JP5188146B2 - Surgical microscope with OCT system - Google Patents

Description

  The present invention relates to a surgical microscope including an observation optical path and a microscope main objective lens through which the observation optical path passes.

  A surgical microscope of the kind mentioned at the beginning is known from US Pat. This document describes a surgical microscope including a binocular tube for main observation and a binocular tube for simultaneous observation. A binocular tube for simultaneous observation and a binocular tube for simultaneous observation are arranged in a common surgical microscope main body. The binocular tube for simultaneous observation and the binocular tube for simultaneous observation have a stereoscopic observation optical path. These stereoscopic observation optical paths pass through a common microscope main objective lens.

  Patent Document 2 describes a surgical microscope including an OCT system.

The OCT system allows non-invasive display and measurement of tissue internal structures using optical coherence tomography. Optical coherence tomography is an optical image generation method that 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, for example, Patent Document 3 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 4, 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 Fourier 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 a 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.

  The OCT system for a surgical microscope described in US Pat. No. 6,057,059 includes a module for generating an OCT scanning path from a short coherent laser beam, which includes 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 2, the OCT scanning optical path is input-coupled to the illumination optical path of the surgical microscope via a beam splitting mirror, and thereby guided through the microscope main objective lens toward the object region. Is done.

German Patent Application No. 102004049368A1 European Patent No. 0815801B1 US Pat. No. 5,321,501 International Publication No. 2006 / 10544A1 Pamphlet

  An object of the present invention is to enable detection of a deep image of an object region with a surgical microscope.

  This problem is solved by a surgical microscope of the type mentioned at the beginning, including an OCT system for inspecting object areas, the OCT system having an OCT scanning optical path guided through the microscope main objective lens, An input coupling member is provided in the observation optical path for coupling the scanning optical path to the observation optical path and guiding it to the object region through the microscope main objective lens.

  In this way, it is possible to incorporate the OCT system into the surgical microscope without causing vignetting in the optical optical path in the surgical microscope or causing image cutting.

  In a development of the invention, the input coupling member is configured as a beam splitting mirror, in particular 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 a development of the invention, the surgical microscope includes an observation optical path for main observation through the microscope main objective and an observation optical path for simultaneous observation, and the input coupling member is in the observation optical path for simultaneous observation. Has been placed.

  In the development example of the present invention, in order to shift the parallel observation optical path to the intermediate image, an optical system module is arranged in the observation optical path for simultaneous observation. In this case, the input coupling member in the observation optical path for simultaneous observation is disposed between the optical system module and the microscope main objective lens. Alternatively, the input coupling member may be provided between the optical system module and the intermediate image.

  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 rotational 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 an optical member whose position can be adjusted in order to adjust the geometric imaging of the exit end of the optical waveguide on 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.

  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 optical path having a first wavelength and a second OCT scanning optical path having a second wavelength different from the first wavelength. Designed to provide you with. 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 in which OCT scanning beams of different wavelengths are provided. In this way, inspection of object areas based on different OCT wavelengths is possible with maximum resolution.

In a development of the invention, the OCT scanning beam of the first OCT system is at least partially superimposed on the right stereoscopic viewing optical path, and the OCT scanning beam of the second OCT system is at least partially on the left stereoscopic viewing optical path. These optical paths pass through the microscope main objective in different areas. In this case, the first OCT system preferably provides an OCT scanning beam with a wavelength λ ₁ = 1300 nm, and the second OCT system preferably provides an OCT scanning beam with a wavelength λ ₂ = 800 nm. In this way, the layer structure of the cornea and the structure of the retina in the patient's eye can be examined simultaneously with a surgical microscope.

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

  A surgical microscope 100 in FIG. 1 has a microscope main objective lens 101 having an optical axis 102. The microscope main objective lens 101 has a focal plane 170, and the stereoscopic observation optical path of the binocular tube 103 for main observation and the stereoscopic observation optical path of the binocular tube 104 for simultaneous observation pass. A zooming magnification system 105 is attached to the binocular tube 103 for main observation. FIG. 1 shows an observation optical path 106 on the right side of the stereoscopic observation optical path of the binocular tube for simultaneous observation. This observation optical path is guided to the object region 108 by the reflecting mirror 107 disposed on the opposite side of the object region 108 of the microscope main objective lens 101. The observation optical path 106 has a lens system 109. The lens system 109 converges the light of the observation optical path 106 that passes through the microscope main objective lens from the object region 108 and becomes parallel after passing through the microscope main objective lens 101, and the binocular tube 104 for simultaneous observation. An intermediate image 110 is obtained.

