JP2008264490A - Operation microscope equipped with oct system - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a variable magnification operation microscope which detects a deep image of an object's region using an OCT scanning light path is configured compactly. <P>SOLUTION: The operation microscope 100 has an observation light path 109 that passes through a microscopic imaging optical system including a microscopic main objective lens system 101 and a magnification system 108 with variable magnification. The microscopic imaging optical system modifies a converging observation light path 109 originated from an object's region 114 into a parallel light path. The operating microscope includes an OCT system 120 for examining the object's region 114. The OCT system 120 provides an OCT scanning light path 190 guided through the microscopic imaging optical system. <P>COPYRIGHT: (C)2009,JPO&INPIT

Description

  The present invention includes a microscope imaging optical system including a microscope main objective lens system and a magnification system having a variable magnification, and an observation optical path passing through the microscope imaging optical system. The microscope imaging optical system is derived from an object region. The present invention relates to a surgical microscope provided with an OCT system for shifting a convergent observation optical path to a parallel optical path and inspecting an object region.

  A surgical microscope of the kind mentioned at the beginning is known from US Pat. This document describes a surgical microscope equipped with a microscope main objective lens through which a stereoscopic observation optical path passes, with a zoom system for a variable magnification. The surgical microscope includes an OCT system. The OCT system includes a module for generating an OCT scanning path from a short coherent laser beam with an analysis unit for evaluating interference signals. This module is accompanied by a device for scanning the OCT scanning optical path. In order to scan the surgical area with the OCT scanning beam path, the scanning device includes two scanning mirrors that can be adjusted about two axes of motion. In the surgical microscope described in Patent Document 1, the OCT scanning optical path is input coupled to the illumination optical path of the surgical microscope via a beam splitting mirror, and is guided to the object region through the microscope main objective lens.

Optical coherence tomography techniques allow non-invasive examination and measurement of structures inside biological tissues. Optical coherence tomography with a corresponding OCT system makes it possible, as an optical image generation method, 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.

  Patent Document 4 discloses a surgical microscope that enables an observer to inspect a surgical region with a stereoscopic observation optical path by looking into an eyepiece. The surgical microscope includes a device for data capture comprising a display and a beam splitter configured as a beam splitting cube. This beam splitter is the main body of the surgical microscope and is placed in the parallel observation optical path between the microscope main objective lens and eyepiece lens. It is superimposed on the parallel observation optical path in the microscope.

European Patent No. 0815801B1 US Pat. No. 5,321,501 International Publication No. 2006 / 10544A1 Pamphlet EP 1220004B1 specification

  An object of the present invention is to detect a deep image of an object region using an OCT scanning optical path, and the transition of the OCT scanning optical path causes an enlarged image of the object region for an observer looking into the eyepiece. A surgical microscope with a variable magnification ratio and a compact construction that matches the transition of the optical observation optical path in the microscope and is adapted to the selected magnification for the cross section of the OCT scanning optical path in the object region. Is to provide.

  This problem is solved by a surgical microscope of the kind mentioned at the outset, in which the OCT system is provided with an OCT scanning beam path guided through the microscope imaging optics.

  In this way, it is ensured that the optical observation beam path and the OCT scanning radiation cover the same zone of the object area, especially in the case of an uneven object area. That is, the observation image itself displayed on the observer looking into the binocular tube of the surgical microscope can be scanned by OCT scanning radiation. At this time, it is possible to detect a deep section of the object region that relies on OCT scanning radiation.

  In the development of the present invention, an input coupling member is provided for guiding the OCT scanning optical path to the observation optical path, thereby superimposing the OCT scanning optical path on the observation optical path and guiding it to the object region through the microscope imaging optical system. It is done. The input coupling member is configured as a beam splitting mirror, particularly preferably as a plane mirror or a beam splitting cube. In this way, the simultaneous observer can always keep the field of view to the object area open.

  In the development example, an output coupling member is disposed between the microscope imaging optical system and the input coupling member in order to output-couple image information from the observation optical path.

