JP2008264489A - Operation microscope equipped with oct system and illumination module for operation microscope equipped with oct system - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide an operation microscope equipped with an OCT system having a small design volume and a design principle that facilitate its retrofitting on an OCT-oriented operation microscope. <P>SOLUTION: The operation microscope 100 has an illumination module 120. The illumination module contains an illuminating optical system for forming an infinite image of a field iris 124 illuminated by a light source and for making an illuminating light path parallel. The illuminating optical system has a first lens group and a second lens group for forming an image of the field iris 124 on an object's region 108 via a microscopic main objective lens 101 of the operation microscope 100. An inputting and coupling member 128 for inputting and coupling an OCT scanning light path to an illuminating light path is arranged between an illuminating light path between the first lens group 125 and the second lens group 126. <P>COPYRIGHT: (C)2009,JPO&INPIT

Description

  The present invention includes an illumination optical system including an observation optical path for inspecting an object region, and an illumination device including an illumination optical system that forms an infinite image of a field stop illuminated by a light source to form a parallel illumination optical path. Has a first lens group and a second lens group, and further includes an objective lens arranged in a parallel illumination optical path for imaging the field stop to the object area, and for inspecting the object area. And an OCT system, which relates to a surgical microscope including an OCT scanning beam path guided through an objective lens.

  Furthermore, the present invention provides a first optical waveguide housing portion for providing illumination light, a field stop that can be illuminated with light derived from the optical waveguide, and an infinite image formed on the field stop in parallel. And an illumination optical system having an imaging optical path, the illumination optical system having a first lens group and a second lens group, and further, illumination emitted from a field stop having parallel imaging optical paths The present invention relates to a surgical microscope illumination module for connecting to a surgical microscope, which includes an illumination mirror that serves to guide light to an object region through a microscope main objective lens.

  A surgical microscope of the kind mentioned at the beginning is known from US Pat. The surgical microscope includes an OCT system that generates an OCT scanning path with a short coherent laser beam. The OCT system includes an analysis unit for evaluating the interference signal. The OCT system includes a device for scanning the OCT scanning optical path, comprising two scanning mirrors that can be adjusted about two axes of motion. The OCT scanning optical path of the surgical microscope is input coupled to the illumination optical path of the surgical microscope via a beam splitting mirror, and thereby guided through the main microscope objective lens toward the object region.

  A surgical microscope illumination module of the type mentioned at the outset is included in the Carl Zeiss surgical microscope system OPMI® Visu200. This illumination module is configured to be attached to the main body of the surgical microscope, and when the illumination module is connected to the surgical microscope, a field stop illuminated with light derived from the optical waveguide is used as a microscope main objective lens. The illumination optical system includes two lens groups that shift to a parallel imaging optical path that extends perpendicularly to the optical axis. The illumination module includes two illumination mirrors that redirect illumination light parallel to the optical axis of the microscope main objective.

The OCT system allows non-invasive display and measurement of tissue internal structures using optical coherence tomography. Optical coherence tomography, as an optical image generation method, makes it possible in particular to generate cross-sectional images or volume images of biological tissue with micrometer resolution. A corresponding OCT system includes a light source for light of coherence length l _c that is supplied to the sample and reference optical paths and is temporally incoherent and spatially coherent. The sample optical path is directed to the tissue to be examined. The OCT system superimposes the laser radiation bounced back to the sample optical path based on the scattering center in the tissue with the laser radiation originating from the reference optical path. An interference signal is generated by the superposition. Based on this interference signal, the position of the scattering center for laser radiation in the examined tissue can be determined.

  Regarding the OCT system, the structural principles of “time domain OCT” and “Fourier domain OCT” are known.

  The structure of “time domain OCT” is described in Patent Document 2, for example, from column 5 line 40 to column 11 line 10 with reference to FIG. In such a system, the optical path length of the reference optical path is continuously changed by a reference mirror capable of high-speed movement. Light derived from the sample optical path and the reference optical path is superimposed on the photodetector. When the optical path lengths of the sample optical path and the reference optical path match, an interference signal is generated in the photodetector.

  “Fourier domain OCT” is described in Patent Document 3, for example. In order to measure the optical path length of the sample optical path, the light derived from the sample optical path is also superimposed on the light derived from the reference optical path. However, unlike “time domain OCT”, in order to measure the optical path length of the sample optical path, the light derived from the sample optical path and the reference optical path is not directly supplied to the detector, but is first measured by the spectrometer. Disassembled. Then, the spectral intensity of the superimposed signal derived from the sample optical path and the reference optical path thus generated is detected by the detector. Similarly, by evaluating the detector signal, the optical path length of the sample optical path can be determined.

