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 for example, relates to 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 doctors during surgery are not rich and sufficient. Therefore, it is very difficult for an ophthalmologist to observe 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, a 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 including a microscope imaging module and an illumination module. The microscope imaging module comprises an objective lens positioned along the principal optical axis, a dichroic beam splitter, a variable magnification unit, a beam splitter, a microscope tube, and an eyepiece lens group. Light rays emitted from the surface of the body to be observed pass through the objective lens, the dichroic beam splitter, and the variable magnification unit in sequence, and are then split into a first beam and a second beam by the beam splitter. The first beam passes through the microscope tube and the eyepiece lens group in sequence along the principal optical axis and is configured to be observed by the observer. The microscope imaging module further comprises an image acquisition unit positioned along the propagation path of the second beam and configured to acquire surgical images. The first beam and the second beam have different propagation directions. The illumination module comprises a coaxial illumination unit and an angled illumination unit, both of which 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 diaphragm, the first field diaphragm is positioned between the first light source and the dichroic beam splitter, the coaxial illumination ray emitted from the first light source passes through the first field diaphragm, is reflected by the dichroic beam splitter, passes through the objective lens, reaches the surface of the object being observed along the direction of the principal optical axis, and forms a first light spot, the angled illumination ray emitted from the angled illumination unit is reflected by the dichroic beam splitter, passes through the objective lens, reaches the surface of the object being observed along a direction that makes a predetermined angle with respect to the principal optical axis, and forms a second light spot, the size of the first light spot is adjustable.

[0007] A second aspect of this disclosure further provides a surgical microscope comprising a surgical microscope system described in any embodiment relating to the first aspect of this disclosure. [Brief explanation of the drawing]

[0008] [Figure 1] This is a schematic diagram of a surgical microscope system applicable to ophthalmic surgery according to the embodiments of this disclosure. [Figure 2]This is a schematic diagram of the first field aperture according to an embodiment of the present disclosure. [Figure 3] This is a schematic diagram of another first field aperture according to an embodiment of the present disclosure. [Figure 4] This is a schematic diagram of another first field aperture according to an embodiment of the present disclosure. [Figure 5] This is a schematic diagram of a fundus functional lens according to an embodiment of the present disclosure. [Figure 6] This is a schematic diagram of a variable magnification unit according to an embodiment of the present disclosure. [Figure 7] This is a schematic diagram of the optical path of a scanning unit according to an embodiment of the present disclosure. [Modes for carrying out the invention]

[0009] The technical content of this disclosure will be described below with reference to the accompanying drawings in the embodiments of this disclosure. The embodiments described are only a part of the embodiments of this disclosure.

[0010] In some embodiments, OCT imaging is further provided for ophthalmic surgery to address the problem of the relatively simple functionality of conventional surgical microscopes. However, in these embodiments, OCT imaging is only applicable preoperatively and cannot be provided intraoperatively in combination with a surgical microscope, thus limiting the support available to ophthalmologists.

[0011] Furthermore, in some embodiments, surgical microscopes applied to ophthalmic surgery have illumination modules comprising a coaxial illumination unit and an angled illumination unit. The angled illumination unit, also called a field illumination unit, can provide illumination at different angles to provide the necessary ambient illumination light for the entire surgical site during use of the surgical microscope. The coaxial illumination unit, also called a 0° illumination unit, can provide background illumination light for the surgical area, which is critically important for cataract surgery, as it is itself limited by the pupillary region of the lens, thus ensuring the basic requirements for an optimal illumination system in cataract surgery. In other words, the background illumination light for the surgical area needs to have uniform red light reflection, and at the same time, good contrast of red light reflection is required, and the coaxial illumination unit can suitably satisfy these requirements. However, in some embodiments of the related technology, the size of the fundus spot (also called the fundus light spot) provided by the coaxial illumination unit cannot be adjusted.