  In a development of the invention, an infinite focus lens system, especially configured as a zoom system, is arranged between the input coupling member and the microscope main objective. In this way, it is possible to change the lateral resolution of the OCT information that can be acquired by the OCT system while adapting it in accordance with the observation image displayed to the observer looking into the eyepiece of the surgical microscope.

  In a development of the invention, the OCT system includes a first scan mirror for scanning the OCT scanning optical path. In addition to this, a second scan mirror is preferably provided, in which case the first scan mirror can be moved about the first axis of rotation and the second scan mirror is the second scan mirror. It can be moved around the rotation axis. The first and second rotation axes are offset laterally and are perpendicular to each other. In this way, it is possible to scan the object region according to the mesh pattern extending vertically.

  In a development of the invention, the OCT system includes an optical waveguide having a light exit area for the OCT scanning optical path, and means are provided for moving the light exit area of the optical waveguide. In this way, the OCT scanning plane can be changed in the object region and adjusted to different OCT wavelengths, taking into account the optical components designed for visible light in the observation beam path for simultaneous observation. It is possible to adjust the system.

  In a development of the invention, the OCT scanning optical path is provided with a position-adjustable optical system for adjusting the geometric imaging of the exit end of the optical waveguide onto the OCT scanning plane. In this way, the OCT scanning plane of the surgical microscope can be displaced relative to the observation plane of the optical observation optical path of the system, and the imaging magnification of the microscope imaging optical system is adjusted. Sometimes it is possible to readjust the imaging magnification of the OCT scanning radiation so that the imaging magnification in the optical observation optical path matches the imaging magnification in the OCT scanning optical path. In this way, there is an advantage that the corresponding imaging magnification can be kept the same.

  In a development of the invention, the position-adjustable optical member is accompanied by a drive unit. In this way, for example, the OCT scanning plane can be changed by a predetermined value relative to the observation plane of the surgical microscope.

  In a development of the invention, the OCT system provides a first OCT scanning beam having a first wavelength and a second OCT scanning beam having a second wavelength different from the first wavelength. Designed to provide In this way, the surgical microscope can be optimized to examine the various tissue structures and body organs of the patient.

  In a development of the invention, first and second OCT systems are provided that provide OCT scanning rays of different wavelengths. In this way, inspection of object areas based on different OCT wavelengths is possible with maximum resolution. In particular, it allows examination of tissue at various penetration depths using an OCT scanning beam. Furthermore, it is possible to design a surgical microscope for various uses.

  In a development of the invention, a coupler between the microscope imaging optics and the OCT system is used to adjust the corresponding change in the optical path length in the OCT system when the working interval of the surgical microscope changes. Provided. In this way, it is ensured that the object region that is clearly imaged by the microscope imaging optical system can also be scanned by the OCT system.

  In a development example of the present invention, in order to make the imaging magnification in the optical observation optical path and the imaging magnification in the OCT scanning optical path compatible with each other, a coupler of the microscope imaging optical system and the collimating optical system of the OCT system is provided. Provided. In this way, it is ensured that the OCT scanning optical path scans the observation area that can be seen in 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 includes a microscope main objective lens system 101 that includes an optical axis 102 and a focal plane 103 that can be displaced correspondingly, and that can be focused by an actuator 150. The microscope main objective lens system 101 includes partial optical systems 151, 152, and 153. The stereoscopic observation optical path of the binocular tube 104 and the illumination optical path 105 of the illumination device 106 including the illumination mirror 107 pass through the microscope main objective lens system. This illumination mirror is arranged on the opposite side to the object of the microscope main objective lens system 101.

  The binocular tube 104 is accompanied by a zoomable enlargement system 108. The microscope main objective lens system 101 and the zoomable enlargement system 108 form the microscope imaging optical system of the surgical microscope 100. FIG. 1 shows an observation optical path 109 on the right side of the stereoscopic observation optical path in the surgical microscope 100.

