JP6577266B2 - Ophthalmic microscope - Google Patents

Description

  The present invention relates to an ophthalmic microscope.

  In the field of ophthalmology, various microscopes are used for magnifying and observing the eye. As such an ophthalmic microscope, a slit lamp microscope and a surgical microscope are known. Some ophthalmic microscopes include an imaging device for photographing a patient's eye, and others are configured to be used simultaneously by a plurality of observers. As an example of the latter, a surgical microscope provided with a main observation system for an operator and a sub-observation system for an assistant is widely used.

Japanese Patent Application Laid-Open No. 2005-4222 JP 2014-26285 A Special table 2013-540538 gazette

  Conventional ophthalmic microscopes that can be used simultaneously by multiple observers require an observation optical system for the number of observers, which complicates the structure, and the type of observation image provided for each observer. There are problems such as being different. As a typical example of the latter problem, there is a surgical microscope having a configuration in which a stereoscopic image can be provided in the main observation system but a stereoscopic image cannot be provided in the secondary observation system. A surgical microscope equipped with a sub-observation system capable of providing a stereoscopic image is also known, but has a demerit that the structure is complicated.

  Furthermore, even if an observation system capable of providing a stereoscopic image is mounted, it may be difficult to obtain a stereoscopic effect depending on the part of the eye. There are individual differences in fusion ability.

  As described above, the conventional ophthalmic microscope has a problem that information in the depth direction of the observed eye cannot be grasped or is difficult in some cases.

  An object of the ophthalmic microscope according to the present invention is to provide information in the depth direction of a patient's eye with a simple configuration.

The ophthalmic microscope according to one embodiment includes an illumination system, a light receiving system, an eyepiece system, a processing unit, and a display control unit. The illumination system irradiates patient eyes with illumination light. The light receiving system guides the return light of the illumination light from the patient's eye to each of the left image sensor and the right image sensor. The eyepiece system includes a left display unit, a left eyepiece lens arranged on the display surface side of the left display unit, a right display unit, and a right eyepiece lens arranged on the display surface side of the right display unit. The processing unit generates morphological information representing the three-dimensional morphologies of the patient's eyes by processing images based on the outputs from the left imaging element and the right imaging element. The display control unit displays an image based on the form information on the left display unit and the right display unit. Further, the light receiving system performs output at a predetermined rate, and the processing unit sequentially detects an image based on the output at the predetermined rate to obtain a displacement of a predetermined feature point and compares it with a predetermined threshold value. The display control unit generates new form information when it is determined that the displacement has exceeded the threshold, and the display control unit generates an image based on the form information displayed on the left display unit and the right display unit. Update to a new image based on the information. Alternatively, the light receiving system outputs at a predetermined rate, and the processing unit includes a detection unit that sequentially analyzes an image based on the output at the predetermined rate to identify a predetermined feature point, and the feature point is specified. The display control unit generates new form information when the feature point is shifted to the state in which the feature point is not specified, and the display control unit creates an image based on the form information displayed on the left display unit and the right display unit. Update to a new image based on the information.
An ophthalmic microscope according to another embodiment includes an illumination system, a light receiving system, an eyepiece system, an OCT system, a processing unit, and a display control unit. The illumination system irradiates patient eyes with illumination light. The light receiving system guides the return light of the illumination light from the patient's eye to each of the left image sensor and the right image sensor. The eyepiece system includes a left display unit, a left eyepiece lens arranged on the display surface side of the left display unit, a right display unit, and a right eyepiece lens arranged on the display surface side of the right display unit. The OCT system divides light from the OCT light source into measurement light and reference light, and detects interference light between the return light of the measurement light from the patient's eye and the reference light. The processing unit generates morphological information representing the three-dimensional morphologies of the patient's eyes by processing the output from the OCT system. The display control unit displays an image based on the form information on the left display unit and the right display unit. Further, the OCT system outputs at a predetermined rate, and the processing unit includes a detection unit that sequentially analyzes the output at the predetermined rate to obtain a displacement of a predetermined feature point and compares it with a predetermined threshold value. When it is determined that the displacement exceeds the threshold value, new form information is generated, and the display control unit generates an image based on the form information displayed on the left display unit and the right display unit based on the new form information. Update to a new image. Alternatively, the OCT system performs output at a predetermined rate, and the processing unit includes a detection unit that sequentially analyzes the output at the predetermined rate to identify a predetermined feature point, and the feature point is specified. When the state shifts from the state to the state where the feature point is not specified, new form information is generated, and the display control unit generates an image based on the form information displayed on the left display unit and the right display unit based on the new form information. Update to a new image.

  According to the ophthalmic microscope of the embodiment, information in the depth direction of a patient's eye can be provided with a simple configuration.

