JP2017023583A - Ophthalmic microscope - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an ophthalmic microscope by which an assistant can observe in binocular by a compact configuration.SOLUTION: An ophthalmic microscope comprises: an illumination system; a pair of main light-receiving systems; a pair of main eyepiece systems; a controller; a light separation element; and a pair of sub light-receiving systems. The illumination system irradiates an eye to be tested with illumination light. In the main eyepiece systems, objective optical axes are arranged in non-parallel to each other in which return light of the illumination light irradiated on the eye to be tested is introduced through respective objective lenses into respective first image pickup devices. The main eyepiece systems respectively include first display parts. The controller causes one of the first display parts in the main eyepiece systems to display an image based on output from one of the first image pickup devices in the main light-receiving systems, and causes the other of the first display parts to display an image based on output from the other of the first image pickup devices. The light separation element is arranged between one objective lens of the main light-receiving systems and the first image pickup device and separates a part of the return light. The sub light-receiving systems introduce a part of the separated return light into each of a pair of second image pickup devices or each of a pair of eyepieces.SELECTED DRAWING: Figure 1

Description

  The present invention relates to an ophthalmic microscope.

  In the field of ophthalmology, various microscopes are used for magnifying and observing the eye. Examples of such an ophthalmic microscope include a slit lamp microscope and a surgical microscope. Some ophthalmic microscopes include an image sensor for photographing an eye, and others include a binocular optical system that provides binocular parallax for stereoscopic observation.

  Some surgical microscopes (operator microscopes) used by an operator who performs an operation on an eye are provided with an assistant's microscope. The assistant's microscope is used by an assistant who assists the operator. Similarly to the surgical microscope, the assistant can also observe the surgical part in three dimensions by guiding the left and right light from the surgical part (observation site) to the eyepiece part of the assistant's microscope.

Japanese Patent No. 4721981

  However, in a conventional surgical microscope in which an operator microscope is provided in the surgeon's microscope, a dedicated optical system is provided in the assistant's microscope separately from the surgeon's microscope, so the structure becomes complicated, There is a problem that the microscope becomes larger.

  The present invention has been made to solve such a problem, and an object of the present invention is to provide an ophthalmic microscope having a compact configuration and allowing an assistant to observe an image of an observation site with binocular eyes.

  The ophthalmic microscope of the embodiment includes an illumination system, a pair of main light receiving systems, a pair of main eyepiece systems, a control unit, a light separation element, and a pair of sub light receiving systems. The illumination system irradiates the eye to be examined with illumination light. The pair of main light receiving systems includes an objective lens and a first imaging device, the objective optical axes of each other are arranged non-parallel, and the return light of the illumination light irradiated to the eye to be examined is passed through each objective lens. Guide to the first image sensor. The pair of main eyepiece systems each include a first display unit and one or more lenses disposed on the display surface side of the first display unit. The control unit displays an image based on an output from one first imaging element of the pair of main light receiving systems on one first display unit of the pair of main eyepiece systems, and the other of the pair of main light receiving systems. An image based on an output from one image sensor is displayed on the other first display unit of the pair of main eyepiece systems. The light separation element is disposed between one objective lens of the pair of main light receiving systems and the first imaging element, and separates part of the return light of the illumination light. The pair of sub light receiving systems guides part of the return light separated by the light separation element to each of the pair of second imaging elements or each of the pair of eyepieces.

  According to the embodiment, it is possible to provide an ophthalmic microscope that has a compact configuration and allows an assistant to observe an image of an observation site with binocular eyes.

It is the schematic which shows an example of a structure of the ophthalmic microscope which concerns on embodiment. It is the schematic which shows an example of a structure of the ophthalmic microscope which concerns on embodiment. It is the schematic which shows an example of a structure of the ophthalmic microscope which concerns on embodiment. It is the schematic which shows an example of a structure of the ophthalmic microscope which concerns on embodiment. It is the schematic which shows an example of a structure of the ophthalmic microscope which concerns on embodiment. It is the schematic which shows the effect | action of the ophthalmic microscope which concerns on embodiment. It is the schematic which shows an example of a structure of the ophthalmic microscope which concerns on the modification of embodiment. It is the schematic which shows an example of a structure of the ophthalmic microscope which concerns on the modification of embodiment. It is the schematic which shows an example of a structure of the ophthalmic microscope which concerns on the modification of embodiment. It is the schematic which shows an example of a structure of the ophthalmic microscope which concerns on the modification of embodiment. It is the schematic which shows an example of a structure of the ophthalmic microscope which concerns on the modification of embodiment. It is the schematic which shows an example of a structure of the ophthalmic microscope which concerns on the modification of embodiment. It is the schematic which shows an example of a structure of the ophthalmic microscope which concerns on the modification of embodiment. It is the schematic which shows an example of a structure of the ophthalmic microscope which concerns on the modification of embodiment. It is the schematic which shows an example of a structure of the ophthalmic microscope which concerns on the modification of embodiment.

  An example of an embodiment of an ophthalmic microscope according to the present invention will be described in detail with reference to the drawings. In addition, it is possible to use the description content of the literature referred in this specification, and arbitrary well-known techniques for the following embodiment.

  An ophthalmic microscope is used for observing (taking) an enlarged image of an eye to be examined in medical treatment or surgery in the ophthalmic field. The observation target part may be an arbitrary part of the patient's eye. For example, the anterior segment may be a cornea, a corner, a vitreous body, a crystalline lens, a ciliary body, or the like, and the retinal segment may be a retina or choroid. Or a vitreous body. Further, the observation target part may be a peripheral part of the eye such as a eyelid or an eye socket.

  Hereinafter, an ophthalmic microscope including a main observation optical system used by an operator and a sub-observation optical system used by an assistant who assists the operator will be described. The main observation optical system may be used by an assistant, and the sub observation optical system may be used by an operator.

  In the following, the return light of the illumination light applied to the eye to be examined is guided to the image sensor, and an image based on the output from the image sensor is displayed on the display unit provided in the eyepiece system, thereby allowing the observer to see the eye to be examined. An ophthalmic microscope that presents the image will be described. However, the ophthalmic microscope may have a configuration in which an image of the eye to be inspected is presented to the observer by guiding the return light of the illumination light irradiated to the eye to the eyepiece lens system.

[Constitution]
1 to 4 show a configuration of an ophthalmic microscope according to the embodiment. 1 and 2 show the configuration of the optical system. FIG. 1 shows an optical system for observing the posterior eye part, and FIG. 2 shows an optical system for observing the anterior eye part. 3A and 3B schematically show the optical path of the sub-observation optical system coupled to the optical path of the main observation optical system. FIG. 3A schematically shows an optical path viewed from the direction in which the operator is located. FIG. 3B schematically shows an optical path viewed from the lateral direction (the direction of arrow K in FIG. 3A). FIG. 4 shows the configuration of the processing system.

  The ophthalmic microscope 1 includes a main observation optical system 2, a sub observation optical system 3, and an illumination system 10 (10L, 10R). The main observation optical system 2 includes a main light receiving system 20 (20L, 20R) and a main eyepiece system 30 (30L, 30R). The main observation optical system 2 may include an illumination system 10. The sub observation optical system 3 includes a sub light receiving system 80 (80L, 80R) and a sub eyepiece system 90 (90L, 90R). When observing the posterior eye portion (retinal or the like), the front lens 95 is disposed immediately before the eye E to be examined. A contact lens or the like can be used instead of the non-contact front lens 95 as shown in FIG. In addition, when observing the corner angle, a contact mirror (three-sided mirror or the like) can be used.