  The surgical microscope 100 includes an OCT system 120 for capturing an OCT image. The OCT system includes a unit 121 for generating and analyzing an OCT scanning optical path. The unit 121 is integrated with the surgical microscope 100. Alternatively, this unit can be arranged outside the surgical microscope, for example on a corresponding tripod. The unit 121 is connected to the optical waveguide 122. Through this optical waveguide 122, the unit 121 provides an OCT scanning optical path. The scanning optical path 123 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 passes through the condenser lens 130 after the OCT scan unit 126. The condenser lens 130 converges the light in the scanning optical path 123 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 condenser lens disposed between the optical waveguide 122 and the OCT scan unit 126 is required. In that case, the condensing lens 130 on the side opposite to the optical waveguide of the OCT scan unit 126 is unnecessary. The light beam 140 derived from the OCT scan unit 126 is guided to the beam splitting mirror 150. The beam splitting mirror 150 is disposed in the observation optical path 106. The beam splitting mirror 150 is substantially transparent to the spectral region visible to the human eye of the observation light in this observation optical path. Conversely, the beam splitting mirror reflects the light in the OCT scanning optical path and superimposes it on the observation optical path 106. The beam splitting mirror 150 may be manufactured as a mirror member having a plane parallel plate or as a beam splitting cube.

  The light in the OCT scanning optical path 123 is focused on the OCT scanning plane 160 by the microscope main objective lens 101. The OCT scanning plane 160 is formed by an optical member of an OCT scanning optical path including an OCT scanning unit 126, a condensing lens 130, a beam splitting mirror 150, a reflecting mirror 107, and a microscope main objective lens 101, and the optical waveguide 123 is emitted to an object region. An end 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 160.

  The light bounced back to the OCT scanning optical path returns to the unit 121 via the reflecting mirror 107 and the beam splitting mirror 150. 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 explains the transition of the stereoscopic observation optical path derived from the binocular tube 103 and the binocular tube 104 of the surgical microscope 100 of FIG. The optical axis 102 of the microscope main objective 101 is located at the center thereof. The stereoscopic light path for the main observations 201 and 202 and the stereoscopic light path for the simultaneous observations 203 and 206 pass through the microscope main objective lens 101 in cross-sectional areas separated from each other.

  FIG. 3 shows the scan mirror unit 126 of the surgical microscope 100 of FIG. The first scan mirror 124 and the second scan mirror 125 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１２２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 122 of FIG. The optical waveguide 122 acts as a monomode fiber for light with 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 122 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 λ ₀ = 1310 nm, an opening angle of θ ₀ ≈0.0827 rad is obtained as a guideline representing beam divergence.

  The front surface 402 of the optical waveguide 122 is an OCT scanning plane 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 101 in the surgical microscope 100 shown in FIG. The image is formed on the object region 108 to 160.

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１２２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の集光レンズ１３０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 intensity transition of the OCT scanning light 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 101 are in the region of the OCT scanning plane 160 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 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:

Where λ is the wavelength of the OCT scanning beam. The following relationship holds between the trunk parameter W of the Gaussian beam 500 and the trunk parameter W ₀ of the scanning light beam 401 emitted from the optical waveguide 122 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 122 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 130 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 160, 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, the optical imaging magnification and the diameter of the fiber core of the optical waveguide 122 are appropriately set for the desired resolution of the OCT system 120. Must be selected.

  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 the light backscattered in the OCT scanning light path 123 of FIG. 1 can be detected. That is, the smaller the confocal parameter z, the greater the loss of the OCT system associated with the lateral resolution at the distance from the object scanned with OCT scanning radiation to the OCT scanning plane 160. 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 determine the body parameter W. Then, the dimension setting of the optical system unit of the OCT scanning optical path 123 shown in FIG. 1 and the fiber core of the optical waveguide 122 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.

