WO2017110145A1 - Ophthalmic microscope system - Google Patents

Abstract

An illumination system of an ophthalmic microscope system according to one embodiment of the present invention emits illumination light on an eye to be examined. A pair of light-receiving systems, having the respective objective optical axes disposed non-parallel to each other and each including an objective lens and an imaging element, guide return light of the illumination light emitted on the to-be-examined eye to the respective imaging elements via the respective objective lenses. An OCT system splits light from an OCT light source into measurement light and reference light, emits the measurement light on the eye to be examined from a direction different from those of the objective optical axes, and detects interference light obtained by synthesizing the reference light with the return light of the measurement light from the eye to be examined. An optical scanner is used to scan the eye to be examined with the measurement light. An image drawing unit draws the range scanned by the optical scanner on an image based on an output from at least one of the imaging elements of the pair of light-receiving systems.

Description

Ophthalmic microscope system

The present invention relates to an ophthalmic microscope system.

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.

O Ophthalmic microscopes may be used in combination with other ophthalmic devices. For example, a system in which an OCT (Optical Coherence Tomography) apparatus or a laser treatment apparatus is combined with an ophthalmic microscope is known. The OCT apparatus is used for acquiring a cross-sectional image or a three-dimensional image of an eye, measuring a size of an eye tissue (such as retinal thickness), or acquiring functional information (such as blood flow information) of an eye. Laser treatment devices are used for photocoagulation treatment of the retina and corners.

US Pat. No. 7,599,591 US Pat. No. 8,922,882

When an OCT apparatus is combined with an ophthalmic microscope, the observation field of the microscope is generally wider than the OCT scan range. In a conventional ophthalmic microscope system, it is difficult to recognize which part of the observation field is scanned when setting a scan range while observing with a microscope.

Also, the conventional ophthalmic microscope system is equipped with a Galileo stereo microscope. The Galileo stereomicroscope is characterized by the fact that the binocular optical system has a common objective lens and that the left and right optical axes of the binocular optical system are parallel, and it is easy to combine other optical systems and optical elements. Have On the other hand, since it is necessary to use a large-diameter objective lens, there is a demerit that the degree of freedom in optical design and mechanism design is limited. Furthermore, since there is a limit to the distance (eye width) between the left and right eyes of the observer, it is difficult to increase the stereo angle of the binocular optical system and it is difficult to obtain a stereoscopic observation image. . In particular, it is extremely difficult to obtain an observation image having a three-dimensional effect when observing at a high magnification. Conversely, although it is possible to reduce the stereo angle, a dedicated optical element (prism or the like) must be arranged in the binocular optical system, which causes a complicated optical configuration. In addition, it is difficult to finely adjust the stereo angle. There is also a problem in terms of operability. For example, a complicated operation for adjusting the focal position according to the observation site must be performed. Typically, when shifting from the anterior ocular segment observation to the fundus oculi observation, it is necessary to perform an operation of moving the microscope itself in the front-rear direction.

An object of the present invention is to provide an ophthalmic microscope system that does not have the disadvantages of a Galileo microscope and that can easily set a scan range by OCT.

The ophthalmic microscope system according to the embodiment includes an illumination system, a pair of light receiving systems, an OCT system, an optical scanner, and an image rendering unit. The illumination system irradiates the eye to be examined with illumination light. Each of the pair of light receiving systems includes an objective lens and an imaging device, the objective optical axes thereof 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. Lead to. The OCT system divides the light from the OCT light source into measurement light and reference light, irradiates the eye with measurement light from a direction different from the objective optical axis, and combines the return light of the measurement light from the eye with the reference light The interference light thus obtained is detected. The optical scanner is used to scan the eye to be examined with measurement light. The image rendering unit renders a scan range of the optical scanner on an image based on an output from at least one image sensor of the pair of light receiving systems.

According to the embodiment, it is possible to eliminate the disadvantages of the Galileo microscope and easily set the scan range by OCT.

Schematic which shows an example of a structure of the ophthalmic microscope system which concerns on 1st Embodiment. Schematic which shows an example of a structure of the ophthalmic microscope system which concerns on 1st Embodiment. Schematic which shows an example of a structure of the ophthalmic microscope system which concerns on 1st Embodiment. Schematic which shows an example of a structure of the ophthalmic microscope system which concerns on 1st Embodiment. Schematic which shows an example of a structure of the ophthalmic microscope system which concerns on 1st Embodiment. The flowchart which shows an example of the usage condition of the ophthalmic microscope system which concerns on 1st Embodiment. Schematic showing an example of the observation image in the usage pattern of the ophthalmic microscope system which concerns on 1st Embodiment. Schematic showing an example of the observation image in the usage pattern of the ophthalmic microscope system which concerns on 1st Embodiment. Schematic showing an example of the observation image in the usage pattern of the ophthalmic microscope system which concerns on 1st Embodiment. Schematic which shows an example of a structure of the ophthalmic microscope system which concerns on 2nd Embodiment. Schematic which shows an example of a structure of the ophthalmic microscope system which concerns on 3rd and 4th embodiment.

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

The ophthalmic microscope system is used for observing (photographing) 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, or a ciliary body, 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.

The ophthalmic microscope system of the embodiment has a function as another ophthalmologic apparatus in addition to a function as a microscope for magnifying and observing an eye to be examined. Other functions as an ophthalmologic apparatus include at least OCT, and may further include laser treatment, axial length measurement, refractive power measurement, high-order aberration measurement, and the like. Other ophthalmologic apparatuses have an arbitrary configuration capable of performing examination, measurement, and imaging of an eye to be examined by an optical method. In the following embodiments, a configuration in which an OCT function and a laser treatment function are combined with a microscope will be described.