[0012] Incidentally, in cataract surgery, if the patient's fundus has only very small lesions, or if the fundus is generally small (for example, if the patient is a child, the fundus is generally small), a closer fundus spot can provide better contrast. Furthermore, in cataract surgery, in cases of relatively thick cataracts, the "red light reflection" may be too dim, and 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 technology, the coaxial illumination unit and the angled illumination unit in the illumination module of a surgical microscope applied to ophthalmic surgery cannot be operated simultaneously and can only be operated individually.

[0014] However, in ophthalmic surgery, there are times when it is necessary to enlarge the field of view to facilitate the surgery, or when an assistant needs to help the surgeon with procedures on the peripheral area of ​​the eyeball. In such cases, it is necessary to operate both a coaxial illumination unit and an angled illumination unit simultaneously.

[0015] Therefore, in order to better meet the needs of surgical microscopes, particularly those of ophthalmic surgery, in some embodiments of the present disclosure, an OCT imaging module is added to the surgical microscope so that OCT imaging is not limited to being available only before ophthalmic surgery, but can also be used during ophthalmic surgery. In some other embodiments of the present disclosure, the illumination module in the surgical microscope is further 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, the illumination module in the surgical microscope is further improved so that the coaxial illumination unit and the angled illumination unit can be operated not only individually but simultaneously.

[0016] Figure 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 Figure 1, the embodiment of the present invention provides a surgical microscope system applicable to ophthalmic surgery, which can be used during medical ophthalmic surgery. The surgical microscope system comprises a microscope imaging module 01 and an illumination module 02. The microscope imaging module 01 comprises an objective lens 11 provided along the principal optical axis L1 from the object plane to the image plane, a dichroic beam splitter 12, a variable magnification unit 13, a beam splitter 14, a microscope tube 15, and an eyepiece lens group 16. Light rays emitted from the surface of the body to be observed M pass through the objective lens 11, the dichroic beam splitter 12, and the variable magnification unit 13 in sequence, and are then split into a first beam S3 and a second beam S4 by the beam splitter 14. The first beam S3 passes through the microscope tube 15 and the eyepiece lens group 16 in sequence along the principal optical axis L1 and is arranged to be observed by the observer, and microscope imaging Module 01 further comprises an image acquisition unit 17 located along the propagation path of the second beam S4 to acquire surgical images, and the first beam S3 and the second beam S4 have different propagation directions. Illumination module 02 comprises a coaxial illumination unit 21 and an angled illumination unit 22, both of which are located on the side facing the objective lens 11 of the dichroic beam splitter 12. Coaxial illumination unit 21 comprises a first light source 211, a first field diaphragm 212, and a first illumination lens group 214. The first field diaphragm 212 is positioned 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. If coaxial illumination unit 21 further comprises a fundus function endoscope 213, the first field diaphragm 212 is positioned between the fundus function endoscope 213 and the first illumination lens group 214.The coaxial illumination ray S1 emitted from the first light source 211 passes through the first field diaphragm 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 observed body surface M along the direction of the principal optical axis L1, and forms a first light spot (fundus spot) of adjustable size. The angled illumination ray S2 emitted from the angled illumination unit 22 is reflected by the dichroic beam splitter 12, then passes through the objective lens 11, reaches the observed body surface M along a direction that makes a predetermined angle (e.g., 5° to 7°) with respect to the principal optical axis L1, and forms a second light spot.

[0017] In embodiments of this disclosure, the microscope imaging module 01 is arranged to magnify and image the eye under observation, the illumination module 02 is arranged to provide illumination to the optical path of the surgical microscope system, and the body surface M under observation may be the object surface on which the retina of the eye under observation is located. With respect to the principal optical axis L1 of the microscope imaging module 01, the microscope imaging module 01 comprises an objective lens 11 arranged sequentially from the object surface to the image plane along the principal optical axis L1, a dichroic beam splitter 12, a variable magnification unit 13, a beam splitter 14, a first reflective mirror 18, a microscope tube 15, and an eyepiece lens group 16. The variable magnification unit 13 may be arranged to adjust the size of the displayed image of the body surface M under observation observed by the eyepiece lens group 16. The illumination module 02 is positioned in the display mirror system to use both coaxial illumination and / or angled illumination for the eye under observation. Coaxial illumination means that the illumination rays are parallel to the principal optical axis L1, and angled illumination means that the illumination rays are at an angle to the principal optical axis L1, for example, the angle can be 5° to 7°.