(Lighting system 10)
The illumination system 10 irradiates the eye E with illumination light. Although not shown, the illumination system 10 includes a light source that emits illumination light, a diaphragm that defines an illumination field, a lens system, and the like. The configuration of the illumination system may be the same as that of a conventional ophthalmologic apparatus (for example, a slit lamp microscope, a fundus camera, a refractometer, etc.).

The illumination systems 10L and 10R of the present embodiment are configured coaxially with the main light receiving systems 20L and 20R, respectively. Specifically, a beam splitter 11L made of, for example, a half mirror is obliquely attached to the main light receiving system (left main light receiving system) 20L for acquiring an image presented to the left eye E ₀ L of the operator (observer). It is installed. The beam splitter 11L couples the optical path of the illumination system (left illumination system) 10L to the optical path of the main light receiving system 20L. The illumination light output from the illumination system 10L is reflected by the beam splitter 11L, and illuminates the eye E coaxially with the main light receiving system 20L. Similarly, a main light receiving system (right main light receiving system) 20R for acquiring an image presented to the right eye E ₀ R of the surgeon has an illumination system (right illumination system) 10R in the optical path of the main light receiving system 20R. A beam splitter 11R for coupling the optical paths is obliquely provided.

  The position of the illumination light with respect to the optical axis of the main light receiving system 20L (20R) can be changed. This configuration is realized, for example, by providing means for changing the irradiation position of the illumination light with respect to the beam splitter 11L (11R) as in the conventional microscope for ophthalmic surgery.

  In this example, the beam splitter 11L (11R) is arranged between the objective lens 21L (21R) and the eye E, but the position where the optical path of the illumination light is coupled to the main light receiving system 20L (20R) is Any position of the main light receiving system 20L (20R) may be used.

(Main light receiving system 20)
In the present embodiment, a pair of left and right main light receiving systems 20L and 20R are provided. The main light receiving system 20L has a configuration for acquiring an image presented to the left eye E ₀ L of the operator, and the main light receiving system 20R is used to acquire an image presented to the right eye E ₀ R. It has a configuration. The main light receiving system 20L and the main light receiving system 20R have substantially the same configuration except that the main light receiving system 20L includes a beam splitter 26L made of, for example, a half mirror. The main light receiving system 20L includes an objective lens 21L, a beam splitter 26L, an imaging lens 22L, and an image sensor 23L. The main light receiving system 20R includes an objective lens 21R, an imaging lens 22R, and an image sensor 23R. The beam splitter 26L is disposed between the objective lens 21L of the main light receiving system 20L and the image sensor 23L, transmits part of the return light of the illumination light that has passed through the beam splitter 11L and has been guided through the objective lens 21L. To separate. A part of the return light of the illumination light separated by the beam splitter 26L is guided to the sub-observation optical system 3.

  A configuration in which the imaging lens 22L (22R) is not provided can also be applied. When the imaging lens 22L (22R) is provided as in the present embodiment, an afocal optical path (parallel optical path) is formed between the objective lens 21L (21R) and the imaging lens 22L (22R). it can. As a result, it becomes easy to arrange optical elements such as filters, and to arrange optical path coupling members to couple optical paths from other optical systems (that is, the degree of freedom and expandability of the optical configuration is improved). )

  Symbol AL1 indicates the optical axis (objective optical axis) of the objective lens 21L of the main light receiving system 20L, and symbol AR1 indicates the optical axis (objective optical axis) of the objective lens 21R of the main light receiving system 20R. An angle θ1 formed by the objective optical axis (left objective optical axis) AL1 and the objective optical axis (right objective optical axis) AR1 indicates a stereo angle in the state shown in FIG. The image sensor 23L (23R) is an area sensor such as a CCD image sensor or a CMOS image sensor.

  The above is the configuration of the main light receiving system 20 when observing the posterior segment (fundus) of the eye E (FIG. 1). On the other hand, when observing the anterior segment, as shown in FIG. 2, the focus lens 24L (24R) and the wedge prism 25L (25R) are arranged at the position on the eye E side with respect to the objective lens 21L (21R). Is done. The focus lens 24L (24R) of this example is a concave lens, and acts to extend the focal length of the objective lens 21L (21R). The wedge prism 25L (25R) deflects the optical path (objective optical axis AL1 (AR1)) of the main light receiving system 20L (20R) outward by a predetermined angle (indicated by reference numerals AL2 and AR2). Thus, the focus lens 24L and the wedge prism 25L are arranged in the main light receiving system 20L, and the focus lens 24R and the wedge prism 25R are arranged in the main light receiving system 20R. Accordingly, the focus position F1 for observing the posterior eye part is switched to the focus position F2 for observing the anterior eye part.

  An angle θ2 formed by the left and right objective optical paths (object optical axes) AL2 and AR2 deflected by the focus lenses 24L and 24R and the wedge prisms 25L and 25R is a stereo angle in the state shown in FIG. That is, by arranging the focus lenses 24L and 24R and the wedge prisms 25L and 25R, the stereo angle of the pair of main light receiving systems 20L and 20R is changed from the stereo angle θ1 for observing the posterior segment to the stereo for observing the anterior segment. It is switched to the angle θ2.

  A convex lens can be used as the focus lens. In this case, the focus lens is disposed in the optical path when observing the posterior eye part, and is retracted from the optical path when observing the anterior eye part. Instead of switching the focal length by inserting / retracting the focus lens, for example, by providing a focus lens that can move in the optical axis direction, the focal length can be changed continuously or stepwise.

  In the example shown in FIG. 2, the wedge prism 25L (25R) has a base direction outside (that is, a base-out arrangement), but a wedge prism having a base-in arrangement can be used. In this case, the wedge prism is disposed in the optical path when observing the posterior eye part, and is retracted from the optical path when observing the anterior eye part. Instead of switching the direction of the optical path by inserting / retracting the wedge prism, it is possible to change the direction of the optical path continuously or stepwise by providing a prism with a variable prism amount (and prism direction). is there.

(Main eyepiece system 30)
In the present embodiment, a pair of left and right main eyepiece systems 30L and 30R are provided. The main eyepiece system (left main eyepiece system) 30L has a configuration to present an image of the eye E obtained by the main light receiving system 20L to the left eye E _{0 L} of the operator, the main eyepiece system (right main ocular system) 30R has a configuration to present an image of the eye E obtained by the main light receiving system 20R on the right eye E _{0 R.} The main eyepiece system 30L and the main eyepiece system 30R have the same configuration. The main eyepiece system 30L (30R) includes a display unit 31L (31R) and a main eyepiece lens system 32L (32R).

  Display unit 31L (31R) is a flat panel display such as an LCD, for example. The size of the display surface of the display unit 31L (31R) is, for example, (diagonal length) 7 inches or less. The screen size of the display device provided in the pair of left and right main eyepiece systems 30L and 30R is the eye width of the operator (distance between pupils, etc.), the size of the apparatus, the design of the apparatus (arrangement of optical systems and mechanisms, etc.), etc. Is subject to restrictions. That is, there is a trade-off between such constraints and the apparent field of view. From such a viewpoint, the maximum screen size of the display units 31L and 31R is considered to be about 7 inches. In addition, by devising the configuration of the main eyepiece systems 32L and 32R and the arrangement of the mechanisms, the display units 31L and 31R having a screen size exceeding 7 inches can be applied, or the small display units 31L and 31R. Can be applied.