  Between the binocular tube 104 and the zoomable magnifying system 108, a first beam splitting cube 112 composed of right angle prisms 110, 111 is in the parallel right observation beam path 109. The same beam splitting cube as the first beam splitting cube 112 is arranged at a corresponding position in the parallel left observation optical path. The first beam splitting cube 112 and the second beam splitting cube have a dual function. That is, they act as an input coupling member that inputs and couples the display of the first display 113 in the observation optical path 109 on the right side and the left observation optical path of the surgical microscope and the display of the second display not shown in FIG. To do.

  That is, the display on the first display 113 and the second display is superimposed on the image of the object region 114 in the binocular tube 104. At the same time, the first beam-splitting cube 112 and the second beam-splitting cube act as members for coupling the OCT scanning optical path 190 provided by the first OCT system 120.

  The surgical microscope 100 includes a first OCT system 120 for capturing an OCT image. The OCT system includes a unit 121 for generating and analyzing an OCT scanning optical path 190 emitted from the optical waveguide 122. The scanning optical path 190 emitted from the optical waveguide 122 is guided to the first scan mirror 124 and the second scan mirror 125 of the OCT scan unit 126, and is provided with a lens 131 and a lens 132 after the OCT scan unit 126. Pass through the possible collimating optics 130. The collimating optical system 130 has a driving device 133 and focuses the scanning light path 190 into a parallel light beam 140.

  Of course, it is also possible to deflect the parallel OCT scanning optical path by the first scanning mirror 124 and the second scanning mirror 125 of the OCT scanning unit 126. For this purpose, an appropriate collimating optical system, for example, a condensing lens, disposed between the optical waveguide 122 and the OCT scan unit 126 is required. In that case, the collimating optical system 130 on the side opposite to the optical waveguide of the OCT scan unit 126 is not necessary.

  The light beam 140 derived from the OCT scan unit 126 is guided to the beam splitting cube 112 in the observation optical path 106. The beam splitting cube 112 is substantially transparent to the spectral region of the observation light in the observation optical path that is visible to the human eye. Conversely, the beam splitting cube reflects the light in the OCT scanning optical path and superimposes it on the observation optical path 106. It should be noted that the beam splitting cube 112 may be manufactured as a mirror member having a plane parallel plate.

  The light in the OCT scanning optical path 190 is focused on the OCT scanning plane 195 by the microscope main objective lens 101. The OCT scanning plane 195 is formed by an optical member of the OCT scanning optical path including the OCT scanning unit 126, the condensing lens 130, the beam splitting cube 112, and the microscope main objective lens 101. It is a plane imaged on. That is, the corresponding geometrical image of the exit end of the optical waveguide is located in the OCT scan plane 195.

  The light bounced back to the OCT scanning optical path returns to the unit 121 via the microscope main objective lens 101, the zoomable magnification system 108, and the beam splitting cube 112. Thus, the OCT scanning light backscattered from the object region 114 is interfered with by OCT radiation originating from the reference optical path. The interference signal is detected by a detector and evaluated by a computer unit which, based on this signal, provides an optical signal between the scattering center of the OCT light in the object region 114 and the light path length in the reference shunt. The difference in path length is calculated.

  When the operation interval 180 of the surgical microscope 100 is changed by adjusting the position of the microscope main objective lens system 101, the optical path length of the scanning optical path of the corresponding OCT system in the surgical microscope is also changed. The actuator 150 of the focusable microscope main objective lens system 101 is electrically connected to an OCT system in the surgical microscope via a signal line 185. This causes a coupling between the OCT system and the microscope main objective system, and thus in the OCT system, if necessary, if the operating interval 180 of the surgical microscope from the object region 114 changes. The optical path length of the reference optical path is adapted accordingly.

  There is an output coupling member 141 between the zoomable magnifying system 108 and the beam splitting cube 112 to supply image information originating from the object area 114 to the recording unit.

  FIG. 2 is a cross-sectional view taken along the line II-II in FIG. This drawing explains the transition of the stereoscopic observation optical path of the surgical microscope 100 of FIG. The optical axis 102 of the microscope main objective 101 is located at the center thereof. The observation light path 109 on the right side and the observation light path 110 on the left side pass through the microscope main objective lens 101 in cross-sectional areas 201, 202, 203 separated from each other together with the illumination light path 105 whose direction is changed by the illumination mirror 107.