[0018] Exemplary, as shown in Figure 1, both the coaxial illumination unit 21 and the angled illumination unit 22 may be positioned 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 positioned to emit a coaxial illumination ray S1. A first field aperture 212 is provided between the first light source 211 and the dichroic beam splitter 12, and the central optical axis of the coaxial illumination ray S1 emitted from the first light source 211 is set to illuminate the overlapping region between the dichroic beam splitter 12 and the principal optical axis L1. As a result, the coaxial illumination ray S1 is reflected by the dichroic beam splitter 12, propagates along the principal optical axis L1, passes through the objective lens 11, reaches the surface of the body to be observed M, and forms a first light spot. The size of the first light spot can be adjusted by adjusting the size of the light-transmitting aperture of the first field diaphragm 212 to meet different illumination needs depending on the size of the fundus and / or the size of the lesion area in the fundus of different patients.

[0019] In embodiments of this disclosure, since the size of the light spot formed on the fundus by the coaxial illumination unit is adjustable, in cataract surgery, if the patient's fundus has only very small lesions or the patient's fundus is relatively small, the surgery can be facilitated by reducing the size of the fundus spot to obtain better contrast. In cataract surgery, if the "red light reflection" is too dim due to the cataract being relatively thick, the surgery can be facilitated by adjusting the size of the fundus spot to increase the brightness of the fundus.

[0020] In an embodiment of the present disclosure, the angled illumination light beam S2 emitted from the angled 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 observed surface M 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 angled illumination unit 22, the propagation direction of the angled 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 observed eye 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-fold lens group composed of a single lens and a double adhesive 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 to change the contact surface between the angled illumination ray S2 and the dichroic beam splitter 12, the magnitude of the angle between the angled illumination 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 to expand the field of view range of the angled illumination, and by decreasing the angle α, the diameter of the second light spot can be decreased to narrow the field of view range of the angled illumination. 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 (e.g., the above-mentioned first light spot) formed by the coaxial illumination unit of the illumination module is set as a light spot with an adjustable size, 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 (e.g., 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 apertures according to embodiments of the present disclosure.

[0025] In the embodiments of this disclosure, the first field diaphragm 212 is provided with a plurality of light-transmitting holes O of different sizes, and by selecting different light-transmitting holes O of the first field diaphragm 212, first light spots of different sizes can be formed.

[0026] In the embodiments of this disclosure, the first field diaphragm 212 is provided with multiple translucent holes O of different diameters. Therefore, to adjust the size of the fundus spot of the subject under examination for different surgical scenarios, the intensity (brightness) and uniformity of the "red light reflection" can be influenced by selecting translucent holes O of different diameters. The red light reflection test is used to examine abnormalities in the posterior part of the eyeball, such as cataracts and corneal opacities, as well as opacity of the visual axis. The larger the diameter of the fundus spot formed by illumination, the more uniform and brighter the "red light reflection" becomes. Conversely, the smaller the diameter of the fundus spot formed by illumination, the better the contrast of the "red light reflection" becomes. If the surgical microscope system needs to use coaxial illumination only, the first light source 211 is turned on, and a light-transmitting aperture O of an appropriate diameter is selected according to the size of the patient's fundus. The coaxial illumination ray S1 emitted from the first light source 211 passes through the light-transmitting aperture O, is reflected by the dichroic beam splitter 12, passes through the objective lens 11, reaches the eye under observation, 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 in the fundus.