As will be described later, the interval between the main eyepiece system 30L and the main eyepiece system 30R can be changed. Thereby, the interval between the main eyepiece system 30L and the main eyepiece system 30R can be adjusted according to the eye width of the surgeon. In addition, the relative orientation of the main eyepiece system 30L and the main eyepiece system 30R can be changed. That is, the angle formed by the optical axis of the main eyepiece system 30L and the optical axis of the main eyepiece system 30R can be changed. Thereby, the convergence of both eyes E ₀ L and E ₀ R can be induced, and stereoscopic vision by the operator can be supported.

(Sub light receiving system 80)
The sub observation optical system 3 is provided with a pair of left and right sub light receiving systems 80L and 80R. The sub light receiving system (left sub light receiving system) 80L has a configuration for acquiring an image presented to the left eye E ₁ L of the assistant who assists the operator. The sub light receiving system (right sub light receiving system) 80R has a configuration for acquiring an image presented to the assistant's right eye E ₁ R. The sub light receiving system 80L and the sub light receiving system 80R have the same configuration. The sub light receiving system 80L (80R) includes an imaging lens 82L (82R) and an image sensor 83L (83R).

  The return light of the illumination light applied to the eye E is guided to the beam splitter 26L through the objective lens 21L. The beam splitter 26L separates part of the return light of the illumination light and transmits the rest. Part of the return light of the illumination light separated by the beam splitter 26L enters the sub light receiving systems 80L and 80R. The remainder of the return light of the illumination light that has passed through the beam splitter 26L is guided to the image sensor 23L. The sub light receiving systems 80L and 80R form a pair of parallel optical paths that respectively guide part of the return light of the illumination light separated by the beam splitter 26L. That is, the normal lines of the imaging surfaces of the imaging elements 83L and 83R are parallel to each other. The sub light receiving systems 80L and 80R guide part of the return light of the illumination light separated by the beam splitter 26L to the image sensors 83L and 83R, respectively, along the formed parallel optical path. Accordingly, an afocal optical path can be formed between the imaging lens 82L (82R) and the image sensor 83L (83R), and an optical element such as a filter or an optical path coupling member can be disposed. It becomes easy to couple the optical paths from the optical system.

(Second eyepiece system 90)
The sub observation optical system 3 is provided with a pair of left and right sub eyepiece systems 90L and 90R. Secondary ocular system (left sub eyepiece system) 90L has a configuration to present an image of the obtained eye E by the sub light receiving system 80L on the passenger of the left eye E _{1 L.} Secondary ocular system (right sub eyepiece system) 90R has a configuration to present an image of the eye E obtained by the sub light receiving system 80R in the passenger of the right eye E _{1 R.} The auxiliary eyepiece system 90L and the auxiliary eyepiece system 90R have the same configuration. The auxiliary eyepiece system 90L (90R) includes a display unit 91L (91R) and an auxiliary eyepiece lens system 92L (92R).

  Display unit 91L (91R) is a flat panel display such as an LCD, for example. The size of the display surface of the display unit 91L (91R) may be, for example, 7 inches or less (diagonal length), similarly to the display unit 31L (31R).

  For example, as shown in FIG. 3A, the beam splitter 26L is disposed between the objective lens 21L and the imaging lens 22L, and the objective optical axis AL1 so that the direction of the reflecting surface thereof is substantially opposite to the operator direction. It is obliquely set against. 3A, the imaging lens 82R (82L) is disposed below the imaging lens 82L (82R), as viewed from the direction of the arrow K in FIG. 3A. Part of the return light of the illumination light separated by the beam splitter 26L is guided to each of the image sensors 83L and 83R via a pair of parallel optical paths formed on the upper side and the lower side. The display units 91L and 91R (second eyepiece systems 90L and 90R) are arranged in the horizontal direction. On the display units 91L and 91R, for example, an image acquired by one or both of the image sensors 83L and 83R is rotated and displayed according to the position of the sub-eyepiece system 90 with respect to the main eyepiece system 30.

  The sub observation optical system 3 (the sub light receiving system 80 and the sub eyepiece system 90) may be rotatable around the objective optical axis AL1 (AL2) of the main light receiving system 20L or the optical path of the main light receiving system 20L. The mechanism for rotating the sub observation optical system 3 may be a known rotation mechanism. Even in this case, the image acquired by one or both of the image sensors 83L and 83R is rotated and displayed in accordance with the position of the sub-eyepiece system 90 with respect to the main eyepiece system 30. Thereby, the assistant can observe the observation site with binoculars at an arbitrary position in the same manner as the operator.

  Similar to the distance between the main eyepiece system 30L and the main eyepiece system 30R, the distance between the subeyepiece system 90L and the subeyepiece system 90R can be changed. Thereby, the space | interval of the auxiliary eyepiece system 90L and the auxiliary eyepiece system 90R can be adjusted according to the eye width of the assistant.

  As described above, the sub-observation optical system 3 is a Galileo optical system, and the optical path of the optical system is coupled to one optical path of the pair of main light receiving systems 20. As a result, the assistant can also observe the observation site with binoculars in the same manner as the operator.

(Control unit 100)
The control unit 100 executes control of each unit of the ophthalmic microscope 1 (see FIG. 4). Examples of control of the illumination system 10 include the following: turning on / off the light source, adjusting the amount of light; adjusting the diaphragm; adjusting the slit width when slit illumination is possible. Control of the image sensors 23 and 83 includes exposure adjustment, gain adjustment, and shooting rate adjustment.

The control unit 100 displays various information on the display unit 31. For example, the control unit 100 causes the display unit 31L to display an image acquired by the image sensor 23L (or an image obtained by processing the image) and displays an image acquired by the image sensor 23R (or processes it). The image obtained in this manner is displayed on the display unit 31R. At this time, the control unit 100 can change the orientation of the image acquired by the image sensor 23L (23R) and cause the display unit 31L (31R) to display the image. For example, as in the present embodiment, when an inverter that converts an inverted image into an erect image is not provided in the light receiving system, the control unit 100 inverts the image acquired by the image sensor 23L (23R) and erects the image. Can be displayed on the display unit 31L (31R). When the main eyepiece system 32L (32R) is configured to invert the image displayed on the display unit 31L (31R) and present it to the left eye E ₀ L (right eye E ₀ R), the control is performed. The unit 100 performs control to display an inverted image on the display unit 31L (31R). With such a configuration, there is no need to provide an inverter, the number of members included in the optical system can be reduced, and the cost can be reduced and the apparatus can be downsized.

  The control unit 100 displays various information on the display unit 91. For example, the control unit 100 displays an image acquired by the image sensor 83L (or an image obtained by processing the image) on one of the display units 91L and 91R. Furthermore, the control unit 100 displays an image (or an image obtained by processing the image) acquired by the image sensor 83R on the other of the display units 91L and 91R. At this time, the control unit 100 can rotate the image based on the output from the image sensor 83 and display the image on the display unit 91 according to the position of the sub-eyepiece system 90 with respect to the main eyepiece system 30. For example, when the secondary eyepiece system 90 faces the main eyepiece system 30, the image captured by the image sensor 83R is displayed on the display unit 91L after being rotated by 180 degrees, and the image captured by the image sensor 83L is displayed on the display unit 91R. The displayed image is rotated 180 degrees and displayed. Thereby, when the secondary eyepiece system 90 faces the main eyepiece system 30, the assistant can also observe the observation site in a three-dimensional manner, like the operator.