It is a schematic diagram showing an example of composition of an ophthalmic microscope concerning an embodiment. It is a schematic diagram showing an example of composition of an ophthalmic microscope concerning an embodiment. It is a schematic diagram showing an example of composition of an ophthalmic microscope concerning an embodiment. It is a schematic diagram showing an example of composition of an ophthalmic microscope concerning an embodiment. It is a flowchart showing an example of the usage pattern of the ophthalmic microscope which concerns on embodiment. It is the schematic for demonstrating an example of the usage condition of the ophthalmic microscope which concerns on embodiment. It is a flowchart showing an example of the usage pattern of the ophthalmic microscope which concerns on embodiment. It is a schematic diagram showing an example of composition of an ophthalmic microscope concerning an embodiment. It is a schematic diagram showing an example of composition of an ophthalmic microscope concerning an embodiment. It is a schematic diagram showing an example of composition of an ophthalmic microscope concerning an embodiment. It is a schematic diagram showing an example of composition of an ophthalmic microscope concerning an 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, the content of the literature referred by this specification and arbitrary well-known techniques can be used for embodiment of this invention.

  An ophthalmic microscope is used for observing and photographing a magnified image of a patient's eye in medical treatment and surgery in the ophthalmic field. The target site for observation or imaging may be any part of the patient's eye. For example, the anterior segment may be the cornea, corner, vitreous body, crystalline lens, ciliary body, etc. It may be the retina, choroid or vitreous. Further, the target part may be a peripheral part of the eye such as a eyelid or an eye socket.

  Although the ophthalmic microscope of the embodiment described below includes a Greenough-type stereomicroscope, other embodiments may include a Galileo stereomicroscope. The Greenough-type stereomicroscope is characterized by the fact that the left and right optical systems are equipped with individual objective lenses and the fact that the left and right optical axes are non-parallel, so that it is easy to obtain a stereoscopic image and has a high degree of freedom in design. Have On the other hand, the Galileo stereomicroscope is characterized by the fact that the left and right optical systems have a common objective lens and the right and left optical axes are parallel, and has the advantage that it is easy to combine other optical systems and optical elements. Have.

  In addition, the ophthalmic microscope of the embodiment described below has an optical coherence tomography (OCT) function in addition to a function of observing and photographing a magnified image of a patient's eye, but in other embodiments, the OCT function is It does not have to be provided. Further, instead of or in addition to the OCT function, any measurement function, imaging function, measurement function, treatment function, and the like that can be used in the ophthalmic field may be provided.

<First Embodiment>
[Constitution]
The structural example of the ophthalmic microscope which concerns on this embodiment is shown in FIGS. 1 to 3 show configuration examples 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 a configuration example of the processing system.

  The ophthalmic microscope 1 includes an illumination system 10 (10L, 10R), a light receiving system 20 (20L, 20R), a main eyepiece system 30 (30L, 30R) used by a main observer (operator, etc.), and other A secondary eyepiece system 35 (35L, 35R) used by an observer (an assistant such as a surgical assistant), an irradiation system 40, and an OCT system 60 are provided. When observing the posterior eye part (retinal or the like), the front lens 90 is disposed immediately before the patient's eye E. 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 patient's 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, an ophthalmic surgical microscope, a slit lamp microscope, 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 main 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 patient's eye E coaxially with the left light receiving system 20L. Similarly, in the right light receiving system 20R for acquiring an image presented to the right eye E ₀ R of the main observer, 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 is oblique. It is installed.

  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 patient's eye E, but the position where the optical path of the illumination light is coupled to the light receiving system 20L (20R) is received. It can be at any position in the system 20L (20R). Further, the illumination system and the light receiving system may be arranged non-coaxially. This configuration is applied to a slit lamp microscope, an ophthalmic surgical microscope, and the like.

(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 obtaining an image presented to the left eye E ₀ L of the main observer, and the right light receiving system 20R obtains an image presented to the right eye E ₀ R. It has the composition of. Further, an image based on the output from one or both of the light receiving systems 20L and 20R is presented to the left eye E ₁ L and the right eye E ₁ R of the assistant.

  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).

  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 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 light receiving element 23L (23R) is an area sensor such as a CCD image sensor or a CMOS image sensor. The light receiving elements 23L and 23R can detect at least visible light. Further, the light receiving elements 23L and 23R may be capable of detecting infrared light.

  The above is the configuration of the light receiving system 20 when observing the posterior segment (fundus) of the patient's 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 patient's 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 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. Left eyepiece system 30L has a configuration to present an image of the obtained patient's eye E by the left light receiving system 20L to the left eye E _{0 L} of main viewer, right ocular system 30R is the right light receiving system 20R It has a configuration for presenting the acquired image of the patient's eye E to the right eye E ₀ R. 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). Display unit 31L (31R) is a flat panel display such as an LCD, for example.

It is possible to change the interval between the left eyepiece system 30L and the right eyepiece system 30R. Thereby, the distance between the left eyepiece system 30L and the right eyepiece system 30R can be adjusted according to the eye width of the main 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 main observer can be supported.