<First Embodiment>
<Constitution>
The configuration of the ophthalmic microscope system according to the embodiment is shown in FIGS. 1 to 4 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. FIG. 3 shows an optical system for providing the OCT function. FIG. 4 shows an optical system for providing a laser treatment function. FIG. 5 shows the configuration of the processing system.

The ophthalmic microscope system 1 includes an illumination system 10 (10L, 10R), a light receiving system 20 (20L, 20R), an eyepiece system 30 (30L, 30R), an irradiation system 40, an OCT system 60, and a laser treatment system. 80. When observing the posterior eye portion (retinal or the like), the front lens 90 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 90 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 surgical microscope, 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 light receiving systems 20L and 20R, respectively. Specifically, the left light receiving system 20L for acquiring an image presented to the left eye E ₀ L of the observer is obliquely provided with a beam splitter 11L made of, for example, a half mirror. The beam splitter 11L couples the optical path of the left illumination system 10L to the optical path of the left light receiving system 20L. The illumination light output from the left illumination system 10L is reflected by the beam splitter 10L and illuminates the eye E to be examined coaxially with the left light receiving system 20L. Similarly, the right light receiving system 20R for acquiring an image presented to the right eye E ₀ R of the observer is obliquely provided with a beam splitter 11R that couples the optical path of the right illumination system 10R to the optical path of the right light receiving system 20R. Has been.

The position of the illumination light with respect to the optical axis of the 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 light receiving system 20L (20R) is received. Any position in the system 20L (20R) may be used.

<Light receiving system 20>
In the present embodiment, a pair of left and right light receiving systems 20L and 20R are provided. The left light receiving system 20L has a configuration for acquiring an image presented to the left eye E ₀ L of the observer, and the right light receiving system 20R is used to acquire an image presented to the right eye E ₀ R. It has a configuration. The left light receiving system 20L and the right light receiving system 20R have the same configuration. The left light receiving system 20L (right light receiving system 20R) includes an objective lens 21L (21R), an imaging lens 22L (22R), and an image sensor 23L (23R).

Note that a configuration in which the imaging lens 22L (22R) is not provided may 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 is easy to arrange optical elements such as filters and to couple optical paths from other optical systems by arranging optical path coupling members (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 left light receiving system 20L, and symbol AR1 indicates the optical axis (objective optical axis) of the objective lens 21R of the right light receiving system 20R. 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 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 left light receiving system 20L (right light receiving system 20R) outward by a predetermined angle (indicated by symbols AL2 and AR2). As described above, the focus lens 24L and the wedge prism 25L are arranged in the left light receiving system 20L, and the focus lens 24R and the wedge prism 25R are arranged in the right light receiving system 20R, whereby the focal position F1 for observing the posterior eye part is observed. To the focal position F2 for anterior ocular segment observation.

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 movable 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 base-in arrangement wedge prism 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.

<Ocular system 30>
In the present embodiment, a pair of left and right eyepiece systems 30L and 30R are provided. The left eyepiece system 30L has a configuration for presenting the image of the eye E to be examined acquired by the left light receiving system 20L to the left eye E ₀ L of the observer, and the right eyepiece system 30L is acquired by the right light receiving system 20L. A configuration for presenting the image of the eye E to be examined to the right eye E ₀ L. The left eyepiece system 30L and the right eyepiece system 30R have the same configuration. The left eyepiece system 30L (right eyepiece system 30R) includes a display unit 31L (31R) and an eyepiece lens system 32L (32R).

The 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 eyepiece systems 30L and 30R depends on the eye width of the observer (distance between pupils, etc.), the size of the apparatus, the design of the apparatus (arrangement of optical system and mechanism, etc.) Limited. 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 eyepiece lens 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- sized display units 31L and 31R can be applied. Can be applied.

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

<Irradiation system 40>
The irradiation system 40 irradiates the eye E with light for realizing the function as the “other ophthalmologic apparatus” from a direction different from the objective optical axis (AL1 and AR1, and AL2 and AR2) of the light receiving system 20. To do. The irradiation system 40 of this example irradiates the eye E with light for OCT (measurement light) and light for laser treatment (aiming light, treatment laser light).

Furthermore, the irradiation system 40 irradiates the eye E with light having a wavelength that can be detected by the image sensors 23L and 23R. This light is used to draw the range of the OCT scan in an image based on the outputs from the image sensors 23L and 23R.

The irradiation system 40 includes an optical scanner 41, an imaging lens 42, a relay lens 43, and a deflection mirror 44. Light from the OCT unit 60, the laser treatment unit 80, and the image rendering light source unit 85 is guided to the optical scanner 41.

The light (measurement light) from the OCT section 60 is guided by the optical fiber 51A and emitted from the end face of the fiber. A collimating lens 52A is disposed at a position facing the fiber end face. The measurement light converted into a parallel light beam by the collimator lens 52A is guided to a member 53 that joins the optical path for OCT and the optical path for laser treatment.

The light from the laser treatment section 80 (aiming light, treatment laser light) is guided by the optical fiber 51B and emitted from the end face of the fiber. A collimating lens 52B is disposed at a position facing the fiber end face. The measurement light converted into a parallel light beam by the collimator lens 52B is guided to the optical path coupling member 53.

The light output from the image rendering light source unit 85 (image rendering light including a wavelength that can be detected by the image sensors 23L and 23R) is a parallel light beam (collimated light) and is guided to the optical path coupling member 86. In this example, the optical path coupling member 86 is disposed between the optical path coupling member 53 and the optical scanner 41, but the present invention is not limited to this. For example, the optical path coupling member 86 can be provided between the collimating lens 52A or 52B and the optical path coupling member 53. More generally, the position of the optical path coupling member 86 can be arbitrarily determined so that the image rendering light is irradiated to the eye E through the optical fiber 41.