  Further, the control unit 100 can rotate the image acquired by one of the imaging elements 83L and 83R and display the image on both the display units 91L and 91R according to the position of the sub-ocular system 90 with respect to the main eyepiece system 30. Is possible. Thereby, even if the position of the sub-eyepiece system 90 with respect to the main eyepiece system 30 is a position where stereoscopic observation is impossible, the assistant can observe the observation site with binocular eyes.

  Furthermore, the control unit 100 controls various mechanisms. As such a mechanism, a stereo angle changing unit 20A, a focusing unit 24A, an optical path deflecting unit 25A, an interval changing unit 30A, and an orientation changing unit 30B are provided.

  The stereo angle changing unit 20A relatively rotates and moves between the main light receiving system 20L and the main light receiving system 20R. That is, the stereo angle changing unit 20A relatively moves the main light receiving system 20L and the main light receiving system 20R so as to change the angle formed between the objective optical axes (for example, AL1 and AR1). This relative movement is, for example, to move the main light receiving system 20L and the main light receiving system 20R by the same angle in opposite rotational directions. In this movement mode, the direction of the angle bisector formed by the objective optical axes (for example, AL1 and AR1) is constant. On the other hand, it is also possible to perform the relative movement so that the direction of the bisector changes.

  FIG. 5 shows an example of a state where the stereo angle is expanded from the state shown in FIG. 2 by controlling the stereo angle changing unit 20A. The stereo angle θ3 shown in FIG. 5 is larger than the stereo angle θ2 shown in FIG. Even if the stereo angle is changed by the stereo angle changing unit 20A, the relative positions (intervals and relative orientations) of the main eyepiece systems 30L and 30R do not change. Also, the focal position does not move by adjusting the distance of the main light receiving systems 20L and 20R with respect to the eye E or changing the focal length of the main light receiving systems 20L and 20R in response to the change in the stereo angle. Control can be performed.

  The focusing unit 24A inserts / withdraws the left and right focus lenses 24L and 24R with respect to the optical path. The focusing unit 24A may be configured to simultaneously insert / retract the left and right focus lenses 24L and 24R. In another example, the focusing unit 24A may be configured to change the focal position by moving the left and right focus lenses 24L and 24R (simultaneously) in the optical axis direction. Alternatively, the focusing unit 24A may be configured to change the focal length by changing (simultaneously) the refractive powers of the left and right focus lenses 24L and 24R.

  The optical path deflecting unit 25A inserts / withdraws the left and right wedge prisms 25L and 25R with respect to the optical path. The optical path deflecting unit 25A may be configured to simultaneously insert / retract the left and right wedge prisms 25L and 25R. In another example, the optical path deflecting unit 25A changes the direction of the optical paths of the left and right main light receiving systems 20L and 20R by changing the prism amounts (and prism directions) of the left and right wedge prisms 25L and 25R (simultaneously). May be configured.

  The interval changing unit 30A changes the interval between the left and right main eyepiece systems 30L and 30R. The interval changing unit 30A may be configured to relatively move the left and right main eyepiece systems 30L and 30R without changing the relative directions of the optical axes of each other. The interval changing unit 30A can also change the interval between the left and right auxiliary eyepiece systems 90L and 90R.

  The direction changing unit 30B changes the relative directions of the left and right main eyepiece systems 30L and 30R. The direction changing unit 30B relatively moves the main eyepiece system 30L and the main eyepiece system 30R so as to change the angle formed by the optical axes of each other. This relative movement is, for example, to move the main eyepiece system 30L and the main eyepiece system 30R by the same angle in opposite rotation directions. In this movement mode, the direction of the bisector of the angle formed by the optical axes of each other is constant. On the other hand, it is also possible to perform the relative movement so that the direction of the bisector changes.

  The control unit 100 includes a brightness adjustment unit 101. The brightness adjustment unit 101 adjusts the brightness of images displayed on the display units 31L and 31R. For example, the luminance adjustment unit 101 has at least one luminance of the left image and the right image so as to reduce the difference in brightness (brightness) between the left image displayed on the display unit 31L and the right image displayed on the display unit 31R. Adjust. The brightness adjustment unit 101 obtains a brightness distribution for each predetermined image area of the left image and the right image, and reduces the difference between the obtained brightness distributions (or statistical values thereof) of the left image and the left image. And the luminance of at least one of the right image can be adjusted. Statistical values include average value, maximum value, minimum value, variance, standard deviation, and median value. Thereby, even if the light quantity of the return light of the illumination light guided to the image sensor 23L by the beam splitter 26L is reduced with respect to the light quantity of the return light of the illumination light guided to the image sensor 23R, A left image and a right image having substantially the same brightness are presented.

  The brightness adjustment unit 101 may adjust the brightness of the left image and the right image by performing exposure adjustment, gain adjustment, shooting rate adjustment, and the like of the image sensors 23L and 23R. Further, the brightness adjusting unit 101 may adjust the brightness of the left image and the right image by controlling the display units 31L and 31R. In addition, the luminance adjustment unit 101 can adjust the luminance of the images displayed on the display units 91L and 91R in the same manner as the luminance adjustment of the images displayed on the display units 31L and 31R.

(Data processing unit 200)
The data processing unit 200 executes various types of data processing. This data processing includes, for example, processing for forming an image and processing for processing an image. In addition, the data processing unit 200 may be capable of executing processing relating to analysis of images, examination results, and measurement results, and information relating to the subject (such as electronic medical record information). The data processing unit 200 is provided with a scaling processing unit 210.

The scaling processing unit 210 enlarges the image acquired by the image sensor 23. This process is a so-called digital zoom process, and includes a process of cutting out a part of an image acquired by the image sensor 23 and a process of creating an enlarged image of the part. The image clipping range is set by an observer (operator, assistant) or by the control unit 100. The scaling processing unit 210 performs the same processing on the image (left image) acquired by the image sensor 23L of the main light receiving system 20L and the image (right image) acquired by the image sensor 23R of the main light receiving system 20R. Apply. Thereby, images of the same magnification are presented to the left eye E ₀ L and right eye E ₀ R of the surgeon.

In addition, the scaling processing unit 210 enlarges the image acquired by the image sensor 83. This process includes a process of cutting out a part of the image acquired by the image sensor 83 and a process of creating an enlarged image of the part, similarly to the digital zoom process for the image acquired by the image sensor 23. The magnification processing unit 210 performs the same processing on the image (left image) acquired by the image sensor 83L of the sub light receiving system 80L and the image (right image) acquired by the image sensor 83R of the sub light receiver system 80R. Apply. Thereby, images of the same magnification are presented to the assistant's left eye E ₁ L and right eye E ₁ R.

  In addition to or instead of such a digital zoom function, a so-called optical zoom function can be provided. The optical zoom function is realized by providing a variable power lens (variable lens system) in each of the left and right main light receiving systems 20L and 20R or the left and right sub light receiving systems 80L and 80R. As a specific example, there is a configuration in which the zoom lens is (selectively) inserted / retracted with respect to the optical path, or a configuration in which the zoom lens is moved in the optical axis direction. Control related to the optical zoom function is executed by the control unit 100.