(Secondary eyepiece system 35)
In the present embodiment, a pair of left and right auxiliary eyepiece systems 35L and 35R are further provided. The secondary eyepiece systems 35L and 35R have the same configuration as the main eyepiece systems 30L and 30R. That is, the left eyepiece system 35L (right eyepiece system 35R) includes a display unit 36L (36R) and an eyepiece lens system 37L (37R). Further, it is possible to change the interval and relative orientation between the left eyepiece system 35L and the right eyepiece system 35R.

The ophthalmic microscope 1 includes a mechanism for changing the positions of the auxiliary eyepiece systems 35L and 35R. For example, a mechanism for continuously moving the auxiliary eyepiece systems 35L and 35R along a circular trajectory around the patient's eye E is provided. Alternatively, a mechanism that allows the secondary eyepiece systems 35L and 35R to be arranged at a plurality of positions on the circular orbit can be provided. As a result, the distance between the left eyepiece system 35L and the right eyepiece system 35R can be adjusted in accordance with the eye width of the assistant, and also the congestion of the assistant's eyes E ₁ L and E ₁ R is induced. It becomes possible.

(Irradiation system 40)
The irradiation system 40 irradiates the patient's eye E with light (measurement light) for performing OCT measurement from a direction different from the objective optical axes (AL1 and AR1, and AL2 and AR2) of the light receiving system 20. In other embodiments, the illumination system may be capable of irradiating the patient's eye with other light in addition to the measurement light for OCT. Specific examples thereof include light for laser treatment (aiming light, treatment laser light).

  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 is guided to the optical scanner 41.

  Light (measurement light) from the OCT unit 60 is guided by the 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 measurement light converted into a parallel light beam by the collimator lens 52 is guided to the optical scanner 41.

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

  The position of the deflection mirror 44 is determined in advance so that the measurement light guided by the irradiation system 40 is irradiated to the patient's eye E from a direction different from the objective optical axis (AL1 and AR1, and AL2 and AR2) of the light receiving system 20. Has been. 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 horizontal optical scanner (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. Further, as an example of means for changing the focal length (focus position in OCT measurement), any one or more of the collimating lens 52, the imaging lens 42, and the relay lens 43 can be moved along the optical axis. There is a configuration.

(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. 3 is an example of a swept source OCT, which divides light from a wavelength sweep type light source (wavelength variable light source) into measurement light and reference light, and returns return light of measurement light from the patient's eye E. 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 swept light source capable of scanning (sweeping) the wavelength of the emitted light, as in 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 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 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 to the patient's eye E via 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 patient's eye E. The return light of the measurement light LS from the patient's 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 100.

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

(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 sensor 23 includes exposure adjustment, gain adjustment, and shooting rate adjustment.

  The control unit 100 displays various information on the display unit 31 (31L, 31R). For example, the control unit 100 displays an image (or an image or data obtained by processing the image) acquired by the image sensor 23L on the display unit 31L, and an image (or the image acquired by the image sensor 23R). The image or data obtained by processing is displayed on the display unit 31R.

  Similarly, the control part 100 displays various information on the display part 36 (36L, 36R). As described above, the ophthalmic microscope 1 includes a mechanism for changing the positions of the auxiliary eyepiece systems 35L and 35R. Furthermore, the ophthalmic microscope 1 may include a sub-ocular system position detection unit that detects the positions of the sub-ocular systems 35L and 35R, that is, the relative positions of the sub-ocular systems 35L and 35R with respect to the main eye systems 30L and 30R. The auxiliary eyepiece system position detection unit includes, for example, an encoder, a microsensor, and the like. The control unit 100 causes the display units 36L and 36R to selectively display images based on the outputs from the light receiving systems 20L and 20R according to the relative positions of the sub-ocular systems 35L and 35R with respect to the main eyepiece systems 30L and 30R. Is possible. For example, when the secondary eyepiece systems 35L and 35R are arranged facing the main eyepiece systems 30L and 30R, the control unit 100 rotates the image acquired by the right light receiving system 20R by 180 degrees to the left display unit 36L. The image acquired by the left light receiving system 20L can be rotated 180 degrees and displayed on the right display unit 36R. In this case, different images are displayed on the left and right display units 36L and 36R. On the other hand, when the secondary eyepiece systems 35L and 35R are arranged on the left side (right side) with respect to the main eyepiece systems 30L and 30R, the control unit 100 displays an image acquired by the left light receiving system 20L (right light receiving system 20R). It can be displayed on both the left and right display units 36L and 36R. At this time, the images displayed on the display units 36L and 36R are rotated according to the relative positions of the sub-eyepiece systems 35L and 35R with respect to the main eyepiece systems 30L and 30R. In this case, the same image is displayed on the left and right display units 36L and 36R.

  The control of the optical scanner 41 is, for example, for sequentially deflecting the measurement light LS so that the measurement light LS is irradiated to a plurality of positions corresponding to a preset OCT scan pattern.

  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.