[0027] In the embodiments of this disclosure, the first field diaphragm 212 can take on various forms. In one possible embodiment, as shown in Figure 2, the first field diaphragm 212 may be a first disc-shaped diaphragm 2121. The centers of a plurality of light-transmitting holes O of different sizes provided in the first disc-shaped diaphragm 2121 are all located on the same circumference with the center of the first disc-shaped diaphragm 2121 as its center. After rotating the first field diaphragm 212 to move one of its light-transmitting holes O to the coaxial illumination path, the principal optical axis of the coaxial illumination ray S1 emitted from the first light source 211 can be precisely transmitted through the center of the light-transmitting hole O, perpendicular to the plane in which the light-transmitting hole O is located, thereby achieving the objectives of precise positioning and easy adjustment.

[0028] Exemplary, as shown in Figure 2, each of the four quadrants of the circular first field diaphragm 212 is provided with translucent holes O of different diameters, and the centers of the four translucent 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 diaphragm 212. When in use, the first field diaphragm 212 can be rotated by 45°, 135°, 225°, and 270° around an axis perpendicular to the surface of the first field diaphragm 212 and passing through the center of the first field diaphragm 212, so as to move different translucent holes O to the coaxial illumination path. After moving any of the translucent holes O of the first field diaphragm 212 to the coaxial illumination path, the principal optical axis of the coaxial illumination ray S1 emitted from the first light source 211 can be precisely transmitted through the center of the translucent hole O perpendicular to the plane in which the translucent hole O is located. The user can select the size of the light-transmitting aperture O of the first field diaphragm 212 according to the size of the patient's fundus, which is beneficial for improving the contrast of microscopic imaging.

[0029] Alternatively, in another possible embodiment, as shown in Figure 3, the first field diaphragm 212 may be a rectangular diaphragm 2122. The centers of multiple light-transmitting holes O of different sizes provided in the rectangular diaphragm 2122 are aligned in the same straight line, and by pushing the first field diaphragm 212, one of the light-transmitting holes O is moved to the coaxial illumination path, and the principal optical axis of the coaxial illumination ray S1 emitted from the first light source 211 is perpendicular to the plane in which the light-transmitting hole O is located, and the light-transmitting hole O is precisely transmitted through its center, thereby achieving the objectives of precise positioning and easy adjustment.

[0030] Exemplary, the rectangular first field diaphragm 212 shown in Figure 3 has four transmissive holes O of different sizes arranged sequentially along its long side. During use, the transmissive holes O that meet the surgical needs can be pushed into the coaxial illumination path by pressing the first field diaphragm 212 along its long side. In this embodiment, after moving any of the transmissive holes O of the rectangular first field diaphragm 212 to the coaxial illumination path, the principal optical axis of the coaxial illumination ray S1 emitted from the first light source 211 can be precisely transmitted through the center of the transmissive hole O, perpendicular to the plane in which the transmissive hole O is located. The user can select the size of the transmissive holes O of the first field diaphragm 212 according to the size of the patient's fundus, which is beneficial for improving the contrast of microscopic imaging.

[0031] Alternatively, in another possible embodiment, as shown in Figure 4, the first field diaphragm 212 may include a plurality of second disc-shaped diaphragms 2123, the plurality of second disc-shaped diaphragms 2123 being arranged in a folded state, each of the second disc-shaped diaphragms 2123 having one light-transmitting hole O, different second disc-shaped diaphragms 2123 having light-transmitting holes O of different sizes, and in the folded state, the centers of the plurality of light-transmitting holes O corresponding to the plurality of second disc-shaped diaphragms 2123 are located on the same axis.

[0032] Exemplary, as shown in Figure 4, each second disc-shaped diaphragm 2123 is provided with one translucent hole O, and the translucent holes O are of different sizes. Multiple second disc-shaped diaphragms 2123 are arranged in a folded state, and the centers of the multiple translucent holes O corresponding to the multiple second disc-shaped diaphragms 2123 are located on the same axis when folded. When in use, the second disc-shaped diaphragm 2123 required for surgery is selected from the first field diaphragm 212, the selected second disc-shaped diaphragm 2123 is moved to the coaxial illumination optical path, and the second disc-shaped diaphragms 2123 that are not selected are folded to reduce the space occupied. After operating the first field diaphragm 212 to move one of the translucent holes O to the coaxial illumination optical path, the principal optical axis of the coaxial illumination ray S1 emitted from the first light source 211 is perpendicular to the plane in which the translucent hole O is located and precisely passes through the center of the translucent hole O, thereby achieving the objectives of accurate positioning and easy adjustment. The user can select the size of the light-transmitting aperture O of the first field diaphragm 212 according to the size of the patient's fundus, which is beneficial for improving the contrast of microscopic imaging.