  Further, the beam splitter 26L is inclined with respect to the objective optical axis AL1. That is, in the main light receiving system 20L, the optical axis of the return light of the illumination light transmitted through the beam splitter 26L is shifted from the objective optical axis AL1, whereas in the main light receiving system 20R, the optical axis of the return light of the illumination light is changed. There is no deviation with respect to the objective optical axis AR1. When this deviation cannot be ignored, the control unit 100 can control the image sensor 23 or the display unit 31 so as to cancel the deviation of the optical axis of the return light of the illumination light in the main light receiving systems 20L and 20R. . For example, the control unit 100 can control the image sensor 23 so as to cancel the positional deviation of the optical axis of the return light of the illumination light on the imaging surfaces of the image sensors 23L and 23R. For example, the control unit 100 controls the display unit 31 so as to cancel the positional deviation of the image displayed on the display unit 31 due to the positional deviation of the optical axis of the return light of the illumination light in the main light receiving system 20. It is possible. Further, the data processing unit 200 can control the image acquired by the image sensor 23 so as to cancel the deviation of the optical axis of the return light of the illumination light in the main light receiving systems 20L and 20R. For example, the data processing unit 200 can be controlled to cancel the positional deviation of the optical axis of the return light of the illumination light with respect to the image acquired by each of the image sensors 23L and 23R.

(User interface 300)
The user interface (UI) 300 has a function for exchanging information between an observer or the like and the ophthalmic microscope 1. The user interface 300 includes a display device and an operation device (input device). The display device may include the display unit 31 or the display unit 91, and may include other display devices. The operation device includes various hardware keys and / or software keys. It is possible to integrally configure at least a part of the operation device and at least a part of the display device. A touch panel display is an example.

(Communication unit 400)
The communication unit 400 performs a process for transmitting information to another apparatus and a process for receiving information transmitted from the other apparatus. The communication unit 400 may include a communication device that conforms to a predetermined network (LAN, Internet, etc.). For example, the communication unit 400 acquires information from an electronic medical record database or a medical image database via a LAN provided in a medical institution. When an external monitor is provided, the communication unit 400 can transmit an image acquired by the ophthalmic microscope 1 to the external monitor substantially in real time.

  The image sensors 23L and 23R are examples of the “first image sensor” according to the embodiment. The display units 31L and 31R are examples of the “first display unit” according to the embodiment. The beam splitter 26L is an example of the “light separation element” according to the embodiment. The image sensors 83L and 83R are examples of the “second image sensor” according to the embodiment. The display units 91L and 91R are examples of the “second display unit” according to the embodiment.

  In the above embodiment, the configuration in which the optical path of the sub-observation optical system 3 is coupled to the optical path of the main light receiving system 20L in the main light receiving system 20L and the main light receiving system 20R has been described. A configuration in which the optical paths of the sub-observation optical system 3 are combined may be employed. Further, two or more auxiliary observation optical systems 3 may be provided, and the optical path of the auxiliary observation optical system 3 may be coupled to the optical paths of the main light receiving system 20L and the main light receiving system 20R.

[effect]
The effect of the ophthalmic microscope of this embodiment will be described.

  An ophthalmic microscope (ophthalmic microscope 1) according to the embodiment includes an illumination system (illumination systems 10L and 10R), a pair of main light receiving systems (main light receiving systems 20L and 20R), and a pair of main eyepiece systems (main eye systems). 30L and 30R), a control unit (control unit 100), a light separation element (beam splitter 26L), and a pair of sub light receiving systems (sub light receiving systems 80L and 80R). The illumination system irradiates the eye to be examined (eye E to be examined) with illumination light. The pair of main light receiving systems includes an objective lens (objective lenses 21L and 21R) and a first imaging device (imaging devices 23L and 23R), the objective optical axes of which are arranged non-parallel to each other, and illumination irradiated to the eye to be examined The return light of the light is guided to each first image sensor through each objective lens. The pair of main eyepiece systems includes a first display unit (display units 31L and 31R) and one or more lenses (main eyepiece system 32L and 32R) arranged on the display surface side of the first display unit. The control unit displays an image based on an output from one first imaging element of the pair of main light receiving systems on one first display unit of the pair of main eyepiece systems, and the other of the pair of main light receiving systems. An image based on an output from one image sensor is displayed on the other first display unit of the pair of main eyepiece systems. The light separation element is disposed between one objective lens of the pair of main light receiving systems and the first imaging element, and separates part of the return light of the illumination light. The pair of sub light receiving systems guides part of the return light separated by the light separation element to each of the pair of second imaging elements (imaging elements 83L and 83R) or each of the pair of eyepieces.

  According to such a configuration, a part of the return light of the illumination light from the eye to be examined is separated by the light separation element disposed between one objective lens of the pair of main light receiving systems and the first imaging element, A part of the separated return light can be guided to the pair of sub light receiving systems. Accordingly, the objective lens is shared by the pair of main light receiving systems and the pair of sub light receiving systems. Accordingly, an observer (operator) who uses a pair of main light receiving systems in a compact configuration can stereoscopically observe an image of an observation site with binocular eyes, and an observer who uses a pair of auxiliary light receiving systems ( (Assistant) can also provide an ophthalmic microscope capable of observing an image of the observation site with binocular eyes.

  In the ophthalmic microscope according to the embodiment, the pair of auxiliary light receiving systems may form a pair of parallel optical paths that respectively guide part of the return light.

  According to such a configuration, a part of the optical path of the return light of the illumination light from the eye to be examined can be an afocal optical path, and an optical element such as a filter is disposed, and an optical path coupling member is disposed. This makes it easy to couple optical paths from other optical systems.

  In addition, the ophthalmic microscope according to the embodiment may include a pair of secondary eyepiece systems (secondary eyepiece systems 90L and 90R). The pair of sub-ocular systems includes a second display unit (display units 91L and 91R) and one or more lenses (sub-ocular lens systems 92L and 92R) arranged on the display surface side of the second display unit. The pair of sub light receiving systems guides part of the return light to each of the pair of second imaging elements. The control unit displays an image based on an output from one second imaging element of the pair of sub light receiving systems on one second display unit of the pair of sub eyepiece systems, and the other of the pair of sub light receiving systems. The image based on the output from the two image sensors is displayed on the other second display unit of the pair of secondary eyepiece systems.

  According to such a configuration, even when the pair of secondary eyepiece systems is arranged at an arbitrary position, an observer using the pair of secondary eyepiece systems can use an ophthalmic microscope capable of observing an image of the observation site with binocular eyes. Can be provided.

  Further, in the ophthalmic microscope according to the embodiment, the control unit rotates the image based on the output from the second image sensor in accordance with the position of the pair of sub light receiving systems with respect to the pair of main light receiving systems, and causes the second display unit to rotate. It may be displayed.

  According to such a configuration, regardless of the position of the pair of secondary eyepiece systems with respect to the pair of main eyepiece systems, an observer who uses the pair of secondary eyepiece systems can observe the image of the observation site with binocular eyes. In particular, when a pair of secondary eyepiece systems are positioned so as to face the pair of main eyepiece systems, an observer using the pair of secondary eyepiece systems provides an ophthalmic microscope capable of stereoscopically observing an image of an observation site with binocular eyes. Will be able to.

  In the ophthalmic microscope according to the embodiment, the control unit (brightness adjusting unit 101) may perform brightness adjustment of a pair of images based on outputs from the pair of main light receiving systems.

