the center of the first disk-shaped stop (2121). Each second disk-shaped stop (2123) is provided with one light-transmitting hole, and different second disk-shaped stops (2123) are provided with light-transmitting holes having different sizes. In the folded state, the centers of the plurality of light-transmitting holes corresponding to the plurality of second disk-shaped stops (2123) are located on the same axis. The surgical microscope system according to claim 2.

4. The coaxial illumination unit (21) and the angled illumination unit (22) can be operated individually or simultaneously. The surgical microscope system according to claim 1.

5. The OCT imaging module (03) further includes a scanning unit (31) and an optical coherence tomography OCT image acquisition unit (32). The OCT image acquisition unit (32) is provided on the main optical axis (L1) between the variable magnification unit (13) and the dichroic beam splitter (12), and the scanning unit (31) is provided on the main optical axis (L1) between the dichroic beam splitter (12) and the objective lens (11). The surgical microscope system according to claim 1.

6. The lens barrel (15) is provided with a first lens group (151) including a meniscus lens and a second lens group (152) including an adhesive lens. The first lens group (151) is located at an end portion of the lens barrel (15) close to the eyepiece lens group (16), and the second lens group (152) is located at an end portion of the lens barrel (15) close to the variable magnification unit (13). The surgical microscope system according to claim 1.

7. The coaxial illumination unit (21) further includes a fundus function lens (213). The fundus function lens (213) includes a light-transmitting portion (P1) and a light-shielding portion (P2). The light-transmitting portion (P1) is provided so as to surround the periphery of the light-shielding portion (P2). The fundus function lens (213) is located between the first light source (211) and the first field stop (212). The light-shielding portion (P2) is located on the optical axis of the coaxial illumination light beam emitted from the first light source (211). The transmittance of the light-shielding portion (P2) is T1, and the transmittance of the light-transmitting portion (P2) is T2, where T1 < 1% and T2 > 99%. The surgical microscope system according to claim 1.

8. The illumination module (02) further includes a stray light absorption unit (23). The stray light absorption unit (23) is provided on the side opposite to the coaxial illumination unit (21) of the dichroic beam splitter (12), and is provided on the propagation path of the illumination light beam that passes through the dichroic beam splitter (12) among the coaxial illumination light beams. The surgical microscope system according to claim 1.

9. The objective lens (11) includes a first lens (111) and a second lens (112) that are adhesively provided. The surface closer to the object side of the lens is the object side surface, and the surface closer to the image side of the lens is the image side surface. The object side surface of the first lens (111) is a plane, the image side surface of the first lens (111) is a concave surface, the object side surface of the second lens (112) is a convex surface, the image side surface of the second lens (112) is a convex surface. The refractive index of the first lens (111) is n1, the refractive index of the second lens (112) is n2, the Abbe number of the first lens (111) is v1, the Abbe number of the second lens (112) is v2, and n1 > n2 and v1 < v2. The surgical microscope system according to claim 1.

10. Comprising the surgical microscope system according to any one of claims 1 to 9 Surgical microscope.

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