European Patent No. 0815801 US Pat. No. 5,321,501 International Publication No. 2006 / 10544A1 Pamphlet

  The object of the present invention is to provide a surgical microscope with an OCT system, which has a small design volume and whose design principle allows a simple retrofit to a surgical microscope for OCT, To provide a surgical microscope illumination module with an integrated OCT system for connection to the surgical microscope.

  The object is to provide an input coupling member for coupling the OCT scanning optical path to the illumination optical path in the illumination optical path between the first lens group and the second lens group. This is solved by a microscope and, further, by a surgical microscope illumination module of the kind mentioned at the beginning, provided with a housing for the second optical waveguide of the OCT system for providing an OCT scanning optical path, The surgical microscope illumination module includes an input coupling member disposed between the first lens group and the second lens group for coupling the OCT scanning optical path to the illumination optical path.

  In a development of the invention, in the surgical microscope or surgical microscope illumination module, the input coupling member is configured as a beam splitting mirror, in particular as a plane mirror or a beam splitting cube.

  In the development example of the present invention, in the surgical microscope, the objective lens arranged in the parallel illumination optical path is configured as a microscope main objective lens, and the observation optical path of the surgical microscope passes. In this way, a particularly compact design form of the surgical microscope is realized.

  In a development example of a surgical microscope, an illumination light direction changing device for changing the direction of illumination light of an illumination device toward the object is provided on the side opposite to the object with respect to the objective lens. In this way, illumination with an axis close to the observation optical path, which is preferable for ophthalmic surgery, is possible.

  In a development of the invention, the direction changing device is configured as a beam splitter through which the observation optical path of the surgical microscope passes. In this way, illumination light can be guided to the object region through the observation optical path of the surgical microscope.

  In a development of the invention, the surgical microscope includes an OCT system comprising a first scanning mirror for scanning the OCT scanning optical path. In addition to this, it is preferable to provide a second scan mirror. In this case, the first scan mirror can be moved around the first rotation axis, and the second scan mirror can move the second rotation axis. The first rotation axis and the second rotation axis are offset laterally and are perpendicular to each other. In this way, the object region can be scanned with a mesh pattern extending vertically.

  In a development of the invention, the surgical microscope includes an OCT system with an optical waveguide having a light exit area for a movably held OCT scanning optical path. In this way, the OCT scanning plane can be changed in the object area, and the system can be adjusted to different OCT wavelengths, taking into account the optical components of the observation beam path designed for visible light. It is.

  In a development of the invention, the surgical microscope has an OCT system with an adjustable collimating optical system that shifts the OCT scanning optical path to a substantially parallel scanning optical path by the second lens group of the illumination optical system. Is included. In this way, in the surgical microscope, it is possible to displace the OCT scanning plane relative to the observation plane of the optical observation optical path of the system.

  The surgical microscope illumination module preferably includes a device for scanning the OCT scanning optical path. This apparatus for scanning can have, for example, a first scan mirror and a second scan mirror. The first scan mirror can be moved around the first rotation axis, the second scan mirror can be adjusted around the second rotation axis, and the first rotation axis and the second rotation axis are on the side. By being offset at right angles to each other and perpendicular to each other, the object region can be scanned with a mesh pattern extending in the vertical direction.

  In a development of the invention, the light exit area of the optical waveguide for the OCT scanning optical path in the surgical microscope illumination module is held movably so that the OCT scanning plane can be adjusted.

  The surgical microscope illumination module is provided with a position-adjustable collimating optical system, which can be used to shift the OCT scanning optical path to a substantially parallel scanning optical path by the second lens group of the illumination optical system. As a result, the OCT scanning plane of the OCT system can be displaced relative to the observation plane of the optical observation optical path.

  Advantageous embodiments of the invention are illustrated in the drawings and are described below.

  The surgical microscope 100 of FIG. 1 has a microscope main objective lens 101 having an optical axis 102 and a focal plane 103 housed in a surgical microscope main body 104. The stereoscopic observation optical path 105 of the binocular tube 106 passes through the microscope main objective lens 101. Surgical microscope 100 includes a zoomable magnification system 107.