  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, an orientation changing unit 30B, an interval changing unit 35A, and an orientation changing unit 35B 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 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.

  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 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. Similarly, the interval changing unit 35A changes the interval between the auxiliary eyepiece systems 35L and 35R.

  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. Similarly, the orientation changing unit 35B changes the relative orientation of the auxiliary eyepiece systems 35L and 35R.

  The control unit 100 includes a processor. In this specification, “processor” means, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an ASIC (Application Specific Integrated Circuit), a programmable logic device (eg, SPLD (Simple ProLigL). It means a circuit such as Programmable Logic Device (FPGA) or Field Programmable Gate Array (FPGA). The control unit 100 implements the functions according to the embodiment by reading and executing a program stored in a storage circuit or a storage device, for example.

  The control unit 100 may include a storage device that stores images acquired by the ophthalmic microscope 1 and information (images, electronic medical record information, etc.) generated by other devices. In addition, the control unit 100 can acquire an image stored in an external storage device by controlling the communication unit 400.

(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 for analyzing images, inspection results, and measurement results, and processing for information related to the subject (electronic medical record information, etc.). The data processing unit 200 includes a processor. The data processing unit 200 includes a magnification changing unit 210, an OCT image forming unit 220, a form information generating unit 230, and a display image forming unit 240.

(Magnification change unit 210)
The magnification changing 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 main observer, assistant, or control unit 100. The magnification changing unit 210 performs the same processing on the image (left image) acquired by the image sensor 23L of the left light receiving system 20L and the image (right image) acquired by the image sensor 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 R of the main observer. In this way, the magnification changing unit 210 functions to change the display magnification of the image presented to the main observer by processing the output from the image sensor 23 (23L, 23R). The image of the same magnification is also presented to the assistant. Note that the magnification changing unit 210 can also provide images with different magnifications for each observer.

  In addition to 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 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.

(OCT image forming unit 220)
The OCT image forming unit 220 forms an image of the patient's 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 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 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 known application software. 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.

(Form information generation unit 230)
The form information generation unit 230 generates information (form information) representing the three-dimensional form of the patient's eye E by at least one of the following processing examples (1) and (2), for example.

  (1) In the first example, form information is generated by processing an image based on outputs from the left and right light receiving systems 20L and 20R. According to the left and right light receiving systems 20L and 20R, the same object (observation site of the patient's eye E) can be photographed from two different positions. Accordingly, there is a parallax between the image based on the output from the left light receiving system 20L (left image) and the image based on the output from the right light receiving system 20R (right image).

  The morphological information generation unit 230 analyzes the left image and the right image using, for example, a triangulation technique, so that from the predetermined reference position to an arbitrary position depicted in both the left image and the right image. The distance can be calculated. The predetermined reference position is, for example, an intermediate position between the center position of the light receiving surface of the left imaging element 23L and the center position of the light receiving surface of the right imaging element 23R. The morphological information generation unit 230 obtains a distance distribution in at least a part of the imaging range by performing such a distance calculation for each of a plurality of positions depicted in both the left image and the right image. This distance distribution (or distribution information obtained by processing this) represents the three-dimensional form of the patient's eye E in the imaging range. In other words, this distance distribution represents the three-dimensional morphology of the imaged tissue surface.

  Note that the method of generating the morphological information based on the outputs from the left and right light receiving systems 20L and 20R is not limited to this, and a method described in other embodiments described later can also be applied.

  (2) In the second example, form information is generated using OCT. Specifically, the control unit 100 controls the OCT system 60 and the optical scanner 41 to execute an OCT scan for at least a part of the imaging range by the imaging elements 23L and 23R. The OCT image forming unit 220 forms image data in this scan range by processing data collected by this OCT scan. This image data is, for example, three-dimensional image data.

  The morphological information generation unit 230 generates morphological information by processing the image data formed by the OCT image forming unit 220. This process includes, for example, extraction of an image region corresponding to the tissue surface of the patient's eye E. When the anterior ocular segment observation is performed, for example, an image region corresponding to the corneal surface, the iris surface, or the lens surface is extracted. When fundus observation is performed, for example, an image region corresponding to the retina surface is extracted. The image area extracted in this way represents the three-dimensional form of the patient's eye E. Note that the extraction of the image region is realized by, for example, a known segmentation process.

  The process of generating the morphological information is not limited to the above method, and can be realized by using an arbitrary modality, an arbitrary imaging technique, an arbitrary measurement technique, and the like. In addition, it is possible to generate form information by combining two or more of a plurality of methods including the above method.

(Display Image Forming Unit 240)
The display image forming unit 240 is presented to the image displayed on the display unit 31 and / or the display unit 36 based on the morphological information acquired by the morphological information generation unit 230, that is, to the main observer and / or assistant. Form an image. The display image forming unit 240 forms such a display image by at least one of the following processing examples (1) and (2), for example.