  According to such a configuration, even when the light separation element is disposed only in one of the pair of main light receiving systems, the eyes of the observer using at least the pair of main eyepiece systems are substantially the same. A bright image can be presented.

[Modification]
The above embodiments are merely examples for carrying out the present invention. A person who intends to implement the present invention can make arbitrary modifications, omissions, additions, substitutions and the like within the scope of the present invention. Hereinafter, the drawings in the above embodiments will be referred to as appropriate.

(Modification 1)
In the above embodiment, part of the return light of the illumination light separated by the beam splitter 26L may be guided to each of the image sensors 83L and 83R via a pair of optical paths parallel to each other in the horizontal direction. .

  6A to 6C schematically show the optical path of the sub-observation optical system coupled to the optical path of the main observation optical system in Modification 1 of the embodiment. FIG. 6A schematically shows an optical path viewed from the direction in which the operator is located. FIG. 6B schematically shows an optical path viewed from the direction of the arrow K ′ in FIG. 3A. FIG. 6C schematically shows an optical path viewed from the lateral direction (the direction of arrow K in FIG. 6A).

  For example, as shown in FIG. 6A, the beam splitter 26L is arranged between the objective lens 21L and the imaging lens 22L, and the objective light is oriented so that the direction of the reflecting surface thereof is in the horizontal direction (the direction opposite to the arrow K). It is inclined with respect to the axis AL1. When viewed from the direction of the arrow K ′, as shown in FIGS. 6B and 6C, the imaging lens 82L (82R) and the imaging lens 82R (82L) are arranged in the horizontal direction. Part of the return light of the illumination light separated by the beam splitter 26L is guided to each of the image sensors 83L and 83R via a pair of optical paths parallel to each other in the horizontal direction. The display units 91L and 91R (second eyepiece systems 90L and 90R) are arranged in the horizontal direction. On the display units 91L and 91R, for example, an image acquired by one or both of the image sensors 83L and 83R is rotated and displayed according to the position of the sub-eyepiece system 90 with respect to the main eyepiece system 30.

  According to this modification, it is not necessary to add a new optical element to guide a part of the return light of the illumination light to the eyes of the assistant, and the assistant can view the image of the observation site with binocular eyes in a more compact configuration. An observable ophthalmic microscope can be provided.

(Modification 2)
In the above embodiment, the focus lenses 24L and 24R and the wedge prisms 25L and 25R are retracted from the optical path during fundus observation, and are inserted into the optical path during anterior segment observation. Such an operation can be automated. In the embodiment, an auxiliary optical member for changing the observation site of the eye to be examined is used. For example, the front lens 95 is disposed in the optical path during fundus observation, and is retracted from the optical path during observation of the anterior segment.

  The ophthalmic microscope of the present modification changes the states of the focus lenses 24L and 24R according to the state of the auxiliary optical member (that is, selection of the observation site). In other words, the control unit 100 controls the lens moving mechanism for linking the focus lenses 24L and 24R according to the change of the observation site by the auxiliary optical member. Similarly, the control unit 100 controls a prism moving mechanism for linking the wedge prisms 25L and 25R in accordance with the change of the observation site by the auxiliary optical member.

  A specific example will be described. When the front lens 95 is retracted from the optical path, the control unit 100 controls the focusing unit 24A and the optical path deflecting unit 25A so that the focus lenses 24L and 24R and the wedge prisms 25L and 25R are inserted into the optical path. . Conversely, the control unit 100 controls the focusing unit 24A and the optical path deflecting unit 25A so as to retract from the focus lenses 24L and 24R and the wedge prisms 25L and 25R in response to the insertion of the front lens 95 into the optical path. To do.

  The ophthalmic microscope according to the present modification may include a configuration for generating information indicating the state of the auxiliary optical member (for example, whether or not the front lens 95 is inserted in the optical path). For example, the arrangement state of the arm that holds the front lens 95 can be detected using a sensor such as a microswitch. Alternatively, in a configuration in which the insertion / retraction of the front lens 95 is performed based on a signal from the control unit 100, the current state of the front lens 95 can be recognized by referring to the control history.

  As another example, based on the image acquired by the image sensor 23L and / or 23R and the current state of the focus lenses 24L and 24R and the wedge prisms 25L and 25R, is the front lens 95 disposed in the optical path? It can be determined whether or not. For example, the data processing unit 200 analyzes an image acquired in a state where the focus lens 24L and the like are arranged on the optical path, thereby obtaining an amount indicating the blurred state of the image. When the amount of blur is equal to or greater than the threshold value, it is determined that the front lens 95 is disposed in the optical path. Conversely, when the amount of blur is less than the threshold value, it is determined that the front lens 95 is retracted from the optical path. In the case of analyzing an image acquired in a state where the focus lens 24L is retracted from the optical path, the state of the front lens 95 can be similarly determined.

  According to this modification, the state of the lens for changing the focal position (focus lenses 24L and 24R) and the state of the deflection member (wedge prisms 25L and 25R) for deflecting the optical path are used for switching the observation site. It can be changed automatically. Therefore, the operability can be further improved.

(Modification 3)
The illumination systems (10L and 10R) of the above embodiment are arranged coaxially with the pair of main light receiving systems (20L and 20R). In this modification, a configuration in which an illumination system is arranged non-coaxially with respect to a pair of main light receiving systems, that is, a configuration capable of irradiating illumination light from a direction different from the objective optical axis of the pair of main light receiving systems will be described. A configuration example of the optical system of this modification is shown in FIG. The illumination system 10S of the ophthalmic microscope 1A can irradiate, for example, slit light to the eye to be examined. A typical example of such an ophthalmic microscope is a slit lamp microscope. In this modification, the relative positions of the illumination system 10S and the main light receiving systems 20L and 20R can be changed as in a slit lamp microscope. That is, the illumination system 10S and the main light receiving systems 20L and 20R are configured to be rotatable around the same axis. Thereby, it is possible to observe the cross section of the cornea etc. illuminated with the slit light from an oblique direction.

  The ophthalmic microscope may include one or both of a coaxial illumination system as in the above embodiment and a non-coaxial illumination system as in this modification. When both illumination systems are provided, the illumination system to be used can be switched in accordance with, for example, switching of the observation site.

(Modification 4)
The ophthalmic microscope may have a function as another ophthalmic apparatus in addition to a function as a microscope for magnifying and observing the eye to be examined. Examples of functions as other ophthalmologic apparatuses include OCT (Optical Coherence Tomography), laser treatment, axial length measurement, refractive power measurement, and higher-order aberration measurement. Other ophthalmologic apparatuses have an arbitrary configuration capable of performing examination, measurement, and imaging of an eye to be examined by an optical method.

  The structural example of the ophthalmic microscope which concerns on this modification is shown in FIGS. The ophthalmic microscope 1B according to this modification includes an OCT function in addition to the same configuration as that of the above embodiment. Specifically, the ophthalmic microscope 1 </ b> B includes an illumination system 40 in addition to the illumination system 10, the main light receiving system 20, the main eyepiece system 30, the sub light receiving system 80, and the subeyepiece system 90 similar to those in the above embodiment.

  The irradiation system 40 irradiates the eye E with light for realizing the function as the “other ophthalmic apparatus” described above from a direction different from the objective optical axis (AL1 and AR1) of the main light receiving system 20. The irradiation system 40 of this example irradiates the eye E with light for OCT (measurement light).