  In order to illuminate the object region 108, the surgical microscope 100 has an illumination module 120 as an illumination device. The illumination module 120 includes an accommodating portion 121 of a first optical waveguide 122 that provides illumination light 123 from a light source (not shown). A field stop 124 whose position is adjustable is illuminated by illumination light 123 emitted from the first optical waveguide 122. An illumination optical system is disposed in the illumination module 120. The illumination optical system includes a first lens group 125, a second lens group 126, and four mirror members 127, 128, 129, and 130.

  The mirror member 127 guides the illumination light emitted from the first lens group 125 to the mirror member 128, from which the illumination light reaches the second lens group 126. The first lens group 125 and the second lens group 126 image the field stop 124 to infinity. That is, the illumination light 123 having a parallel optical path is emitted from the second lens group 126. The optical axis 120 of the illumination optical path extends perpendicularly to the optical axis 102 of the microscope main objective lens 101 on the exit side of the second lens group 126 and is guided toward the illumination mirror 130 having the passage 131. The illumination mirror 130 guides illumination light to the object region 108 in parallel with the optical axis 102 of the microscope main objective lens 101.

  Furthermore, the illumination module 120 includes an illumination mirror 132 to which illumination light reaching through the passage part 131 of the illumination mirror 130 is supplied.

  The illumination mirror 132 can be adjusted in the vertical direction with respect to the optical axis 102 of the microscope main objective lens 101 as shown by a double arrow 133. This makes it possible to adjust the incident angle of the illumination light in the object region 108.

  In order to change the intensity of the illumination light guided to the object region, the illumination mirrors 130 and 132 are provided with diaphragms 134 and 135 whose positions can be adjusted. By adjusting the positions of the apertures 134 and 135, the intensity of the illumination light guided through the microscope main objective lens 101 can be changed.

  The illumination module 120 has a housing 150 for the second optical waveguide 151 connected to the OCT system 152.

  The OCT system 152 allows an OCT image to be taken to inspect the object region 108. The OCT system includes a unit for generating and analyzing an OCT scanning optical path 153.

  The OCT system 152 is preferably incorporated into a tripod pole not shown in detail in the surgical microscope. Alternatively, it is possible in principle to accommodate the OCT system in the illumination module 120.

  The scanning optical path 153 emitted from the optical waveguide 151 is guided toward the first scan mirror 154 and the second scan mirror 155 of the OCT scan unit 156, and passes through the condenser lens 157 after the OCT scan unit 156. .

  The light beam 160 derived from the OCT scan unit 156 is guided to the mirror member 128. The mirror member 128 acts as a beam splitting mirror. This mirror member almost completely reflects the illumination light emitted from the optical waveguide 122, but is transmissive to the OCT scanning optical path. Thereby, the OCT scanning light path 153 is superimposed on the illumination light 123. The mirror member 128 is manufactured as a mirror member having a plane parallel plate in the illumination module 120. Alternatively, it can be configured as a beam splitting cube.

  The light in the OCT scanning optical path 153 is guided to the object region 108 together with the illumination light through the illumination mirrors 130 and 132. The condenser lens 157, the second lens group 126 of the illumination optical system of the illumination module 120, and the microscope main objective lens 101 converge the OCT scanning optical path 153 on the OCT scanning plane 170. The OCT scanning plane 170 is determined by the optical member of the OCT scanning optical path including the OCT scanning unit 156, the condensing lens 157, the mirror member 128, the mirror member 130, and the mirror member 132, and is determined by the microscope main objective lens 101. Further, the exit end portion 173 of the optical waveguide is a plane on which a geometric image is formed. That is, a corresponding geometric image of the exit end of the optical waveguide is located in the OCT scan plane 170. In order to adjust the OCT scanning plane, on the other hand, the condensing lens 157 is held movably as indicated by a double arrow 172 by a position adjustment driving device 171. On the other hand, in addition to this, the exit end 173 of the optical waveguide 151 for the OCT scanning optical path can be displaced by the position adjusting device 174 as shown by a double arrow 175. When the OCT scan plane 170 is adjusted, the reference optical path of the OCT system is also readjusted to the required extent.

  The light backscattered to the OCT scanning optical path returns to the OCT system 152 via the microscope main objective lens 101, the mirror members 132 and 130, the lens group 126, and the mirror member 128. Thus, the OCT scanning light backscattered from the object region is interfered by OCT radiation originating from the reference optical path. The interference signal is detected by the detector and evaluated by the computer unit. Based on this signal, the computer unit calculates an optical path length difference between the OCT light scattering center in the object region and the light path length in the reference shunt.