[0033] Continuing to refer to Figure 1, the lens barrel 15 is provided with a first lens group 151 and a second lens group 152. The first lens group 151, which includes a meniscus lens, is located at the end of the lens barrel 15 closest to the eyepiece lens group 16, while the second lens group 152, which includes a bonded lens, is located on the side of the lens barrel 15 closest to the variable magnification unit 13.

[0034] For example, the first lens group 151 and the second lens group 152 are provided at both ends of the lens barrel 15, respectively. The first lens group 151, located at the end closer to the eyepiece lens group 16, is a meniscus lens. This meniscus lens may be a negative meniscus lens with its convex surface facing the eyepiece lens group 16. It can focus the light rays emitted from the variable magnification unit 13, reducing spherical aberration in the imaging light path of the microscope. Furthermore, the design of the meniscus lens contributes to reducing the numerical aperture (NA) of the variable magnification unit 13 and the lens barrel 15, thereby reducing the overall size of the device and further reducing the proportion it occupies in the surgical space of the surgical microscope. The second lens group 152, located at the end closer to the variable magnification unit 13, employs bonded lenses to eliminate reflection loss on both sides of the lens and prevent total internal reflection in the air gap, allowing for easy correction of off-axis image quality and on-axis chromatic aberration. For example, 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 group 16.

[0035] NA is the product of the sine of half the aperture angle (2β) of the medium between the lens and the object being observed and the refractive index (n), and is expressed by the formula NA = n * sinβ. The aperture angle, also called the "lens aperture angle," is the angle formed by the point of the object 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 beam of light incident on the lens, and this is proportional to the effective diameter of the lens and inversely proportional to the distance from the focal point.

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

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

[0038] Exemplary, the first light source 211 can be a white light source, and a fundus function lens 213 is provided between the first light source 211 and the first field diaphragm 212 to avoid damaging the observed eye due to excessive white light intensity. In this embodiment, the fundus function lens 213 can be a flat lens designed as a circular shape, and a light-shielding portion P2 is positioned at the center of the fundus function lens 213, having an adjustable size depending on factors such as the intensity of the light source, the coaxial illumination field, and the observed person's perception of light stimulation. For example, the center of the fundus function lens 213 is coated with a black light-absorbing material with a diameter of 1 mm, and this black-coated area is enlarged to a diameter of approximately 15 mm in the fundus by the illumination lens. The transmittance T1 of the black-coated area is less than 1%, and the light-transmitting portion P1 is positioned around the periphery of the light-shielding portion P2, with the transmittance T2 of the light-transmitting portion P1 being greater than 99%. In the embodiments of this disclosure, by arranging the above-described fundus functional lens 213, in addition to ensuring coaxial illumination, it is possible to protect the pupil of the observed person from damage caused by strong light. The technical proposal of this embodiment is particularly suitable for child and adolescent patients, as it can avoid damage to the pupil of the eye caused by strong light.

[0039] Continuing to refer to Figure 1, the angled illumination unit 22 includes a second light source 221, a second field aperture 222, and a second illumination lens group 223, the second light source 221 being arranged to emit an angled illumination ray S2. Referring back to Figure 1, in a 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 be turned on and off using different activation switches or buttons.

[0040] In embodiments of this disclosure, in some surgical scenarios, coaxial illumination (0° illumination) and angled illumination (e.g., 5° to 7° field illumination) can operate independently, and the two coaxial illumination paths corresponding to the left and right eyes are symmetrical with respect to the principal optical axis of the surgical microscope system. In some other surgical scenarios, coaxial illumination and 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 of the coaxial illumination and the angled illumination is set to 4:15, and the angle between the angled illumination ray S2 refracted by the objective lens 11 and the coaxial illumination ray S1 refracted by the objective lens 11 is set to 5° to 7°, thereby achieving the effect of equalizing the energy of the light spot and improving the field of view and illumination brightness.