In this example, the measurement light, the aiming light, the treatment laser light, and the image rendering light are all irradiated to the eye E through the common optical scanner 41. It is not limited. For example, two optical scanners are provided, and a first group of one or more of measurement light, aiming light, therapeutic laser light, and image rendering light is irradiated to the eye to be examined via the first optical scanner, and The optical system can be configured such that the second group other than the first group is irradiated to the eye to be examined via the second optical scanner.

When the wavelength for OCT and the wavelength for laser treatment are different, a dichroic mirror can be used as the optical path coupling member 53. Typically, broadband light having a center wavelength of about 1050 nm is used as light for OCT, and laser light with a wavelength of about 635 nm can be used as light for laser treatment (for example, the aiming light is Any visible light can be used). On the other hand, when both wavelengths are substantially the same or close, a half mirror can be used as the optical path coupling member 53. As another example, when the timing of performing OCT and the timing of performing laser treatment are different, an optical path switching member such as a quick return mirror can be used as the optical path coupling member 53. In the example shown in FIG. 1 and the like, the measurement light from the OCT unit 60 passes through the optical path coupling member 53 and enters the optical scanner 41, and the light from the laser treatment unit 80 is reflected by the optical path coupling member 53 and is reflected by the optical scanner 41. Is incident on. Similarly, for the optical path coupling member 86, a dichroic mirror, a half mirror, an optical path switching member, or the like can be used.

The optical scanner 41 is a two-dimensional optical scanner, and an x scanner 41H that deflects light in a first direction (x direction) and a y scanner 41V that deflects light in a second direction (y direction) orthogonal to the first direction. Including. Each of the x scanner 41H and the y scanner 41V may be any 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 each of the collimating lenses 52A and 52B or in the vicinity thereof. Furthermore, the optical scanner 41 is disposed, for example, at the entrance pupil position of the imaging 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). A one-dimensional optical scanner can be placed at the exit pupil position and / or the entrance pupil position.

The imaging lens 42 once forms an image of the parallel light flux (measurement light, aiming light, treatment laser light) that has passed through the optical scanner 41. Further, in order to re-image this light in the eye E (observation site such as the fundus and cornea), this light is relayed by the relay lens 43 and reflected by the deflection mirror 44 toward the eye E.

The position of the deflection mirror 44 is determined in advance so that the light guided by the irradiation system 40 is irradiated to the eye E from a direction different from the objective optical axis (AL1 and AR1, and AL2 and AR2) of the light receiving system 20. ing. In this example, the deflection mirror 44 is disposed at a position between the left light receiving system 20L and the right light receiving system 20R where the respective objective optical axes are disposed non-parallel. One of the factors enabling such an arrangement is an improvement in the degree of freedom of the optical configuration due to the arrangement of the relay lens 43. Further, for example, the distance between the position conjugate with the optical scanner in the first direction (x scanner 41H in this example) and the objective lenses 21L and 21R can be designed to be sufficiently small. Can be achieved.

In general, since the scanable range (scannable angle) by the optical scanner 41 is limited, the scanable range can be expanded by applying the imaging lens 42 (or imaging lens system) having a variable focal length. Is possible. In addition, any configuration for expanding the scannable range can be applied.

<OCT section 60>
The OCT unit 60 includes an interference optical system for performing OCT. An example of the configuration of the OCT unit 60 is shown in FIG. The optical system shown in FIG. 4 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 100.

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 a collimator 67 by an optical fiber 66A, converted into a parallel light beam, and guided to a corner cube 70 via an optical path length correction member 68 and a 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 light amount is adjusted under the control of the control unit 100. 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 51A and emitted from the end face of the fiber, and is converted into a parallel light beam by the collimator lens 52A. The measurement light LS converted into a parallel light beam is applied to the eye E through the dichroic mirror 53, the optical scanner 41, the imaging lens 42, the relay lens 43, and the deflection mirror 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 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 divides the interference light by a predetermined branching ratio (for example, 1: 1), thereby generating a pair of interference light LC. 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 the pair of photodetectors. The detector 79 sends the detection result (detection signal) to the control unit 100.

In this example, the swept source OCT is applied, but other types of OCT, such as a spectral domain OCT, can be applied. In spectral domain OCT, a broadband low-coherence light source is used, and the spectral distribution of interference light is detected using a spectroscope.

<Laser treatment unit 80>
The laser treatment unit 80 includes a configuration for performing laser treatment. In particular, the laser treatment unit 80 generates light irradiated to the eye E. The laser treatment unit 80 includes an aiming light source 81A, a treatment light source 81B, a galvano mirror 82, and a light shielding plate 83. In addition, members other than these can be provided in the laser treatment unit 80. For example, an optical element (such as a lens) that allows light generated by the laser treatment unit 80 to enter the end face of the optical fiber 51B can be provided immediately before the optical fiber 51B.

The aiming light source 81A generates aiming light LA for aiming at a site where laser treatment is performed. An arbitrary light source is used as the aiming light source 81A. In the present embodiment, a configuration in which the aim is adjusted while observing a captured image of the eye E is applied. Therefore, a light source (laser light source, light emitting diode) that emits light in a wavelength band in which the image sensor 23 (23L and 23R) has sensitivity. Etc.) is used as the aiming light source 81A. In addition, when the structure which aims at visual observation is applied, visible light is used as the aiming light LA. The aiming light LA is guided to the galvanometer mirror 82.

The treatment light source 81B emits a treatment laser beam (treatment light LT). The treatment light LT may be visible laser light or invisible laser light depending on the application. The treatment light source 81B may be a single laser light source or a plurality of laser light sources that emit laser beams having different wavelengths. The treatment light LT is guided to the galvanometer mirror 82.

The aiming light LA and the treatment light LT reach the same position on the reflection surface of the galvanometer mirror 82. The aiming light LA and the treatment light LT may be collectively referred to as “irradiation light”. The direction of the galvano mirror 82 (the reflection surface thereof) is at least a direction in which the irradiation light is reflected toward the optical fiber 51B (an irradiation direction) and a direction in which the irradiation light is reflected toward the light shielding plate 83 (a stop direction). And changed.