  FIG. 2 is a cross-sectional view taken along the line II-II in FIG. This drawing shows the illumination mirrors 130 and 132 and explains the transition of the stereoscopic observation optical path 105 in the surgical microscope 100 of FIG. Two stereoscopic partial optical paths 105 a and 105 b pass through the microscope main objective lens 101. The optical axis 102 of the microscope main objective 101 is located at the center thereof.

  FIG. 3 shows the OCT scan unit 156 of the surgical microscope 100 of FIG. The first scan mirror 154 and the second scan mirror 155 are arranged so as to be able to rotate about the two axes 303 and 304 extending perpendicularly to each other by the actuators 301 and 302. This makes it possible to scan the OCT scanning optical path 305 with the plane 306.

を満たしており、このときＮＡは光導波路の前面の開口数である。光導波路１２２のファイバコアの直径ｄは、５μｍ＜ｄ＜１０μｍの範囲内にあるのが好ましい。このパラメータ範囲内では、光導波路１２２はガウス形の波長モードで光を案内する。ＯＣＴ走査光線４０１は、胴部パラメータＷ₀と開口パラメータθ₀とによって特徴づけられる、近似的にガウス形の放射断面形状で光導波路１５１から射出され、このとき次式が成り立つ。

FIG. 4 shows the front area 402 of the optical waveguide 151 of FIG. The optical waveguide 151 acts as a monomode fiber for light having a wavelength λ = 1310 nm. The diameter d of the fiber core of the optical waveguide 122 is:

Where NA is the numerical aperture of the front surface of the optical waveguide. The diameter d of the fiber core of the optical waveguide 122 is preferably in the range of 5 μm <d <10 μm. Within this parameter range, the optical waveguide 122 guides light in a Gaussian wavelength mode. The OCT scanning light beam 401 is emitted from the optical waveguide 151 in an approximately Gaussian radiation cross-sectional shape characterized by the body parameter W ₀ and the aperture parameter θ _0, and at this time, the following equation is established.

Therefore, for a fiber core diameter of d ₀ = 10 μm and a wavelength of λ ₀ = 1310 nm, an opening angle of θ ₀ ≈0.0827 rad is obtained as a guide representing beam divergence.

  The front surface 402 of the optical waveguide 151 passes through the scan mirrors 154 and 155, the condensing lens 157, the mirror member 128, the second lens group 126, the mirror member 130, and the mirror member 132 in the surgical microscope 100 shown in FIG. Then, an image is formed on the OCT scanning plane 170 of the object region 107 through the microscope main objective lens 101.

ここでλはＯＣＴ走査光線の波長である。ガウス光束５００の胴部パラメータＷと、図４に示す、光導波路１５１から射出される走査光線４０１の胴部パラメータＷ₀との間には、次の関係が成り立つ：
Ｗ＝βＷ₀
ここでβは、ＯＣＴ走査平面における図１の光導波路１５１の射出端部の上に述べた幾何学的結像の拡大パラメータないし縮小パラメータである。βは、図１の集光レンズ１５７の焦点距離ｆ₁および顕微鏡主対物レンズの焦点距離ｆ₂との間で、次の関係によって結びついている：
ｆ₂／ｆ₁＝β FIG. 5 shows the transition of the intensity distribution of the OCT scanning light beam 401 in the direction perpendicular to the OCT scanning plane 501. In the OCT scanning plane 501, the intensity distribution of the OCT scanning radiation has the smallest narrow part. Outside the range of the OCT scanning plane, the diameter of the OCT scanning optical path increases. Since the OCT scanning light beam 401 is emitted from the optical waveguide 151 of FIG. 4 with an approximately Gaussian radiation cross-sectional shape, the condenser lens 157 and the microscope main objective lens 101 are in the region of the OCT scanning plane 170 for the OCT scanning light beam. , Causing a so-called Gaussian beam 500 of the OCT scanning beam 401. The Gaussian light beam 500 is represented by the confocal parameter z as a guideline indicating the longitudinal length of the trunk portion of the Gaussian light beam, and as a guideline representing the diameter of the smallest narrow portion 502 of the OCT scanning light beam 401, that is, the trunk thereof. Characterized by the body parameter W as a measure of the diameter of the part, where:

Where λ is the wavelength of the OCT scanning beam. The following relationship holds between the body parameter W of the Gaussian beam 500 and the body parameter W ₀ of the scanning light beam 401 emitted from the optical waveguide 151 shown in FIG.
W = βW ₀
Here, β is an enlargement parameter or reduction parameter of the geometric imaging described above the exit end of the optical waveguide 151 in FIG. 1 in the OCT scanning plane. β is between the focal length f ₂ of the focal length f ₁ and a microscope main objective of the condenser lens 157 of FIG. 1, are linked by the following relationship:
f ₂ / f ₁ = β

  The size of the structure that can be resolved by the OCT scanning beam 401 is determined by its diameter in the OCT scanning plane 170, that is, by the body parameter W. For example, if an application requires a lateral resolution of about 40 μm for an OCT system in a surgical microscope, the Nyquist theorem requires that the cross-sectional area of the OCT scanning beam 401 at the surface be about 20 μm. Therefore, when the wavelength of the OCT scanning beam 153 shown in FIG. 1 is λ, the optical imaging magnification of the OCT optical path, the diameter of the fiber core of the optical waveguide 151, and the desired resolution of the OCT system 152 Must be selected appropriately.

  The confocal parameter z as a guide representing the longitudinal length of the body portion of the Gaussian beam determines a deep region in the axial direction in which the light backscattered in the OCT scanning optical path 153 in FIG. 1 can be detected. That is, the smaller the confocal parameter z, the greater the loss of the OCT system related to the lateral resolution at the distance from the object scanned with OCT scanning radiation to the OCT scanning plane 170. This is because the location of the scattering center can be specified only within the “funnel” determined by the body parameter W and the confocal parameter z.

On the one hand, the axial resolution of the OCT system is limited by the light coherence length l _c of the light source used in the OCT system, and on the other hand, the lateral resolution of the OCT system is such that its depth stroke is confocal parameter z It is advantageous to adjust the confocal parameter z for the depth stroke of the OCT system since it decreases beyond a given length.

  Then, for a specific wavelength λ of the OCT scanning beam 401, the possible lateral resolution of the OCT system of FIG. 1 is obtained. This is because the wavelength λ and the confocal parameter z specify the body parameter W. Then, the dimension setting of the optical system unit of the OCT scanning optical path 153 and the fiber core of the optical waveguide 151 shown in FIG. 1 can be selected so that the corresponding body parameter W is generated.

  The operating microscope 100 is designed so that the focal plane 170 of the microscope main objective 101 in the visible spectral region coincides with the OCT scanning plane 160. Then, the body portion 502 of the OCT scanning beam shown in FIG. 5 is located on the focal plane of the surgical microscope.

  Instead of such a design of a surgical microscope, an offset between the OCT scanning plane and the focal plane of the surgical microscope may be intended. Such an offset is preferably not larger than the confocal parameter z of the OCT scanning beam in the region of the OCT scanning plane. This makes it possible, for example, to visualize an object region located just below the focal plane of a surgical microscope by means of OCT. Alternatively, for certain applications, the confocal parameter may be used, for example, to allow the surface of the cornea of a patient's eye to be examined by a surgical microscope while simultaneously visualizing the back of the patient's eye cornea or its lens by an OCT system. It is meaningful to provide a fixed offset that exceeds.

  By moving the OCT scanning plane further away from the microscope main objective 101 of FIG. 1 by the Rayleigh parameter z, the depth stroke of the OCT system in the object region can be maximized.

  One modified embodiment of the surgical microscope 100 described with reference to FIG. 1 includes a focusable microscope main objective that is adjustable in focal length. This measure also allows displacement of the OCT scan plane and changes of the geometric imaging of the exit end of the optical waveguide in the OCT scan plane.

FIG. 2 is a surgical microscope with an illumination module incorporating an OCT system. FIG. It is sectional drawing which followed the II-II line | wire of FIG. 1 which shows a microscope main objective lens. This is the area of the lighting module that is equipped with the OCT system. It is an intensity distribution of the OCT scanning light beam emitted from the optical waveguide of the OCT system in the surgical microscope. It is an intensity distribution of the OCT scanning light beam in the OCT scanning plane of the object region of the surgical microscope.