  (1) In the first example, an auxiliary image that is displayed together with the enlarged image of the patient's eye E and that provides information in the depth direction is formed. Here, the magnified image of the patient's eye E is, for example, a real-time moving image (observed image), a moving image acquired in the past, a frozen image of a moving image, a still image (captured image) captured in the past, or the like. Good. Further, the auxiliary image to be formed may be a shape model that represents a three-dimensional shape of the tissue surface of the patient's eye E, for example.

  Specific examples of such a shape model include a contour line model, a wire frame model, a surface model, and a lattice model. The contour line model is a shape model including one or more lines connecting positions having the same height (distance in the depth direction) with respect to a predetermined reference plane. The wire frame model is a shape model that represents a three-dimensional shape with vertices and lines. The surface model is a shape model obtained by adding surface information (plane, curved surface, etc.) to each section expressed by the wire frame model. The lattice model is a shape model obtained by three-dimensionally deforming a two-dimensional lattice having regular sections.

  The auxiliary image may include an image showing the position of the characteristic part of the patient's eye E and an image showing its outline. Examples of the characteristic part include a vertex, a ridge line, a convex part, and a concave part.

  The display image forming unit 240 includes known application software for creating a shape model from the shape information acquired by the shape information generation unit 230, and creates the shape model by executing this. The shape model created in this way is used as a display image.

  Further, the display image forming unit 240 analyzes the shape information, the shape model, the image based on the output from at least one of the light receiving elements 23L and 23R, the OCT image (three-dimensional image data, etc.), etc. An image region corresponding to the characteristic part is specified. This analysis may include, for example, differential calculation, edge detection, and the like. Further, the display image forming unit 240 creates an image showing the position (center, center of gravity, etc.) and contour of the specified image area. Alternatively, the display image forming unit 240 creates an image in which the position and contour of the specified image region are emphasized. This enhanced image is created, for example, by changing the values (RGB values, luminance values, etc.) of pixels other than the pixels indicating the position and contour of the specified image region to a predetermined constant value (zero, etc.).

  (2) In the second example, an enlarged image (observation image, captured image, etc.) of the patient's eye E based on outputs from the light receiving systems 20L and 20R is processed based on the form information. This processing is performed by, for example, left and right parallaxes based on the left form information generated from the left image obtained by the left light receiving system 20L and the right form information generated from the right image obtained by the right light receiving system 20R. The amount is obtained, and the amount of parallax is reflected in the newly obtained enlarged image. Since the left and right enlarged images created in this manner have the amount of parallax, the observer can easily obtain a stereoscopic effect.

  This example is particularly effective for an enlarged image presented to the assistant. That is, the left and right correspondences of the main eyepiece systems 30L and 30R and the light receiving systems 20L and 20R are fixed, and suitable parallax is always present in the left and right images presented thereby. On the other hand, the positions of the auxiliary eyepiece systems 35L and 35R are variable, and the same image as the image presented to the main eyepiece systems 30L and 30R is also provided to the auxiliary eyepiece systems 35L and 35R (however, as described above) Image selection and rotation). Therefore, stereoscopic vision becomes difficult depending on the positions of the auxiliary eyepiece systems 35L and 35R. For example, when the secondary eyepiece systems 35L and 35R are arranged at positions different from the positions facing the main eyepiece systems 30L and 30R, when the same image is presented to the left and right secondary eyepiece systems 35L and 35R, the original parallax is reversed. Therefore, stereoscopic viewing cannot be performed. However, since the original parallax (or parallax close to it) is given by applying this example, stereoscopic viewing is possible regardless of the positions of the sub-ocular systems 35L and 35R.

  This example includes, for example, processing for converting the viewpoint of the enlarged image based on the form information. Specifically, the display image forming unit 240 first obtains the amount of parallax from the left form information and the right form information. Next, the display image forming unit 240 determines the amount of parallax based on the left image (enlarged image) based on the output from the left light receiving system 20L and the right image (enlarged image) based on the output from the right light receiving system 20R. A pair of enlarged images (viewpoint conversion images) having The pair of viewpoint-converted images are obtained by converting the viewpoint of the left image and the viewpoint of the right image, respectively, according to the relative positions (relative orientations) between the main eyepiece systems 30L and 30R and the sub-eyepiece systems 35L and 35R. It is assumed that the viewpoints of the left and right viewpoint-converted images are rotated in accordance with the direction of the light receiving systems 20L and 20R arranged in accordance with the positions of the main eyepiece systems 30L and 30R, respectively, according to the current auxiliary eyepiece systems 35L and 35R. Corresponds to the positions of the imaging elements 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 units 31 and 36 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 transmits images acquired by the ophthalmic microscope 1 (images acquired by the light receiving system 20, OCT images, etc.) to the external monitor substantially in real time. can do.

[Usage form]
A usage pattern of the ophthalmic microscope of the present embodiment will be described.