When the galvano mirror 82 is arranged in the stop direction, the irradiation light reaches the light shielding plate 83. The light shielding plate 83 is a member made of, for example, a material and / or form that absorbs irradiation light, and has a light shielding effect.

In the present embodiment, the aiming light source 81A and the treatment light source 81B each continuously generate light. Then, the galvano mirror 82 is arranged in the irradiation direction, so that the eye E is irradiated with the irradiation light. Moreover, the irradiation of the irradiation light with respect to the eye E to be examined is stopped by arranging the galvanometer mirror 82 in the stop direction. In other embodiments, the aiming light source 81A and / or the treatment light source 81B may be configured to be able to generate light intermittently. That is, the aiming light source 81A and / or the treatment light source 81B may be configured to generate pulsed light. For this purpose, the control unit 100 executes pulse control. When this configuration is applied, it is not necessary to provide the galvanometer mirror 82 and the light shielding plate 83.

<Image rendering light source unit 85>
The image rendering light source unit 85 outputs image rendering light including a wavelength that can be detected by the image sensors 23L and 23R. The image rendering light is output as a parallel light beam. The image rendering light source unit 85 is provided with a light source such as an LED or a laser light source. The image rendering light source unit 85 may include a collimating lens.

<Control unit 100>
The control part 100 performs control of each part of the ophthalmic microscope system 1 (see FIG. 5). 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 sensor 23 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 processes an image acquired by the image sensor 23R (or processes it). The image obtained in this manner is displayed on the display unit 31R.

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; The aiming light LA and / or the treatment light LT is sequentially deflected so that the aiming light LA and / or the treatment light LT is irradiated to a plurality of positions according to the laser treatment pattern; the eye E to be subjected to the OCT scan The image rendering light from the image rendering light source unit 85 is sequentially deflected so that the range is rendered on the images acquired by the image sensors 23L and 23R.

Control targets included in the OCT unit 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. Control targets included in the laser treatment unit 80 include an aiming light source 81A, a treatment light source 81B, a galvanometer mirror 82, and the like.

The control unit 100 also controls the image rendering light source unit 85. This control includes switching on / off the output of the image rendering light, changing the characteristics (wavelength, intensity, etc.) of the image rendering light, and the like.

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 the left light receiving system 20L and the right light receiving system 20R. That is, the stereo angle changing unit 20A relatively moves the left light receiving system 20L and the right light receiving system 20R so as to change the angle formed by the objective optical axes (for example, AL1 and AR1). This relative movement is, for example, to move the left light receiving system 20L and the right light receiving system 20R by the same angle in opposite rotation directions. In this movement mode, the direction of the angle bisector formed by the mutual 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.

The focusing unit 24A inserts / withdraws the left and right focus lenses 24L and 24R from 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 in the optical axis direction (simultaneously), or the left and right focus lenses 24L and 24R It may be configured to change the focal length by changing the refractive power of 24R (simultaneously).

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 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 eyepiece systems 30L and 30R. The interval changing unit 30A may be configured to relatively move the left and right eyepiece systems 30L and 30R without changing the relative directions of the optical axes of each other.

The orientation changing unit 30B changes the relative orientation of the left and right eyepiece systems 30L and 30R. The direction changing unit 30B relatively moves the left eyepiece system 30L and the right 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 left eyepiece system 30L and the right 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.

<Data processing unit 200>
The data processing unit 200 executes various types of data processing. This data processing includes processing for forming an image, processing for processing an image, and the like. 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 includes a scaling processing unit 210, an OCT image forming unit 220, and a drawn image information generation unit 230.

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 the observer or by the control unit 100. The scaling processing unit 210 performs the same processing on the image (left image) acquired by the imaging device 23L of the left light receiving system 20L and the image (right image) acquired by the imaging device 23R of the right light receiving system 20R. Apply. Thereby, images of the same magnification are presented to the left eye E ₀ L and the right eye E ₀ L of the observer.

In addition to or in place 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 magnification lens (variable lens system) in each of the left and right light receiving systems 20L and 20R. As a specific example, there is a configuration in which the variable magnification lens is (selectively) inserted / retracted with respect to the optical path, or a configuration in which the variable magnification lens is moved in the optical axis direction. Control related to the optical zoom function is executed by the control unit 100.

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 unit 60. The control unit 100 sends detection signals sequentially output from the detector 79 to the OCT image forming unit 220. The OCT image forming unit 220 applies, for example, a Fourier transform or the like to the spectrum distribution based on the detection result obtained by the detector 79 for each series of wavelength scans (for each A line), thereby obtaining a reflection intensity profile for 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 200 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 may have a function of analyzing an image acquired by the light receiving system 20. The data processing unit 200 may include an analysis function that combines analysis of an image acquired by the light receiving system 20 and analysis of an OCT image.

The drawn image information generation unit 230 generates information (drawn image information) related to an image drawn by deflecting the image drawing light with the optical scanner 41. The control unit 100 projects the image corresponding to the control content of the optical scanner 41 onto the eye E by controlling the optical scanner 41 (and the image rendering light source unit 85) based on the rendered image information. This projected image is picked up by the left and right light receiving systems 20L and 20R (that is, the image pickup devices 23L and 23R). As a result, an image (fundus image, anterior eye image, etc.) of the eye E on which the projection image is drawn is output from the image sensors 23L and 23R.

An example of processing executed by the drawn image information generation unit 230 will be described. OCT scanning conditions (scanning conditions: position, pattern, etc.) are preset. The scan condition may be, for example, any of a default condition, a condition set by the user, and a condition set from a disease name, a test purpose, a past test result (such as an electronic medical record), and the like.