  The irradiation system 40 includes an OCT system 60, a collimating lens 52, an optical scanner 41, a focus lens 42, a deflection mirror 43, and an OCT objective lens 44.

(OCT system 60)
The OCT system 60 includes an interference optical system for performing OCT. An example of the configuration of the OCT system 60 is shown in FIG. The optical system shown in FIG. 9 is an example of a swept source OCT, which splits light from a wavelength scanning type (wavelength sweep type) light source into measurement light and reference light, and returns return light of measurement light from the eye E to be examined. Interference light is generated by interfering with the reference light passing through the reference light path, and this interference light is detected. The detection result (detection signal) of the interference light by the interference optical system is a signal indicating the spectrum of the interference light, and is sent to the control unit 100a.

  The light source unit 61 includes a wavelength scanning type (wavelength sweeping type) light source capable of scanning (sweeping) the wavelength of emitted light in the same manner as a general swept source type OCT apparatus. The light source unit 61 temporally changes the output wavelength in the near-infrared wavelength band that cannot be visually recognized by the human eye.

  The light L0 output from the light source unit 61 is guided to the polarization controller 63 by the optical fiber 62 and its polarization state is adjusted. The light L0 is guided to the fiber coupler 65 by the optical fiber 64 and converted into the measurement light LS and the reference light LR. Divided.

  The reference light LR is guided to the collimator 67 by the optical fiber 66A, converted into a parallel light beam, and guided to the corner cube 70 via the optical path length correction member 68 and the dispersion compensation member 69. The optical path length correction member 68 functions as a delay unit for matching the optical path length (optical distance) of the reference light LR with the optical path length of the measurement light LS. The dispersion compensation member 69 acts as a dispersion compensation means for matching the dispersion characteristics between the reference light LR and the measurement light LS.

  The corner cube 70 folds the traveling direction of the reference light LR in the reverse direction. The corner cube 70 is movable in a direction along the incident optical path and the outgoing optical path of the reference light LR, thereby changing the length of the optical path of the reference light LR. Note that any one of a means for changing the length of the optical path of the measurement light LS and a means for changing the length of the optical path of the reference light LR may be provided.

  The reference light LR that has passed through the corner cube 70 passes through the dispersion compensation member 69 and the optical path length correction member 68, is converted from a parallel light beam into a focused light beam by the collimator 71, enters the optical fiber 72, and is guided to the polarization controller 73. Accordingly, the polarization state of the reference light LR is adjusted. Further, the reference light LR is guided to the attenuator 75 by the optical fiber 74, and the amount of light is adjusted under the control of the control unit 100a. The reference light LR whose light amount has been adjusted is guided to the fiber coupler 77 by the optical fiber 76.

  On the other hand, the measurement light LS generated by the fiber coupler 65 is guided by the optical fiber 51 and emitted from the end face of the fiber, and is converted into a parallel light beam by the collimator lens 52. The measurement light LS converted into a parallel light beam is irradiated onto the eye E through the optical scanner 41, the focus lens 42, the deflection mirror 43, and the OCT objective lens 44. The measurement light LS is reflected and scattered at various depth positions of the eye E. The return light of the measurement light LS from the eye E includes reflected light and backscattered light, travels in the same direction as the forward path in the reverse direction, is guided to the fiber coupler 65, and passes through the optical fiber 66B to the fiber coupler 77. To reach.

  The fiber coupler 77 combines (interferences) the measurement light LS incident through the optical fiber 66B and the reference light LR incident through the optical fiber 76 to generate interference light. The fiber coupler 77 generates a pair of interference light LC by dividing the interference light at a predetermined branching ratio (for example, 1: 1). The pair of interference lights LC emitted from the fiber coupler 77 are guided to the detector 79 by optical fibers 78A and 78B, respectively.

  The detector 79 is, for example, a balanced photodiode that includes a pair of photodetectors that respectively detect a pair of interference lights LC and outputs a difference between detection results obtained by these. The detector 79 sends the detection result (detection signal) to the control unit 100a.

  In this example, swept source OCT is applied, but other types of OCT, such as spectral domain OCT, can be applied.

  As shown in FIG. 8, light (measurement light) from the OCT system 60 is guided by an optical fiber 51 and emitted from the end face of the fiber. A collimating lens 52 is disposed at a position facing the fiber end face. The collimating lens 52 converts the measurement light emitted from the fiber end face into a parallel light beam. The measurement light converted into a parallel light beam by the collimator lens 52 is guided to the optical scanner 41. The collimating lens 52 may be movable along the optical path of the measuring light as a focus lens (or one of the lens groups constituting the focus lens).

  The optical scanner 41 is a two-dimensional optical scanner, and includes an x scanner 41H that deflects light in the horizontal direction (x direction) and a y scanner 41V that deflects light in the vertical direction (y direction). Each of the x scanner 41H and the y scanner 41V may be an arbitrary type of optical scanner, and for example, a galvanometer mirror is used. The optical scanner 41 is disposed, for example, at the exit pupil position of the collimating lens 52 or a position in the vicinity thereof. Furthermore, the optical scanner 41 is disposed, for example, at the entrance pupil position of the focus lens 42 or a position in the vicinity thereof.

  When a two-dimensional optical scanner is configured by combining two one-dimensional optical scanners as in this example, the two one-dimensional optical scanners are arranged apart from each other by a predetermined distance (for example, about 10 mm). Thereby, for example, any one-dimensional optical scanner can be arranged at the exit pupil position and / or the entrance pupil position.

  The focus lens 42 temporarily forms an image of the parallel light beam (measurement light) that has passed through the optical scanner 41. The light that has passed through the focus lens 42 is reflected by the deflection mirror 43 toward the OCT objective lens 44. The light passing through the OCT objective lens 44 is irradiated to the eye E.

  The position of the deflection mirror 43 is determined in advance so that the light from the OCT system 60 is irradiated to the eye E from a direction different from the objective optical axis (AL1 and AR1, and AL2 and AR2) of the main light receiving system 20. . In this example, the deflection mirror 43 is arranged at a position between the main light receiving system 20L and the main light receiving system 20R where the objective optical axes are arranged non-parallel.

  FIG. 10 schematically shows a perspective view of the deflection mirror 43 and the OCT objective lens 44. In FIG. 10, the cross section of the optical path of the main light receiving system 20L in the direction perpendicular to the objective optical axis AL1 (AL2) and the cross section of the optical path of the main light receiving system 20R in the direction perpendicular to the objective optical axis AR1 (AR2) are schematically shown. It is represented.

  In order to make the light from the OCT system 60 incident on the eye E from an incident direction as close to the vertical as possible, the deflection mirror 43 and the objective light axis (AL1 and AR1, and AL2 and AR2) of the main light receiving system 20 An OCT objective lens 44 is arranged. The end 43a on the objective optical axis side of the main light receiving system 20 of the deflection mirror 43 and the end 44a on the objective optical axis side of the main light receiving system 20 of the OCT objective lens 44 are the optical path of the main light receiving system 20L and the main light receiving system 20R. It is in close contact with the optical path.