(First usage pattern)
An example of the usage form of the ophthalmic microscope is shown in FIG. In this example, morphological information is obtained from the front image (observation image, captured image, etc.) of the patient's eye E, and a shape model created based on this is displayed as an overlay on the observation image. It should be noted that other forms are possible, such as creating and displaying a viewpoint conversion image based on the form information obtained from the front image of the patient's eye E.

(S1: Set the position of the auxiliary eyepiece system)
First, the positions of the auxiliary eyepiece systems 35L and 35R are set in accordance with the position of the assistant with respect to the main observer. The set position is automatically detected by the sub-ocular system position detection unit or manually input using the user interface unit 300, and the information (sub-ocular system position information) is input to the control unit 100. The control unit 100 sends secondary eyepiece position information to the data processing unit 200. The display image forming unit 240 executes processing based on the sub-ocular system position information.

(S2: Start observation of patient's eyes)
When the user performs a predetermined operation, the control unit 100 controls the left and right illumination systems 10L and 10R to start irradiating the patient's eye E with illumination light.

  Further, the control unit 100 displays an image (left observation image) acquired at a predetermined rate by the left imaging element 23L on the left display unit 31L of the main eyepiece system 30L at a predetermined frame rate, and also by the right imaging element 23R. An image acquired at a rate (right observation image) is displayed on the right display unit 31R of the main eyepiece system 30R at a predetermined frame rate. At this time, the display control of the left observation image and the display control of the right observation image are synchronized. The main observer can stereoscopically observe the patient's eye E in real time via the main eyepiece systems 30L and 30R.

  In addition, the control unit 100 selectively selects the left observation image and / or the right observation image for the left display unit 36L of the subocular system 35L and the right display unit 36R of the subocular system 35R based on the subocular system position information. And display them synchronously. The assistant can perform binocular observation of the patient's eye E in real time via the auxiliary eyepiece systems 35L and 35R. It is assumed that stereoscopic viewing is not possible with this binocular observation.

  The main observer operates the left and right light receiving systems 20L and 20R so that a desired observation field is obtained. Further, the observation magnification is adjusted. The observation magnification is changed by a digital zoom (magnification changing unit 210).

(S3: Generate form information)
The form information generation unit 230 generates form information by processing an image based on outputs from the left and right light receiving systems 20L and 20R. The generation of form information in this example is performed according to the above processing example (1) of the form information generation unit 230, for example. The images used for generating the morphological information are, for example, a left image and a right image (based on the left and right signals output from the left and right light receiving systems 20L and 20R that are capturing a moving image of the patient's eye E substantially simultaneously) Left and right frames) or left and right captured images acquired by photographing the patient's eye E at an arbitrary timing.

(S4: Create a shape model)
The display image forming unit 240 creates a shape model that represents the three-dimensional shape of the tissue surface of the patient's eye E based on the shape information generated in step S3. The creation of the shape model in this example is performed according to the above processing example (1) of the display image forming unit 240, for example.

(S5: The shape model is overlaid on the observation image of the auxiliary eyepiece system)
The control unit 100 overlays the shape model acquired in step S4 on the observation image displayed on the left display unit 36L of the secondary eyepiece system 35L, and displays it on the right display unit 36R of the secondary eyepiece system 35R. This shape model is displayed as an overlay on the observed image. The overlay display is executed using a layer function, for example. That is, an observation image is displayed on the first layer, and a shape model is displayed on the second layer. The opacity (alpha value) is arbitrarily set and can be adjusted by the user, for example.

  The control unit 100 or the data processing unit 200 can perform alignment between the observation image (first layer) and the shape model (second layer). This registration may include any image registration method, including feature point extraction and affine transformation, for example.

  An example of an image presented to the assistant in this example is shown in FIG. In the example shown in FIG. 6, an observation image G that is a moving image of the anterior segment is displayed on the left display unit 36L (right display unit 36R) of the subocular system 35L, and the three-dimensional form of the corneal surface is displayed. A contour line model M representing (height distribution) is overlaid on the observation image G. Thereby, the assistant can grasp the height distribution, that is, the three-dimensional shape, while observing the anterior segment of the patient's eye E as a moving image. The assistant can switch between display / non-display of the contour line model M by operating the user interface 300, for example.

(Second usage pattern)
An example of the usage pattern of the ophthalmic microscope is shown in FIG. In this example, morphological information is obtained from the OCT image of the patient's eye E, and a viewpoint conversion image created based on this is displayed. It should be noted that other forms are possible, such as creating and displaying a shape model based on the form information obtained from the OCT image of the patient's eye E.

(S11: Set the position of the auxiliary eyepiece system)
Similar to step S1 in FIG. 5, the positions of the sub-ocular systems 35L and 35R are set.

(S12: Start observation of patient's eyes)
Similar to step S2 in FIG. 5, observation of the patient's eye E is started.