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

[0042] As shown in Figure 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 bonded lenses. Exemplarily, the front fixed group 120 includes a third lens 121 and a fourth lens 122 arranged sequentially along the principal 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) arranged sequentially along the principal 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) arranged sequentially along the principal optical axis from the image side to the object side. The rear fixed group 150 includes two lenses, an adhesive lens 1501 and a meniscus lens 1502, which are arranged sequentially along the principal optical axis from the image side to the object side.

[0043] According to the embodiments of this 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 this 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 may vary in the range from 0° to 7.4°, and the pupil diameter of the variable magnification unit 13 may vary in the range from 3.4 mm to 18 mm.

[0044] In the embodiments of this disclosure, the compensation group 140 is positioned to compensate for off-axis aberrations that occur during zoom movement, effectively achieving a balance of aberrations across the entire zoom range and ensuring image clarity at different focal length states. The cooperation between the variable magnification group 130 and the compensation group 140 enables continuous focusless variable magnification. The large system variable magnification and the continuously changing field of view allow for continuous focusless variable magnification in the surgical microscope, eliminating discomfort to the observer (e.g., surgeon) caused by the field of view popping out.

[0045] In embodiments of this disclosure, as shown in Figure 1, the objective lens 11 includes a first lens 111 and a second lens 112 provided by an adhesive configuration, wherein the surface of the lens closest to the object plane is the object side surface, and the surface of the lens closest to the image plane is the image side surface, the object side surface of the first lens 111 is flat, the image side surface of the first lens 111 is concave, the object side surface of the second lens 112 is convex, the image side surface of the second lens 112 is convex, 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である。

[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. It is primarily used to describe the refractive power of a material to light. Different materials have different refractive indices, and the higher the refractive index of a material, the stronger its ability to refract incident light. The Abbe number is used to indicate the index of the 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. As a result, light of different colors has different propagation paths, and ultimately exhibits aberration (referred to as chromatic aberration) due to the difference in the optical paths of light of different colors. In the embodiments of this disclosure, the first lens 111 is a plano-concave lens and the second lens 112 is a convex-convex lens. The first lens 111 and the second lens 112 are bonded together, and the refractive index n1 of the first lens 111 is made greater than the refractive index n2 of the second lens 112. This increases the amount of incident light, but at the same time introduces chromatic aberration. 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 chromatic aberration can be eliminated.

[0048] In embodiments of this disclosure, as shown in Figure 1, the lighting module 02 further comprises a stray light absorption unit 23. The stray light absorption unit 23 is positioned on the opposite side of the dichroic beam splitter 12 from the coaxial lighting unit 21 and is positioned along the propagation path of the lighting rays S1 that pass through the dichroic beam splitter 12.

[0049] In embodiments of this disclosure, the illumination module 02 further comprises a stray light absorption unit 23 for preventing stray light interference, which is primarily arranged to absorb stray light propagating through the dichroic beam splitter 12. Thus, the stray light absorption unit 23 is located on the opposite side of the dichroic beam splitter 12 from the coaxial illumination unit 21, and the coaxial illumination rays S1 passing through the dichroic beam splitter 12 can be absorbed by the stray light absorption unit 23, thereby achieving the objective of eliminating stray light. Exemplarily, the stray light absorption unit 23 is an elliptical cup structure formed internally by a light-absorbing material, but its inner surface may be coated with a light-absorbing film. The curvature of the elliptical cup is determined by the distance to the dichroic beam splitter 12 and the distance to the objective lens 11. In embodiments of this disclosure, the stray light absorption unit 23 may be designed as the outer wall of the mechanical frame of the objective lens 11.