  The optical scanner 41 and the deflecting surface of the deflecting mirror 43 are optically substantially conjugate. In particular, the deflection surface of the y scanner 41V that deflects the light from the OCT system 60 in a direction substantially parallel to the objective optical axis of the main light receiving system 20 and the deflection surface of the deflection mirror 43 are optically substantially conjugate. . In this example, the deflection surface of the y scanner 41V that deflects the light from the OCT system 60 in the plane orthogonal to the plane including the pair of objective optical axes of the main light receiving system 20 and the deflection surface of the deflection mirror 43 are optically approximately. Arranged in a conjugate. As a result, the size H (see FIG. 10) of the deflection surface of the deflection mirror 43 that is inclined with respect to the direction of the objective optical axis of the main light receiving system 20 can be reduced. By reducing the size H of the deflection mirror 43, the deflection mirror 43 and the OCT objective lens 44 can be arranged closer to the objective optical axis of the main light receiving system 20.

  In the present embodiment, the end 44a on the objective optical axis side of the main light receiving system 20 of the OCT objective lens 44 is cut out linearly. Thereby, the observation light path of the main light receiving system 20L and the observation light path of the main light receiving system 20R are not blocked by the peripheral edge of the OCT objective lens 44. By cutting off the end of the OCT objective lens 44, the deflection mirror 43 and the OCT objective lens 44 can be arranged closer to the objective optical axis of the main light receiving system 20. Note that the end portion 44a is not linear, and may be cut out in a curved shape, for example.

  The deflection mirror 43 is a reflection mirror in which an end 43a on the objective optical axis side of the main light receiving system 20 on the deflection surface (reflection surface) is formed in a straight line. The end 43a of the deflection mirror 43 and the end 44a of the OCT objective lens 44 are disposed so as to be substantially in contact with the optical path of the main light receiving system 20L and the optical path of the main light receiving system 20R. Thereby, the deflection mirror 43 and the OCT objective lens 44 can be arranged at a position as close as possible to the objective optical axis of the main light receiving system 20.

  FIG. 11 schematically illustrates an optical path arrangement diagram when the respective optical paths of the main light receiving system 20 and the irradiation system 40 are viewed from the objective optical axis direction of the main light receiving system 20. The objective optical axis AL1 (AL2) of the main light receiving system 20L is provided in the vicinity of the lens center of the objective lens 21L. The objective optical axis AR1 (AR2) of the main light receiving system 20R is provided in the vicinity of the lens center of the objective lens 21R. The objective optical axis OL of the irradiation system 40 is provided in the vicinity of the lens center of the OCT objective lens 44. A distance D1 between the lens center of the objective lens 21L and the lens center of the OCT objective lens 44 and a distance D2 between the lens center of the objective lens 21R and the lens center of the OCT objective lens 44 are substantially equal. Thereby, it is possible to make the light from the irradiation system 40 enter from the optical axis direction as close as possible to the objective optical axis of the main light receiving system 20.

  The distance D3 (base length) between the lens center of the objective lens 21L and the lens center of the objective lens 21R may be longer than the distances D1 and D2 (length of the hypotenuse). Thereby, it becomes possible to make the light from the irradiation system 40 enter from the optical axis direction closer to the objective optical axis of the main light receiving system 20.

  As described above, the deflection mirror 43 and the OCT objective lens 44 can be disposed close to the objective optical axis of the main light receiving system 20. Thereby, the light from the OCT system 60 can be incident on the eye E from an incident direction as close to the vertical direction as possible.

  An example of the configuration of the processing system of the ophthalmic microscope 1B is shown in FIG. Hereinafter, differences from the above embodiment (see FIG. 4) will be described. The control unit 100a controls the optical scanner 41 and the OCT system 60. The data processing unit 200a is provided with an OCT image forming unit 220.

  The control of the optical scanner 41 includes the following: The measurement light LS is sequentially deflected so that the measurement light LS is irradiated to a plurality of positions according to a preset OCT scan pattern.

  Control targets included in the OCT system 60 include a light source unit 61, a polarization controller 63, a corner cube 70, a polarization controller 73, an attenuator 75, a detector 79, and the like.

  The OCT image forming unit 220 forms an image of the eye E based on the detection result of the interference light LC obtained by the detector 79 of the OCT system 60. The control unit 100 a sends detection signals sequentially output from the detector 79 to the OCT image forming unit 220. The OCT image forming unit 220 performs, for example, Fourier transform or the like on the spectrum distribution based on the detection result obtained by the detector 79 for each series of wavelength scans (for each A line), thereby reflecting the reflection intensity profile in each A line. Form. Further, the OCT image forming unit 220 forms image data by imaging each A-line profile. Thereby, a B-scan image (cross-sectional image) and volume data (three-dimensional image data) are obtained.

  The data processing unit 200a may have a function of analyzing the image (OCT image) formed by the OCT image forming unit 220. This analysis function includes retinal thickness analysis and comparative analysis with normal eyes. Such an analysis function is executed using a known application. Further, the data processing unit 200 a may have a function of analyzing an image acquired by the main light receiving system 20. The data processing unit 200a may include an analysis function that combines analysis of an image acquired by the main light receiving system 20 and analysis of an OCT image.

  It is possible to arbitrarily combine the configurations described in the above embodiment or its modification.

1 Ophthalmic microscope 10L, 10R Illumination system 20L, 20R Main light receiving system 21L, 21R Objective lens 23L, 23R Image sensor 26L Beam splitter 30L, 30R Main eyepiece system 31, 31L, 31R Display unit 32L, 32R Main eyepiece lens system 80L, 80R secondary light receiving system 90L, 90R secondary eyepiece system 100 control unit

Claims (5)

An illumination system that illuminates the eye to be examined; and
Each of the first imaging elements includes an objective lens and a first imaging element, the objective optical axes of the objective lens and the first imaging element are arranged non-parallel to each other, and the return light of the illumination light irradiated to the eye to be examined is passed through the objective lens. A pair of main light receiving systems leading to the element;
A pair of main eyepiece systems each including a first display unit and one or more lenses arranged on the display surface side of the first display unit;
An image based on an output from one of the pair of main light receiving systems is displayed on one of the first display units of the pair of main eyepiece systems, and the other of the pair of main light receiving systems is displayed. A control unit that displays an image based on an output from the first image sensor on the other first display unit of the pair of main eyepiece systems;
A light separating element that is arranged between one objective lens of the pair of main light receiving systems and the first imaging element and separates part of the return light of the illumination light;
A pair of secondary light receiving systems for guiding a part of the return light separated by the light separation element to each of a pair of second imaging elements or each of a pair of eyepieces;
Including ophthalmic microscope. 2. The ophthalmic microscope according to claim 1, wherein the pair of auxiliary light receiving systems forms a pair of parallel optical paths that respectively guide a part of the return light. A pair of secondary eyepiece systems each including a second display unit and one or more lenses arranged on the display surface side of the second display unit;
The pair of sub light receiving systems guides part of the return light to each of the pair of second imaging elements,
The control unit displays an image based on an output from one of the second imaging elements of the pair of secondary light receiving systems on the second display unit of one of the pair of secondary eyepiece systems, and the pair of secondary light receiving systems. The ophthalmology according to claim 1 or 2, wherein an image based on an output from the other second imaging element of the light receiving system is displayed on the second display unit of the other of the pair of sub-ocular systems. Microscope. The control unit rotates an image based on an output from the second image sensor according to a position of the pair of sub light receiving systems with respect to the pair of main light receiving systems, and displays the image on the second display unit. The ophthalmic microscope according to claim 3. The ophthalmic microscope according to any one of claims 1 to 4, wherein the control unit performs brightness adjustment of a pair of images based on outputs from the pair of main light receiving systems.

Images