As a first example, the scan condition can be used as extracted image information as it is.

As a second example, extracted image information representing a part of the range represented by the scan condition can be generated. For example, in the three-dimensional scan (raster scan), the optical scanner 41 is controlled to move the measurement light LS along a plurality of parallel lines. In this case, extracted image information representing the outer edge (outline) of the raster scan can be generated. In addition, extracted image information representing a feature position (center position, end position, etc.) in the range represented by the scan condition may be generated.

As a third example, it is possible to generate extracted image information that represents a range represented by a scan condition and represents a position outside the range. For example, the extracted image information can be generated so that four arrow images indicating four vertices in the raster scan range are projected.

Here, the extracted image information of the second and third examples is generated based on the scan condition. In addition, the aspect and generation method of extraction image information are not limited to these.

<User interface 300>
The user interface (UI) 300 has a function for exchanging information between an observer or the like and the ophthalmic microscope system 1. The user interface 300 includes a display device and an operation device (input device). The display device may include the display unit 31 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. In the case where an external monitor is provided, the communication unit 400 converts an image acquired by the ophthalmic microscope system 1 (an image acquired by the light receiving system 20, an OCT image, etc.) to the external monitor substantially in real time. Can be sent.

<Usage pattern>
A usage pattern of the ophthalmic microscope system 1 according to the embodiment will be described. The flowchart of FIG. 6 represents an example of the usage pattern.

(S1: Start observation with a microscope)
First, the user starts observing a microscopic image of the eye E. For example, in response to the user performing an observation start operation with a microscope, the control unit 100 starts output of illumination light from the illumination systems 10L and 10R, and displays an image based on the output from the image sensor 23L. The image is displayed on the display unit 31L, and an image based on the output from the image sensor 23R is displayed on the display unit 31R. The user can binocularly observe the image of the eye E through the eyepieces 30L and 30R. In this observed image, only a part of the eye E is depicted.

An observation image G1 shown in FIG. 7A is an example of an observation image obtained at this stage in the case of fundus observation. The observation image G1 is an image for observing the fundus surface over a wide area, and forms forms such as the optic nerve head, the macula, and blood vessels.

(S2: Set OCT scan conditions)
The user or the ophthalmic microscope system 1 sets OCT scan conditions. When the user sets this, for example, the control unit 10 causes the user interface 300 or the display units 31L and 31R to display an interface (GUI or the like) for setting scan conditions. The user sets scan conditions using this interface.

When the ophthalmic microscope system 1 sets the scan conditions, for example, the control unit 100 or the data processing unit 200 sets the scan conditions based on a disease name, a test purpose, a past test result (such as an electronic medical record), and the like. For example, apply the default scan condition for each disease, apply the default scan condition for each type of screening or screening, or apply the scan condition applied in the past examination of the subject (the eye to be examined). It is possible to apply again.

(S3: Generate drawn image information)
The drawn image information generation unit 230 generates drawn image information based on the scan condition set in step S2.

(S4: Start drawing the scan range)
The control unit 100 controls the image rendering light source unit 85 to start outputting image rendering light, and controls the optical scanner 41 based on the rendering image information generated in step S3. Thereby, the range (scan range) in which the OCT scan is executed according to the scan conditions (scan position, scan pattern, size, etc.) set in step S2 is depicted in the observation image.

At this time, the control unit 100 can repeatedly execute the control of the optical scanner 41 based on the drawn image information. This repetition rate is set to be equal to or less than the frame rate of the observation image, for example. Further, it is possible to detect the movement of the eye E from the change in the position of the feature point in the observation image, and to control the optical scanner 41 so as to displace the irradiation position of the image rendering light in accordance with this movement. Such control is called tracking.

For example, when the optical scanner 41 is controlled so as to move the image rendering light along the outer edge of the raster scan after the observation image G1 of FIG. 7A is obtained, the projected image (frame) of the image rendering light together with the fundus morphology. An observation image G2 in which R1 is depicted is obtained (see FIG. 7B). The user can grasp the scan range set in step S2 from such an observation image G2.

(S5: Was the scan condition changed?)
The user can change the scan condition using the user interface 300. If the scan condition is not changed, such as when the scan condition is confirmed (S5: NO), the process proceeds to step S6.

On the other hand, when the scanning condition is changed (S5: YES), the process proceeds to step S3. When the scan condition is changed, the drawn image information generation unit 230 generates new drawn image information based on the new scan condition (S3). Next, the control unit 100 controls the optical scanner 41 based on the new drawn image information, so that a scan range corresponding to the new scan condition is drawn on the observation image.

For example, when the scan position is changed after the observation image G2 of FIG. 7B is obtained, an observation image G3 in which a frame-like image R2 indicating the scan range after movement is drawn together with the fundus morphology is obtained (FIG. 7C). See). The user can grasp the scan range corresponding to the changed scan condition from such an observation image G3. Note that the change of the scan condition is not limited to the change of the scan position, and may be an arbitrary change of the scan pattern, size, and the like. Steps S3 to S5 are repeated until a desired scan condition is set.

(S6: Perform OCT scan)
When the scan condition is determined (S5: NO), the control unit 100 waits for an OCT scan start trigger. The start trigger is, for example, an instruction from the user or satisfaction of a predetermined condition (tracking or the like). When receiving the input of the start trigger, the control unit 100 controls the optical scanner 41 and the OCT unit 60 based on the current scan condition to execute the OCT scan. This OCT scan is performed on the scan range grasped by the user.

(S7: Process the collected data)
The OCT image forming unit 220 processes the data collected in step S6. Thereby, an OCT image and analysis data are obtained.

(S8: OCT image / analysis data is displayed)
The control unit 100 displays the OCT image and analysis data obtained in step S7 on the user interface 300 and / or the display units 31L and 31R, for example. Thereby, the user can confirm an OCT image and analysis data. Note that it is possible to switch the display of OCT images and analysis data on / off.