Explanation of symbols

  DESCRIPTION OF SYMBOLS 100 Surgical microscope, 101 Microscope main objective lens, 108 Object area | region, 120 Illumination module, 124 Field stop, 125 1st lens group, 126 2nd lens group, 128 Input coupling member

Claims (18)

An observation optical path (105) for inspecting the object region (108);
An illumination optical system having a first lens group (125) and a second lens group (126) for forming a field stop (124) illuminated by a light source infinitely into a parallel illumination optical path; A lighting device (120);
An objective lens (101) disposed in a parallel illumination optical path to image the field stop (124) onto the object region (108);
An OCT system (152) for inspecting the object area (108),
The OCT system (152) is a surgical microscope (100) including an OCT scanning optical path (153) guided through the objective lens (101),
An input coupling member (128) for coupling the OCT scanning optical path to the illumination optical path is provided in the illumination optical path between the first lens group (125) and the second lens group (126). Features a surgical microscope.   The surgical microscope according to claim 1, wherein the input coupling member (128) is configured as a beam splitting mirror configured as a plane mirror or a beam splitting cube.   The objective lens arranged in a parallel observation optical path is configured as a microscope main objective lens (101), and the observation optical path (105, 105a, 105b) of the surgical microscope (100) passes therethrough. The surgical microscope according to claim 1 or 2.   A direction changing device (129, 130) for changing the direction of illumination light of the illumination device toward the objective lens (101) is provided on the opposite side of the object of the objective lens (101). The surgical microscope according to claim 3.   The surgical microscope according to claim 4, wherein the direction changing device is configured as a beam splitter through which the observation optical path of the surgical microscope passes.   The OCT system includes a first scan mirror (154) that is movable about a first axis of rotation (303) to scan the OCT scanning optical path. The surgical microscope according to any one of the preceding items.   A second scan mirror (155) that can be moved around a second rotation axis (304) is further provided, and the first rotation axis (303) and the second rotation axis (304) are The surgical microscope according to claim 6, wherein the surgical microscope is laterally offset and perpendicular to each other.   The OCT system includes a light guide (151) having a light exit area for the OCT scanning light path, and means are provided for moving the light exit area (174) of the light guide (151). The surgical microscope according to any one of claims 1 to 7, characterized in that   The OCT system includes a collimating optical system (157) that shifts the OCT scanning optical path to a substantially parallel scanning optical path together with the second lens group (126) of the illumination optical system. The surgical microscope according to any one of claims 1 to 8.   10. The means (171) for moving the collimating optics (157) to adjust the OCT scanning plane (170) of the OCT system (152). Surgical microscope. A surgical microscope illumination module (120) for connection to a surgical microscope (100) comprising:
A receiving portion (121) of the first optical waveguide (122) for providing illumination light (123);
A field stop (124) that can be illuminated with light derived from the optical waveguide (122);
An illumination optical system having a first lens group (125) and a second lens group (126) for imaging the field stop (120) infinitely into parallel imaging optical paths;
An illuminating mirror (128, 130) that serves to guide the illumination light emitted from the field stop (124) having a parallel imaging optical path to the object region 108 through the microscope main objective 101; Microscope illumination module for
To provide an OCT scanning optical path (153), a receiving part (150) for the second optical waveguide (151) of the OCT system (152) is provided,
The surgical microscope illumination module (120) is disposed between the first lens group (125) and the second lens group (126) that couples the OCT scanning optical path (153) to the illumination optical path. Surgical microscope illumination module, characterized in that it includes a structured input coupling member (128).   The surgical microscope illumination module according to claim 11, wherein the input coupling member (128) is configured as a beam splitting mirror configured as a plane mirror or a beam splitting cube.   The surgical microscope illumination module according to claim 11 or 12, wherein the surgical microscope illumination module includes a device (156) for scanning the OCT scanning optical path.   14. The apparatus (156) for scanning the OCT scanning optical path comprises a first scanning mirror (154) that can be moved about a first axis of rotation (303). The surgical microscope illumination module as described.   A second scan mirror (155) that can be moved around a second rotation axis (304) is provided, and the first rotation axis (303) and the second rotation axis (304) are on the side. The surgical microscope illumination module according to claim 14, wherein the surgical microscope illumination module is offset toward each other and is perpendicular to each other.   The OCT system includes a light guide (151) having a light exit area for the OCT scanning light path, and means are provided for moving the light exit area (174) of the light guide (151). The surgical microscope illumination module according to any one of claims 11 to 14, wherein the surgical microscope illumination module is provided.   The OCT system includes a collimating optical system (157) that shifts the OCT scanning optical path to a substantially parallel scanning optical path together with the second lens group (126) of the illumination optical system. The surgical microscope illumination module according to any one of claims 11 to 16.   18. A means (171) for moving the collimating optics (157) to adjust the OCT scanning plane (170) of the OCT system (152). Surgical microscope illumination module.

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