  FIG. 6 shows yet another surgical microscope 600 that incorporates an OCT system 620. In the case where the module of the surgical microscope 600 matches the module of the surgical microscope 100 shown in FIG. 1, the number obtained by adding the numeral 500 to FIG.

  Unlike the case of the surgical microscope 100 shown in FIG. 1, the surgical microscope 600 has a beam-splitting mirror in the convergent observation optical path between the lens barrel lens system 609 and the intermediate image 610 of the object region generated thereby. 650 is provided. The OCT system 620 includes a unit 621 for generating an OCT scanning beam path 623 in two different wavelength regions, ie, generating an OCT scanning beam having a wavelength λ = 800 nm and an OCT scanning beam having a wavelength λ = 1310 nm. can do.

  The OCT scanning optical path 623 emitted from the optical waveguide 622 is guided to the scan mirror unit 626 including the scan mirrors 624 and 625 through the first OCT lens system 630, and the second OCT lens from the scan mirror unit 626. The system 631 is reached. The OCT lens systems 630 and 631 cause an intermediate image 632 at the exit end of the optical waveguide at a plane 633 conjugate with the OCT scanning plane 660 in the object region 608.

  In order to allow the operator to adjust the OCT scanning plane 660 relative to the object plane 608 of the optical observation optical path of the surgical microscope 600, the position of the exit end of the lens systems 630, 631 and the optical waveguide 622 can be adjusted. Is intended. For this purpose, the surgical microscope 600 includes drive units 671, 672, 673 assigned to the lens systems 630, 631 and the optical waveguide 622. By the drive units 671, 672, and 673, the lens systems 630 and 631 and the optical waveguide 622 can be displaced as indicated by double arrows 674, 675, and 676. In particular, not only can the position of the OCT scanning plane 660 be changed, but also the exit end of the optical waveguide 622 can be enlarged or reduced to a desired value.

  A modified embodiment of the surgical microscope 600 described with reference to FIG. 6 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.

  In displacing the OCT scan plane of the OCT system 620 of the surgical microscope 600, the reference beam path of the system (not shown) is readjusted so that the reference beam path is always adapted to the set OCT scan plane. It is preferable to do so.

  FIG. 7 shows an area 700 of a third surgical microscope in which two OCT systems 720, 780 are provided. This surgical microscope also has a microscope main objective lens 701 having an optical axis 702. The objective lens 701 transmits left and right stereoscopic observation optical paths 703 and 704 for main observation, and left and right stereoscopic observation optical paths 705 and 706 for simultaneous observation. Stereoscopic observation optical paths 705 and 706 for simultaneous observation are guided to the object region 708 by a reflecting mirror 707 disposed on the opposite side of the object region 708 of the microscope main objective lens 701.

OCT systems 720 and 780 include units 721 and 781, respectively, for generating and analyzing OCT scanning light paths. These units 721 and 781 provide the first OCT scanning beam 723 and the second OCT scanning beam 783 at different wavelengths λ ₁ and λ ₂ via the optical waveguides 722 and 782. The OCT scanning light beams 723 and 783 are guided toward the beam splitting mirror 750 through OCT scanning units 726 and 776 including condensing lenses 730 and 731 and a scanning mirror.

  The beam splitting mirror 750 is disposed in the stereoscopic observation optical paths 705 and 706 for simultaneous observation. This beam splitting mirror is substantially transparent to the spectral region of the observation light visible to the human eye, but reflects the OCT scanning rays 723 and 783 so that these OCT scanning rays are observed in the observation optical path 705. The microscope main objective lens 701 is passed therewith.

  The light bounced from the object region 708 to the OCT scanning optical paths 723 and 783 is evaluated by units 721 and 781 for generating and analyzing the corresponding OCT scanning optical paths.

The use of two OCT systems makes it possible to scan the object area with different wavelengths of OCT light, and for each OCT scanning path, wavelengths λ ₁ , λ ₂ and confocal parameters z ₁ , z ₂ and torso parameters W ₁ and W ₂ can be best selected for maximum resolution.

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 a microscope main objective lens. This is the area of the OCT system in a surgical microscope. 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. Fig. 2 is a second surgical microscope incorporating an OCT system. FIG. 6 is a partial view showing a third surgical microscope in which two OCT systems are incorporated.