Alternatively, the range of the OCT scan executed in step S6 may be stored, and an image indicating the scan range may be drawn in the current observation image together with the display of the OCT image. When a scan pattern composed of a plurality of lines (straight lines, curves, etc.) is applied, a B-scan image along a desired line can be selectively displayed. In this case, a line corresponding to the displayed B-scan image can be drawn in the current observation image. For example, when raster scanning is performed and three-dimensional image data is obtained, when the user selects a desired line, the control unit 100 displays a B-scan image along the selected line, and this line is displayed. An image showing the position of can be drawn in the current observation image.

<Action and effect>
The operation and effect of the ophthalmic microscope system of this embodiment will be described.

The ophthalmic microscope system according to this embodiment includes an illumination system, a pair of light receiving systems, an OCT system, an optical scanner, and an image rendering unit. The illumination system (10L, 10R) irradiates the eye to be examined with illumination light. Each of the pair of light receiving systems (20L, 20R) includes an objective lens (21L, 21R) and an image sensor (23L, 23R). Furthermore, the objective optical axes (AL1, AR1, etc.) are arranged non-parallel. In addition, the pair of light receiving systems guides the return light of the illumination light applied to the eye to be examined to each imaging device via each objective lens. The OCT system (OCT unit 60, a member disposed in the optical path of the measurement light) divides the light from the OCT light source (light source unit 61) into measurement light and reference light, and emits measurement light from a direction different from the objective optical axis. The interference light obtained by irradiating the subject's eye and combining the return light of the measurement light from the subject's eye with the reference light is detected. The optical scanner (41) is used for scanning the eye to be examined with measurement light. An image rendering unit (such as an image rendering light source unit 85) scans a range of light measured by an optical scanner (that is, an OCT scan range) on an image (observation image or the like) based on an output from at least one image sensor of a pair of light receiving systems. ).

Here, the “image based on the output from the image sensor” may be an output image itself from the image sensor, or an image obtained by processing this output image (for example, an enlarged image by the scaling processing unit 210). Further, the scan range may already be drawn on the output image from the image sensor, or the scan range may be drawn before or when the output image is displayed. This embodiment corresponds to the former. The latter will be described later.

According to such an embodiment, since the OCT scan range is drawn on the observation image or the like of the eye to be examined, the scan range can be grasped while observing the eye to be examined with a microscope. In the embodiment, since the Galileo microscope is not applied, there is no disadvantage. For example, in this embodiment, an objective lens is provided for each of the pair of light receiving systems, and a large-diameter objective lens common to both light receiving systems is not used. As a result, the arrangement of elements for OCT, laser therapy, etc. is facilitated, and the apparatus can be miniaturized. Thus, according to the present embodiment, it is possible to eliminate the disadvantages of the Galileo microscope and easily set the scan range by OCT.

In the embodiment, the image rendering unit may be configured to output an image in which the scan range is rendered from the imaging device. For example, in this embodiment, an image representing the scan range is projected onto the eye to be examined, and the projected image is captured by a pair of light receiving systems. Therefore, in the image output from the light-receiving system image sensor, an image representing the scan range is drawn together with the image of the eye to be examined. It should be noted that other configurations can be applied to output an image depicting the scan range from the image sensor. It is also possible to output an image in which the scan range is not drawn from the image sensor and add an image representing the scan range to the output image. These configurations will be described later.

Furthermore, the image rendering unit may include a light source (image rendering light source unit 85) that outputs light having a wavelength detectable by the image sensor. By irradiating the eye to be examined with the light output from the light source, an image in which the scan range is depicted can be output from the image sensor. For example, in the present embodiment, the image rendering light output from the image rendering light source unit 85 is sequentially deflected by the optical scanner 41 to project an image representing the scan range onto the eye to be examined. It should be noted that other configurations can be applied to project an image representing the scan range onto the eye to be examined. For example, a configuration in which a beam having a predetermined cross-sectional shape is projected onto the eye to be examined via an optical deflector can be applied.

In the embodiment, the image rendering unit may include an optical path coupling member that couples the optical path of the light output from the light source for image rendering to the optical path of the OCT system. Here, the optical path coupling member is disposed closer to the OCT light source than the optical scanner. For example, in the present embodiment, the optical path coupling member 86 disposed between the optical path coupling member 53 and the optical scanner 41 changes the optical path of the image rendering light output from the image rendering light source unit 85 to the measurement light for OCT. Coupled to the optical path. Further, the embodiment includes a laser treatment system that irradiates the eye to be examined with an aiming light output from the aiming light source and a treatment light output from the treatment light source via an optical scanner. In the present embodiment, the laser treatment unit 80 corresponds to this. In such an embodiment, a light source for image rendering is provided separately from the laser treatment system (aiming light source). In general, the single treatment range (eg, pattern size in pattern laser treatment) with a laser treatment system is narrower than the OCT scan range. Even when there are such restrictions, it is possible to render the OCT scan range by providing an image rendering light source independently. An embodiment in the case where there is no such restriction will be described later.

In the embodiment, a pair of eyepieces for a user to perform binocular observation can be provided. Each eyepiece includes a display unit and one or more lenses arranged on the display surface side of the display unit. In the present embodiment, the eyepiece unit 30L including the display unit 31L and the eyepiece lens system 32L and the eyepiece unit 30R including the display unit 31R and the eyepiece lens system 32R correspond to a pair of eyepiece units. In addition, the display unit (31L or 31R) included in one (30L or 30R) of the pair of eyepieces is used as an output from the image sensor (23L or 23R) of one (20L or 20R) of the pair of light receiving systems. Display the based image. Furthermore, the display unit (31R or 31L) included in the other (30R or 30L) of the pair of eyepieces is based on the output from the other (20R or 20L) image sensor (23R or 23L) of the pair of light receiving systems. Display an image.