FIG. 3 shows the first OCT system 120 and the second OCT system 320 in the surgical microscope 100 of FIG. Similar to the first OCT system 120, the second OCT system 320 includes a unit 321 for generating and analyzing an OCT scanning optical path. However, the wavelength regions of the OCT scanning optical paths of both OCT systems 120 and 320 are different. That is, the first OCT system relies on OCT scanning radiation of wavelength λ ₁ = 1310 nm. The second OCT system 320 operates with OCT scanning radiation at a wavelength λ ₂ = 800 nm. Of course, the OCT system can be designed for other operating wavelengths. The operating wavelength can be embodied in particular within the range of 600 nm <λ <1500 nm, preferably each depending on the application.

  The OCT scanning optical path 190 of the first OCT system 120 is input coupled to the first beam splitting cube in the observation optical path on the right side of the surgical microscope 100 via the condenser lens 130, and the second OCT system 320. The OCT scanning optical path 390 is superimposed on the second beam splitting cube in the observation optical path on the left side of the surgical microscope 100 via the second condenser lens.

  For this purpose, the OCT system 320 includes an OCT scan unit 326 that includes scan mirrors 324 and 325 and a condensing lens 330 that condenses the light in the OCT scanning optical path 390 into a parallel light beam, similar to the OCT system 120. Yes.

  The first scan mirrors 124 and 324 and the second scan mirrors 125 and 325 of the OCT system 120 and 320 have two axes 305, 306, 307, and 308 extending perpendicular to each other by actuators 301, 302, 303, and 304. It is arranged so that it can rotate as a center. This makes it possible to scan the OCT scanning optical paths 190, 390 in one plane independently of each other.

  In order to allow the operator to adjust the OCT scanning plane with respect to the object plane of the optical observation optical path of the surgical microscope 100 shown in FIG. 1, the exit ends of the condenser lenses 131 and 331 and the optical waveguides 127 and 327 A position adjustment possibility of 133,333 is intended. For this purpose, drive units 371, 372, 373 and 374 are assigned to the condenser lenses 131 and 331 and the optical waveguides 127 and 327, respectively. By these drive units, the condenser lenses 131 and 331 and the optical waveguides 127 and 327 can be displaced as indicated by double arrows 374, 375, 376, and 377. Thereby, in particular, not only the position of the OCT scanning plane can be changed, but also the exit ends of the optical waveguides 127 and 327 can be enlarged or reduced in accordance with a desired value.

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。したがって光導波路１２７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１２７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Ｗ₁と開口パラメータθ₁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１２７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 127 of FIG. The optical waveguide 127 acts as a monomode fiber for light with a wavelength λ ₁ = 1310 nm. The diameter d of the fiber core of the optical waveguide 127 is:

Where NA is the numerical aperture of the front surface of the optical waveguide. Therefore, the diameter d of the fiber core of the optical waveguide 127 is preferably in the range of 5 μm <d <10 μm. Within this parameter range, the optical waveguide 127 guides light in a Gaussian wavelength mode. The OCT scanning light beam 401 is emitted from the optical waveguide 127 with an approximately Gaussian radiation cross-section characterized by the body parameter W ₁ and the aperture parameter θ _1, and at this time, the following equation is established.

Therefore, for a fiber core diameter of d ₁ = 10 μm and a wavelength of λ ₁ = 1310 nm, an opening angle of θ ₀ ≈0.0827 rad is obtained as a guideline representing light divergence.

  The front surface 402 of the optical waveguide 122 is OCT scanned via the scan mirrors 124 and 125, the condensing lens 130, the beam splitting mirror 150, the reflecting mirror 107, and the microscope main objective lens system 101 in the surgical microscope 100 shown in FIG. An image is formed on the plane 195 in the object region 108.