(S13: Perform OCT scan)
The control unit 100 receives a predetermined trigger and causes the OCT unit 60 and the optical scanner 41 to execute an OCT scan of the patient eye E. This OCT scan is, for example, a three-dimensional scan (volume scan), and data of a three-dimensional region including at least a part of an observation site is collected. The OCT image forming unit 220 forms 3D image data based on the collected data.

(S14: Generate form information)
The form information generation unit 230 generates form information by processing the three-dimensional image data formed in step S13. The generation of form information in this example is performed according to the above processing example (2) of the form information generation unit 230, for example.

(S15: Start viewpoint conversion)
The display image forming unit 240 starts viewpoint conversion based on the form information generated in step S14. That is, the display image forming unit 240 performs viewpoint conversion on each frame of the observation image (moving image) provided to the sub-ocular systems 35L and 35R. The viewpoint conversion in this example is performed according to the above processing example (2) of the display image forming unit 240, for example.

(S16: The viewpoint conversion image is displayed on the secondary eyepiece system as an observation image)
The control unit 100 causes the left display unit 36L of the sub-eyepiece system 35L and the right display unit 36R of the sub-eyepiece system 35R to display moving images of the viewpoint conversion images that are sequentially formed in step S15. Thereby, the assistant can perform moving image observation while grasping the three-dimensional shape of the patient's eye E. The assistant can switch execution / stop of the viewpoint conversion by operating the user interface 300, for example.

[Action / Effect]
The operation and effect of the ophthalmic microscope according to the embodiment will be described.

  An ophthalmic microscope according to one embodiment includes an illumination system (10L, 10R), a light receiving system (20L, 20R), an eyepiece system (main eyepiece systems 30L and 30R; sub-eyepiece systems 35L and 35R), and a processing unit ( The data processing unit 200, particularly the morphological information generation unit 230), and the display control unit (control unit 100) are provided.

  The illumination system irradiates patient eyes with illumination light. The light receiving system guides the return light of the illumination light applied to the patient's eye to each of the left imaging element (23L) and the right imaging element (23R). The eyepiece system includes a left display unit (31L, 36L), a left eyepiece lens (32L, 37L) disposed on the display surface side of the left display unit, a right display unit (31R, 36R), and a display on the right display unit. Right eyepieces (32R, 37R) disposed on the surface side. The processing unit generates morphological information representing the three-dimensional shape of the patient's eye by processing an image based on outputs from the left imaging element (23L) and the right imaging element (23R). The display control unit displays an image based on the form information on the left display unit (31L, 36L) and the right display unit right display unit (31R, 36R).

  An ophthalmic microscope according to another embodiment includes an illumination system (10L, 10R), a light receiving system (20L, 20R), an eyepiece system (main eyepiece systems 30L and 30R; auxiliary eyepiece systems 35L and 35R), and an OCT system ( 60), a processing unit (data processing unit 200, in particular, morphological information generation unit 230), and a display control unit (control unit 100).

  The illumination system irradiates patient eyes with illumination light. The light receiving system guides the return light of the illumination light applied to the patient's eye to each of the left imaging element (23L) and the right imaging element (23R). The eyepiece system includes a left display unit (31L, 36L), a left eyepiece lens (32L, 37L) disposed on the display surface side of the left display unit, a right display unit (31R, 36R), and a display on the right display unit. Right eyepieces (32R, 37R) disposed on the surface side. The OCT system divides light from the OCT light source (light source unit 61) into measurement light and reference light, and detects interference light between the return light of the measurement light from the patient's eye and the reference light. The processing unit generates morphological information representing the three-dimensional morphologies of the patient's eyes by processing the output from the OCT system. The display control unit displays an image based on the form information on the left display unit and the right display unit and the right display unit of the eyepiece unit.

  In the embodiment, the processing unit (data processing unit 200) may include a model creation unit (display image forming unit 240). The model creation unit creates a shape model representing the three-dimensional shape of the tissue of the patient's eye based on the shape information. The display control unit displays an enlarged image (observation image, captured image, etc.) of the patient's eye based on the output from the light receiving system on the left display unit and the right display unit of the eyepiece unit, and displays the shape model together with the enlarged image Can be made. For example, the shape model can be displayed in an overlay on the enlarged image of the patient's eye.

  In the embodiment, the processing unit (data processing unit 200) may include an image processing unit (display image forming unit 240). The image processing unit processes an enlarged image (observation image, captured image, etc.) of the patient's eye based on the output from the light receiving system based on the form information. The display control unit can display the image created by the image processing unit on the left display unit and the right display unit of the eyepiece unit.

  Here, the image processing unit may be able to execute processing for converting the viewpoint of the enlarged image based on the form information. The display control unit can display the viewpoint conversion image obtained by the viewpoint conversion on the left display unit and the right display unit of the eyepiece unit.

  In an embodiment, two or more eyepiece systems may be provided including a main eyepiece system (30L and 30R) and one or more secondary eyepiece systems (35L and 35R). The main eyepiece system is used by the main observer (such as a doctor who performs an operation), and the secondary eyepiece system is used by an assistant (such as a surgical assistant). The display control unit can display an image (a shape model, a viewpoint conversion image, etc.) based on the morphological information only on the left display unit and the right display unit of any of the sub-ocular systems.