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

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

[0052] In the embodiments of this disclosure, the OCT imaging module 03 is positioned to acquire and display an OCT image of the eye under observation. OCT is a common ophthalmic examination method and is mainly used for examining the anterior and posterior segments (including the fundus) of the eyeball. In the embodiments of this 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 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 principal optical axis L1. The scanning unit 31 further comprises a Garbo scanner 311, a focusing 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 Garbo scanner 311 is positioned to scan the eye under examination, and the focus lens 312 is a negative lens configured to allow for fine adjustment of its axial direction. Through the cooperation of the Garbo scanner 311 and the focus lens 312, OCT tomographic imaging of the observed body surface M can be achieved.

[0053] The OCT image acquisition unit 32 is positioned 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, and the light rays from the surface of the body to be observed that pass through the dichroic beam splitter 12 are split 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 tomography image, while 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 microscope image. Alternatively, in another embodiment, a spectroscopic unit 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 from the surface of the body to be observed that pass through the dichroic beam splitter 12 are split into two paths by the spectroscopic unit (the two path rays have different propagation directions). One ray is incident on the OCT image acquisition unit 32 to form an OCT tomography image, while the other ray is directly incident on the variable magnification unit 13 along the direction of the principal optical axis L1 to form a microscope image. According to the embodiments of this disclosure, since the OCT image acquisition unit 32 is positioned 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 in accordance with the change in magnification of the surgical microscope. Since the observed body surface M and the CCD image plane are conjugate planes, the OCT image displayed on the CCD screen in real time can match the microscopic image of the observed body surface M observed through the eyepiece group 16. As a result, the OCT image displayed on the CCD screen by the OCT image acquisition unit 32 matches the imaging magnification of the observed body surface M as seen by the observer (e.g., the surgeon) through the surgical microscope eyepiece group 16.Thus, the microscopic images observed by the surgeon through the eyepiece group 16 during surgery match the OCT images observed by the assistant through the CCD screen mentioned above, making it possible to perform teaching during surgery.

[0054] According to embodiments of this disclosure, the microscopic image observed through the eyepiece group 16 of the surgical microscope, the surgical image acquired via the image acquisition unit 17, and the OCT image acquired via the OCT image acquisition unit 32 have the same image content and field of view. Furthermore, the microscopic image observed through the eyepiece group 16 and the OCT image acquired via the OCT image acquisition unit 32 and displayed on the CCD screen have the same image content and field of view, as well as the same magnification. The surgical image acquired by the image acquisition unit 17 can be retrieved for postoperative archiving and analysis.

[0055] Based on the same inventive concept, embodiments of the present disclosure further provide a surgical display microscope, the surgical microscope comprising a surgical display microscope system according to the above embodiment, the surgical display microscope also having the effects of the surgical display microscope system of the above embodiment, which can be understood by referring to the interpretation of the surgical display microscope system described above, and will not be repeated below. [Explanation of symbols]

[0056] L1 Main optical axis, M Observed surface, 01 Microscope imaging module, 02 Illumination module, 03 O Optical 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 Microscope tube, 16 Eyepiece group, 17 Image acquisition unit, 18 First reflective mirror, S3 First beam, S4 Second beam, 21 Coaxial illumination unit, 211 First light source, 212 First field diaphragm, 2121 First disc diaphragm, 2122 Rectangular diaphragm, 2123 Second disc diaphragm, O Translucent hole, 213 Fundus functional lens, P1 Translucent part, P2 Shading part, 214 First illumination lens group, 22 Angled illumination unit, 221 222 Second light source, 223 Second field aperture, 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 Garbo scanner, 312 Focus lens, 313 OCT system light source, 314 Second reflection mirror, 315 Focusing lens, 32 OCT image acquisition unit.