ここでλ₁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１２２から射出される走査光線４０１の胴部パラメータＷ₁との間には、次の関係が成り立つ：
Ｗ＝βＷ₁
ここでβは、ＯＣＴ走査平面における図１の光導波路１２２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のコリメート光学系１３０の焦点距離ｆ₁と、顕微鏡主対物レンズ系１０１と拡大システム１０８とを備える顕微鏡結像光学系の焦点距離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 beam 401 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 122 of FIG. 4 in an approximately Gaussian radiation cross-sectional shape, the condenser lens 130 and the microscope main objective lens system 101 are regions of the OCT scanning plane 195 for the OCT scanning light beam. Thus, a so-called Gaussian light beam 500 of the OCT scanning light beam 401 is caused. The Gaussian light beam 500 is used as a standard representing the diameter of the smallest narrow portion 502 of the OCT scanning light beam 401 by the confocal parameter z as a standard representing the longitudinal length of the body part of the Gaussian light beam. Characterized by the body parameter W as a measure of the diameter of the part, where:

Here, λ ₁ 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 ₁ of the scanning light beam 401 emitted from the optical waveguide 122 shown in FIG.
W = βW ₁
Here, β is an enlargement parameter or reduction parameter of the geometric imaging described above the exit end of the optical waveguide 122 in FIG. 1 in the OCT scanning plane. β is between the focal length f ₁ of the collimating optical system 130 of FIG. 1, the focal length f ₂ of the microscope imaging optical system comprises a microscope main objective system 101 and magnification system 108, associated by the following relationship ing:
f ₂ / f ₁ = β

  The position-adjustable collimating optical system of the OCT system makes it possible to adapt the imaging parameter β of the corresponding OCT optical path in response to changes in the imaging magnification of the microscope imaging optical system. For this adaptation, the respective respective imaging magnifications are preferably chosen equally.

  Thereby, the specific scan pattern of the OCT scanning optical path is automatically adapted to the observation image presented to the observer when looking into the eyepiece of the surgical microscope 100 in FIG. Is done.

  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 195, 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 123 shown in FIG. 1 is λ, for the desired resolution of the OCT system 120, the optical imaging magnification of the OCT optical path, the diameter of the fiber core of the optical waveguide 122, and Must be selected appropriately.

  The confocal parameter z as a guide indicating the longitudinal length of the body portion of the Gaussian light beam determines an axial depth region in which light backscattered in the OCT scanning optical path 190 of FIG. 1 can be detected. That is, the smaller the confocal parameter z, the greater the loss of the OCT system associated with lateral resolution at the distance from the object scanned with OCT scanning radiation to the OCT scanning plane 195. 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 has its depth stroke exceeding the confocal parameter. Therefore, it is advantageous to adjust the confocal parameter z according to the depth stroke of the OCT system.

  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 Rayleigh parameter z determine the body parameter W. Then, the dimension setting of the optical system unit of the OCT scanning optical path 190 and the fiber core of the optical waveguide 122 shown in FIG. 1 can be selected so that the corresponding body parameter is generated. The same is true for the optics unit in the OCT scanning path of the second OCT system 320 of the surgical microscope.

  The surgical microscope 100 shown in FIG. 1 is designed so that the focal plane 103 of the microscope main objective lens 101 in the visible spectral region coincides with the OCT scanning plane 195 of the OCT system of the surgical microscope. Then, the corresponding OCT scanning beam barrel 502 shown in FIG. 5 is located at 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 greater than the confocal parameter of the OCT scan beam in the region of the OCT scan 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 further moving the OCT scanning plane away from the microscope main objective system 101 of FIG. 1 by the confocal parameter z, the depth stroke of the OCT system in the object region can be maximized.