In the embodiment, a setting unit for setting a scan range by the optical scanner may be provided. In that case, the image rendering unit can render the scan range set by the setting unit. The scan range may be set manually or automatically. For example, in the present embodiment, the manual setting unit includes the user interface 300 (and the control unit 100), and the automatic setting unit includes the control unit 100 (and the data processing unit 200). The scan range setting may include various scan condition settings such as a scan pattern setting, a scan position setting, and a scan size setting.

Second Embodiment
In the first embodiment, a dedicated light source for rendering the scan range is provided. In the second embodiment, a configuration in which an aiming light source of a laser therapy system is used for drawing a scan range, that is, a configuration in which a scan range drawing light source and an aiming light source are used in common will be described. Hereinafter, the same elements as those in the first embodiment will be described with the same reference numerals. Further, differences from the first embodiment will be mainly described. Unless otherwise specified, the same configurations, functions, operations, effects and the like as in the first embodiment are applied.

FIG. 8 shows a configuration example of an ophthalmic microscope system according to the second embodiment. The ophthalmic microscope system 1000 has a configuration in which the image rendering light source unit 85 and the optical path coupling member 86 are excluded from the ophthalmic microscope system 1 (FIG. 1) of the first embodiment. The configurations of the OCT unit 60 and the laser treatment unit 80 are the same as those in the first embodiment. The processing system of the ophthalmic microscope system 1000 may be the same as that in the first embodiment (FIG. 5) except that the image rendering light source unit 85 is not included. Hereinafter, the drawings and contents of the first embodiment apply mutatis mutandis.

In the second embodiment, light output from the aiming light source 81A is used as image rendering light. This light includes a wavelength that can be detected by the image sensors 23L and 23R. The aiming light for laser treatment and the image output light may have different wavelengths. In that case, for example, an aiming light source capable of switching and outputting light of two or more different wavelength bands is used. Such an aiming light source may include two or more light sources, and may include a wavelength variable light source. It is also possible to generate light of two or more different wavelength bands using a wavelength selection element (such as a filter).

The image rendering light output from the aiming light source 81A is reflected by the galvanometer mirror 82, guided to the optical fiber 51B, converted into a parallel light beam by the collimator lens 52B, and guided to the optical path of the measurement light LS by the optical path coupling member 53. Further, the image rendering light is irradiated to the eye E from a direction different from both the objective optical axes AL1 and AR1 via the optical scanner 41 and the like.

The drawn image information generation unit 230 generates drawn image information in the same manner as in the first embodiment. The control unit 100 controls the optical scanner 41 based on the generated drawn image information. Accordingly, an image representing the OCT scan range can be projected onto the eye E using the image rendering light. This projected image is picked up by the light receiving systems 20L and 20R. In the images output from the image sensors 23L and 23R, an image representing the scan range is depicted. Images based on the output images are displayed on the display units 31L and 31R of the eyepieces 30L and 30R. Thus, the user can grasp the currently set scan range.

According to the present embodiment, similarly to the first embodiment, the disadvantages of the Galileo microscope can be eliminated and the scan range by OCT can be easily set. Further, since the image representing the OCT scan range is formed using the laser treatment system aiming light source, the configuration can be simplified and the cost can be reduced.

<Third Embodiment>
In the first embodiment and the second embodiment, an observation image in which a scan range is depicted is obtained by projecting an image onto the eye to be examined using light from a light source. On the other hand, in the third embodiment, the scan range is drawn by controlling the image sensor of the light receiving system. Hereinafter, the same elements as those in the first embodiment will be described with the same reference numerals. Further, differences from the first embodiment will be mainly described. Unless otherwise stated, the same configurations, functions, operations, effects, and the like as in the first embodiment are applied.

FIG. 9 shows a configuration example of an ophthalmic microscope system according to the third embodiment. The ophthalmic microscope system 2000 has a configuration in which the laser treatment unit 80, the image rendering light source unit 85, and the optical path coupling member 86 are excluded from the ophthalmic microscope system 1 (FIG. 1) of the first embodiment. The configuration of the OCT unit 60 is the same as that in the first embodiment. The processing system of the ophthalmic microscope system 2000 may be the same as that in the first embodiment (FIG. 5) except that the laser treatment unit 80 and the image rendering light source unit 85 are not provided. Hereinafter, the drawings and contents of the first embodiment apply mutatis mutandis. In addition, in the modification of 3rd Embodiment, the laser treatment part 80 and another function part may be provided.

The control unit 100 controls the image sensors 23L and 23R to output an image depicting the scan range from the image sensor. Therefore, the drawn image information generation unit 230 can generate drawn image information indicating the pixels of the image sensors 23L and 23R corresponding to the scan range based on the scan condition, for example. Such a pixel is specified based on, for example, the characteristics and arrangement of elements included in the optical system. Furthermore, the characteristics (eye refractive power, axial length, etc.) of the eye E can also be referred to. It is also possible to use a technique such as ray tracing.

The control unit 100 processes a signal corresponding to the pixel indicated by the generated drawn image information. For example, the control unit 100 converts a luminance value corresponding to the pixel into a predetermined value. Specifically, the luminance value can be converted to zero, or the RGB value can be converted to a predetermined value. Such pixel value conversion is realized by controlling the image sensors 23L and 23R or by processing images output from the image sensors 23L and 23R. When a raster scan is performed as a typical example, the luminance value of a pixel corresponding to the outer edge of the raster scan range is converted to zero. In this case, an observation image of the eye E in which the scan range is presented with a black frame is obtained. At this time, similarly to the tracking described above, the pixel whose pixel value is converted can be changed in accordance with the movement of the eye E.