Explanation of symbols

  DESCRIPTION OF SYMBOLS 100 Surgical microscope, 101 Microscope main objective lens, 106 Observation optical path for simultaneous observation, 108 Object region, 120 OCT system, 123 OCT scanning optical path, 150 Input coupling member

Claims (13)

An observation optical path (106, 203, 606, 705, 706);
A surgical microscope (100, 600, 700) comprising a microscope main objective lens (101, 601, 701) through which the observation optical path (106, 203, 606, 705, 706) passes,
The surgical microscope includes an OCT system (120, 620, 720, 780) for inspecting an object region (108, 608, 708);
The OCT system (120, 620, 720, 780) has an OCT scanning optical path (123, 623, 723, 783) guided through the microscope main objective lens (101, 601),
The OCT scanning optical path (123, 623, 723, 783) is coupled to the observation optical path (106, 606, 705, 706), and the object region (108, 608) is passed through the microscope main objective lens (101, 601, 701). , 708) are provided with input coupling members (150, 650, 750) in the observation optical path (106) ,
A first OCT system (720) and a second OCT system (780) are provided to provide OCT scanning beams (723, 783) of different wavelengths,
The OCT scanning beam (723) of the first OCT system (720) is at least partially superimposed on the right stereoscopic viewing optical path (705) and together, the microscope main objective of the surgical microscope (700) (701), the OCT scanning beam (783) of the second OCT system (780) is at least partially superimposed on the left stereoscopic viewing optical path (706), and together the surgical microscope (700) A surgical microscope characterized by passing through the microscope main objective lens (701) .   The surgical microscope according to claim 1, wherein the input coupling member is configured as a beam splitting mirror (150, 650, 750) configured as a plane mirror or a beam splitting cube.   An observation optical path (201, 202, 703, 704) for main observation and an observation optical path (106, 203, 606, 705, 706) for simultaneous observation are provided, both of which are the microscope main objective lens. (101, 601, 701), and the input coupling member (150, 650, 750) is disposed in the observation optical path (106, 203, 606, 705, 706) for simultaneous observation. The surgical microscope according to claim 1, wherein the surgical microscope is characterized.   An optical system module (109, 609) is arranged in the observation optical path (106, 606) for simultaneous observation in order to shift the parallel observation optical path to the intermediate image (110, 610). The surgical microscope according to claim 3.   The input coupling member (150) is disposed between the optical system module (109) and the microscope main objective lens (101) in the observation optical path (106) for simultaneous observation. The surgical microscope according to claim 4.   The input coupling member (650) is disposed between the optical system module (609) and the intermediate image (610) in the observation optical path (606) for simultaneous observation. The surgical microscope according to claim 4.   The OCT system (120, 620) for scanning the OCT scanning optical path includes a first scan mirror (124, 624) that can be moved about at least one first rotation axis (303). The surgical microscope according to any one of claims 1 to 6, wherein the surgical microscope is provided.   A second scan mirror (124, 125, 624, 625) that can be moved about the second rotation axis (304) is further provided, and the first rotation axis (303) and the second rotation mirror (304) are provided. The surgical microscope according to claim 7, characterized in that the rotation axes (304) are offset laterally and are perpendicular to each other.   The OCT system (120, 620) includes a light guide (122, 622) having a light exit area for an OCT scanning path, and means for moving the light exit area of the light guide is provided. The surgical microscope according to any one of claims 1 to 8, wherein   Positionable optical members (630, 631) in the OCT scanning optical path (623) to adjust the geometric imaging of the exit end of the optical waveguide (622) onto the OCT scanning plane (660). The surgical microscope according to claim 1, wherein the surgical microscope is provided.   The surgical microscope according to claim 10, wherein a drive unit (672, 673) is attached to the optical member (630, 631) capable of adjusting the position.   The OCT system (120, 620) provides a first OCT scanning beam (623) having a first wavelength and a second OCT having a second wavelength different from the first wavelength. The surgical microscope according to any one of the preceding claims, characterized in that it is designed to provide a scanning beam (623). The first OCT system (720) provides an OCT scanning beam (723) with a wavelength λ ₁ = 1300 nm, and the second OCT system (780) provides an OCT scanning beam (783) with a wavelength λ ₂ = 800 nm. The surgical microscope according to claim 1 , wherein:

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