1 is a first surgical microscope incorporating an OCT system. It is sectional drawing which followed the II-II line | wire of FIG. 1 which shows the microscope main objective lens of a surgical microscope. FIG. 3 is an area of a surgical microscope equipped with first and second OCT systems. 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 Operating microscope, 101 Microscope main objective lens system, 108 Magnification system, 109 Observation optical path, 114 Object area | region, 120 OCT system, 190 OCT scanning optical path

Claims (17)

A microscope imaging optical system (including a microscope main objective lens system (101) and a magnification system (108) having a variable magnification ratio) that shifts the convergent observation optical path (109) derived from the object region (114) to a parallel optical path ( 101, 108)
An observation optical path (109) for inspecting an object region passing through the microscope imaging optical system (101, 103);
A surgical microscope (100) provided with an OCT system (120, 320) for inspecting an object region (114),
The surgical microscope characterized in that the OCT system (120, 320) provides an OCT scanning optical path (190, 390) guided through the microscope imaging optical system (101, 108).   The OCT scanning optical path (190, 390) is input-coupled to the observation optical path (109, 110) so that it is superimposed on the observation optical path (109) and then passed through the microscope imaging optical system (114). The surgical microscope according to claim 1, further comprising an input coupling member (112) for guiding to ().   A display indicator (113) is provided, and the input coupling member (112) for the OCT scanning optical path (190, 390) acts as an input coupling member for display information and the observation optical path (109). 4. The surgical microscope according to claim 3, wherein display information is superimposed on the surgical information.   The surgical microscope according to claim 2 or 3, wherein the input coupling member (112) is configured as a plane splitting mirror or a beam splitting mirror configured as a beam splitting cube.   An output coupling member (141) for coupling image information from the observation optical path (109) is disposed between the microscope imaging optical system (101, 108) and the input coupling member (112). The surgical microscope according to any one of claims 2 to 4, wherein   The surgical microscope according to any one of claims 1 to 5, wherein the magnifying system of the microscope imaging optical system is configured as an infinite focus lens system (108).   The surgical microscope according to claim 6, characterized in that the afocal lens system is configured as a zoom system (108).   The OCT system (120) includes a first scan mirror (124) that can be moved about a first axis of rotation (306) to scan the OCT scan path (190). The surgical microscope according to any one of claims 1 to 7.   A second scan mirror (125) that can be moved about the second rotation axis (306) is further provided, and the first rotation axis (306) and the second rotation axis (305) are provided. The surgical microscope according to claim 8, wherein the surgical microscope is laterally offset and perpendicular to each other.   The OCT system includes a light guide (127, 327) having a light exit area (402) for the OCT scanning light path (190, 390), and the light exit area ( The operating microscope according to any one of claims 1 to 9, characterized in that means (371, 372) for moving 402) are provided.   11. The OCT system according to any one of claims 1 to 10, characterized in that it comprises a collimating optical system (130) for supplying a parallel scanning optical path (109) to the input coupling member (112). Surgical microscope.   A position-adjustable optical system for adjusting the geometric imaging of the exit end (402) of the optical waveguide (127, 327) to the OCT scanning plane (195) in the OCT scanning optical path (190) The surgical microscope according to any one of claims 1 to 11, wherein (130, 131, 331) is provided.   The surgical microscope according to claim 12, wherein a drive unit (373, 374) is attached to the optical system (130, 131, 331) capable of adjusting the position.   The OCT system is designed to provide a first OCT scan beam having a first wavelength and to provide a second OCT scan beam having a second wavelength different from the first wavelength. The surgical microscope according to any one of claims 1 to 13, wherein the surgical microscope is provided.   15. A first OCT system (120) and a second OCT system (320) are provided to provide OCT scanning beams (190, 390) of different wavelengths. The surgical microscope according to any one of the above.   In order to adjust the corresponding change in the optical path length of the reference optical path in the OCT system (120, 320) when the working interval (180) of the surgical microscope (100) changes, the microscope imaging The surgical microscope according to any one of claims 1 to 15, wherein a coupler for an optical system (101, 108) and the OCT system (120, 320) is provided.   In order to mutually adapt the imaging magnification in the optical observation optical path (109) of the surgical microscope (100) and the imaging magnification in the OCT scanning optical path (190), the microscope imaging optical system (101, A surgical microscope according to any one of claims 1 to 16, characterized in that a coupler between 108) and the collimating optics (130) of the OCT system (120) is provided.

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