Claims

1. The system comprises a microscope imaging module (01) and an illumination module (02), The microscope imaging module (01) comprises an objective lens (11) positioned along the principal optical axis (L1), a dichroic beam splitter (12), a variable magnification unit (13), a beam splitter (14), a microscope tube (15), and an eyepiece lens group (16). Light rays emitted from the surface of the body to be observed (M) pass through the objective lens (11), the dichroic beam splitter (12), and the variable magnification unit (13) in sequence, and then through the beam splitter (14). The first beam (S3) is divided into a first beam (S3) and a second beam (S4), the first beam (S3) is configured to pass sequentially through the microscope tube (15) and the eyepiece lens group (16) along the principal optical axis (L1) and be observed by the observer, the microscope imaging module (01) further comprises an image acquisition unit (17) located on the propagation path of the second beam (S4) and configured to acquire surgical images, the first beam (S3) and the second beam (S4) have different propagation directions, The illumination module (02) comprises a coaxial illumination unit (21) and an angled illumination unit (22), both of which are located on the side of the same dichroic beam splitter (12) facing the objective lens (11), and the coaxial illumination unit (21) includes a first light source (211) and a first field diaphragm (212), the first field diaphragm (212) being provided between the first light source (211) and the dichroic beam splitter (12), and the central optical axis of the light ray emitted from the first light source (211) and the dichroic beam splitter (12) intersect in the overlapping region between the dichroic beam splitter (12) and the principal optical axis, so that the coaxial illumination light ray emitted from the first light source (211) passes through the first field diaphragm (212). The angled illumination unit (22) includes a second light source (221), and the central optical axis of the light ray emitted from the second light source (221) is outside the overlapping region of the dichroic beam splitter (12) and the main optical axis, and intersects the dichroic beam splitter (12). As a result, the angled illumination light ray emitted from the second light source (221), after being reflected by the dichroic beam splitter (12), passes through the objective lens (11) and reaches the surface of the object to be observed (M) along a direction that forms a predetermined angle with respect to the main optical axis (L1), forming a second light spot. The size of the first light spot is adjustable. The coaxial lighting unit (21) and the angled lighting unit (22) can be operated individually or simultaneously. Surgical microscope system.

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

3. The first field diaphragm (212) is, One first disc-shaped aperture (2121) and A rectangular aperture (2122) in which the centers of multiple light-transmitting holes of different sizes are located on the same straight line, It comprises at least one of a plurality of second disc-shaped apertures (2123) that are folded and provided, The centers of the multiple translucent holes (O) of different sizes provided in the first disc-shaped aperture (2121) are all located on the same circumference with the center of the first disc-shaped aperture (2121) as the center. Each second disc-shaped aperture (2123) is provided with one light-transmitting hole, and different second disc-shaped apertures (2123) are provided with light-transmitting holes of different sizes. In the folded state, the centers of the multiple light-transmitting holes corresponding to the multiple second disc-shaped apertures (2123) are located on the same axis. The surgical microscope system according to claim 2.

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

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

6. The coaxial illumination unit (21) further comprises a fundus functional lens (213), the fundus functional lens (213) including a light-transmitting portion (P1) and a light-shielding portion (P2), the light-transmitting portion (P1) being provided so as to surround the light-shielding portion (P2), the fundus functional lens (213) being located between the first light source (211) and the first field diaphragm (212), the light-shielding portion (P2) being 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) being T1 and the transmittance of the light-transmitting portion (P1) being T2, where T1 < 1% and T2 > 99%. The surgical microscope system according to claim 1.

7. The lighting module (02) further comprises a stray light absorption unit (23), which is located on the opposite side of the dichroic beam splitter (12) from the coaxial lighting unit (21), and is located on the propagation path of the illumination rays that pass through the dichroic beam splitter (12) among the coaxial illumination rays. The surgical microscope system according to claim 1.

8. The objective lens (11) includes a first lens (111) and a second lens (112) bonded together, wherein the surface of the lens closer to the object surface is the object side surface, and the surface of the lens closer to the image plane is the image side surface. The object side of the first lens (111) is flat, the image side of the first lens (111) is concave, the object side of the second lens (112) is convex, the image side of the second lens (112) is convex, 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.

9. The surgical microscope system comprises the surgical microscope system according to any one of claims 1 to 8. Surgical microscope.

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