According to this embodiment, similarly to the first embodiment, the disadvantages of the Galileo microscope can be eliminated, and the scan range by OCT can be easily set. Furthermore, since the scan range is depicted by controlling the image sensor without providing a light source as in the first embodiment, the configuration can be simplified and the cost can be reduced.

<Fourth embodiment>
In order to obtain an observation image in which the scan range is depicted, in the first and second embodiments, light from a light source is used, and in the third embodiment, an image sensor of a light receiving system is controlled. In the fourth embodiment, the scan range is drawn on the observation image by display control. Hereinafter, the same elements as those in the first embodiment will be described with the same reference numerals. Further, differences from the first embodiment will be mainly described. Unless otherwise stated, the same configurations, functions, operations, effects, and the like as in the first embodiment are applied.

The ophthalmic microscope system of the fourth embodiment includes, for example, the same optical system as that of the third embodiment (see FIG. 9). The processing system may be the same as that of the first embodiment (FIG. 5) except that the laser treatment unit 80 and the image rendering light source unit 85 are not included. Hereinafter, the drawings and contents of the first embodiment will be applied mutatis mutandis with reference mainly to FIGS. 9 and 5. In addition, in the modification of 4th Embodiment, the laser treatment part 80 and another function part may be provided.

The control unit 100 controls the display units 31L and 31R to render the scan range on the observation image of the eye E obtained by the light receiving systems 20L and 20R. Note that the observation image and the scan range may be displayed on a display device provided outside the eyepieces 30L and 30R.

The drawn image information generation unit 230 corresponds to the scan range based on the scan condition based on, for example, the characteristics and arrangement of elements included in the optical system and the characteristics of the eye E (eye refractive power, axial length, etc.). The drawn image information indicating the pixels of the display units 31L and 31R to be generated is generated. At this time, it is also possible to use a technique such as ray tracing.

The control unit 100 renders the scan range on the observation image by converting and displaying the pixel value (luminance value, RGB value, etc.) indicated by the generated rendered image information. Alternatively, the control unit 100 can use a layer display function. For example, an observation image can be displayed on the first layer, and an image indicating the scan range can be displayed on the second layer arranged in front of the first layer. The opacity (alpha value) of the second layer is arbitrarily set.

According to this embodiment, similarly to the first embodiment, the disadvantages of the Galileo microscope can be eliminated, and the scan range by OCT can be easily set. Furthermore, since the scan range is depicted by display control (electronic reticle, electronic mask) without providing a light source as in the first embodiment, the configuration can be simplified and the cost can be reduced. it can.

The first to fourth embodiments are merely examples of 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.

DESCRIPTION OF SYMBOLS 1 Ophthalmic microscope system 10L, 10R Illumination system 20L, 20R Light receiving system 21L, 21R Objective lens 23L, 23R Image sensor 41 Optical scanner 60 OCT part 80 Laser treatment part 85 Image drawing light source unit 230 Drawing image information generation part

Claims (11)

1. An illumination system that illuminates the eye to be examined; and
   A pair including an objective lens and an imaging element, the objective optical axes of which are arranged non-parallel to each other, and the return light of the illumination light irradiated on the eye to be examined is guided to the imaging element via the objective lens. The light receiving system of
   The light from the OCT light source is divided into measurement light and reference light, the measurement light is irradiated to the subject eye from a direction different from the objective optical axis, and the return light of the measurement light from the eye to be examined is the reference light An OCT system for detecting interference light obtained by combining with
   An optical scanner for scanning the eye with the measurement light;
   An ophthalmic microscope system comprising: an image rendering unit that renders a scan range of the optical scanner in an image based on an output from at least one of the pair of light receiving systems.
2. The ophthalmic microscope system according to claim 1, wherein the image rendering unit outputs an image in which the scan range is rendered from the imaging device.
3. The image rendering unit includes a light source that outputs light having a wavelength that can be detected by the imaging device, and irradiates the eye to be examined with light output from the light source, thereby rendering an image in which the scan range is rendered The ophthalmic microscope system according to claim 2, wherein the image is output from an image sensor.
4. 4. The image rendering unit includes an optical path coupling member that is disposed closer to the OCT light source than the optical scanner and couples an optical path of light output from the light source to an optical path of the OCT system. The ophthalmic microscope system described in 1.
5. The ophthalmologic according to claim 4, further comprising: a laser treatment system that irradiates the eye to be examined with the aiming light output from the aiming light source and the treatment light output from the treatment light source through the optical scanner. Microscope system.
6. The ophthalmic microscope system according to claim 4, wherein the aiming light source is used as the light source.
7. 3. The ophthalmic microscope according to claim 2, wherein the image rendering unit includes a first control unit that outputs the image in which the scan range is rendered from the imaging device by controlling the imaging device. system.
8. A pair of eyepieces each including a display unit and one or more lenses arranged on the display surface side of the display unit;
   The display unit included in one of the pair of eyepieces displays an image based on an output from one of the imaging elements of the pair of light receiving systems, and is included in the other of the pair of eyepieces. The ophthalmic microscope system according to any one of claims 1 to 7, wherein the display unit displays an image based on an output from the other imaging device of the pair of light receiving systems.
9. The image rendering unit includes a second control unit that renders the scan range in the image by controlling display means on which an image based on an output from the imaging element is displayed. The ophthalmic microscope system described in 1.
10. A pair of eyepieces each including the display means and one or more lenses arranged on the display surface side of the display means;
    The display means included in one of the pair of eyepieces displays an image based on an output from one of the imaging elements of the pair of light receiving systems, and is included in the other of the pair of eyepieces. The ophthalmic microscope system according to claim 9, wherein the display unit displays an image based on an output from the other imaging device of the pair of light receiving systems.
11. A setting unit for setting a scanning range by the optical scanner;
    The ophthalmic microscope system according to any one of claims 1 to 10, wherein the image rendering unit renders the scan range set by the setting unit into an image based on an output from the imaging device.

Images