  According to the embodiment including the above-described configuration, an image based on the morphological information representing the three-dimensional morphologies of the patient's eyes can be presented, so that information on the depth direction of the patient's eyes can be provided to the observer. In addition, when two or more eyepiece systems are provided, an image obtained by a common image sensor can be provided to these eyepiece systems, and thus the configuration is simpler than that of a conventional ophthalmic microscope. Furthermore, in spite of such a simple configuration, information on the depth direction of the patient's eye can be provided to the main observer and / or assistant.

<Second Embodiment>
In this embodiment, several examples of processing for generating morphological information from front images (observation images, captured images, etc.) of patient eyes will be described. The structural example of the ophthalmic microscope which concerns on this embodiment is shown in FIGS. 8 and 9 show examples of the configuration of the optical system. FIG. 10 shows a configuration example of the processing system.

  An ophthalmic microscope 500A shown in FIG. 8 includes the same optical system as that of the first embodiment, but is different from the first embodiment in that it additionally includes a projection system 501A. The projection system 501A projects pattern light having a predetermined shape onto the patient's eye E. Examples of this pattern light include circular bright lines, multiple bright spots arranged in a circle, multiple bright lines arranged concentrically, multiple bright spots arranged concentrically, arranged at equal intervals vertically and horizontally There are a plurality of bright lines (that is, a plurality of bright lines forming a lattice), a plurality of bright points arranged in a lattice point, and the like.

  Projection system 501A includes, for example, a light source and a lens system. This light source includes, for example, a plurality of light emitting elements arranged in a predetermined pattern. Alternatively, the light source may include a display device (liquid crystal display, digital mirror device / projector, etc.) capable of displaying a predetermined pattern image (for example, a plurality of bright spots, one or more bright lines). This light source outputs light in a wavelength band (for example, visible and / or near infrared) in which the image sensors 23L and 23R are sensitive.

  The light beam output from the projection system 501A is deflected by the deflecting member 502A and projected onto the patient's eye E. The deflecting member 502A is disposed in front of or near the patient's eye E. When the deflecting member 502A is arranged in the optical path of the OCT measuring light LS, the deflecting member 502A reflects, for example, visible light from the projection system 501A and transmits the measuring light LS that is near-infrared light. It is a mirror. When the projection system 501A outputs near infrared light, a half mirror can be used as the deflecting member 502A. On the other hand, when the deflection member 502A is disposed at a position deviating from the optical path of the measurement light LS, a reflection mirror can be used as the deflection member 502A.

  An ophthalmic microscope 500B shown in FIG. 9 includes the same optical system as that of the first embodiment, but is different from the first embodiment in that it additionally includes a projection system 501B. The projection system 501B operates with the optical scanner 41 and the like to project pattern light having a predetermined shape onto the patient's eye E. This pattern light may be the same as in the case of FIG. The projection system 500B outputs light in a wavelength band (for example, visible and / or near infrared) in which the image sensors 23L and 23R have sensitivity.

  Projection system 501B includes, for example, an arbitrary light source and a collimating lens. The ophthalmic microscope 500B includes a combining member 502B that combines the optical path of the collimated light output from the projection system 501B with the optical path of the OCT measuring light LS. As the synthesis member 502B, a dichroic mirror or a half mirror is used according to the wavelength band of the collimated light. The combining member 502B guides the collimated light from the projection system 501B to the optical scanner 41. The collimated light that has passed through the optical scanner 41 is irradiated to the patient's eye E via the imaging lens 42, the relay lens 43, and the deflection mirror 44. The control unit 100 deflects the collimated light according to a predetermined pattern. Thereby, pattern light of a predetermined shape is projected onto the patient's eye E.

  FIG. 10 illustrates a configuration example of a processing system of an ophthalmic microscope including the ophthalmic microscope 500A illustrated in FIG. 8, the ophthalmic microscope 500B illustrated in FIG. 9, or another projection system. The processing system shown in FIG. 10 is configured in the same manner as that of the first embodiment, but is different from the first embodiment in that a projection system 501 is additionally provided. The projection system 501 is a projection system 501A shown in FIG. 8, a projection system 501B shown in FIG. 9, or another projection system.

  The return light of the pattern light projected on the patient's eye E is detected by the left and right imaging elements 23L and 23R. Thereby, an image (projected image) of pattern light projected on the tissue surface (corneal surface, iris surface, lens surface, retina surface, etc.) of the patient's eye E is obtained.

  The form information generation unit 230 (processing system) projects a pattern light projection image based on outputs from the image sensors 23L and 23R and a predetermined shape of the pattern light (that is, the pattern light is projected onto a known surface (such as a plane)). Morphological information is generated by comparing the projected image with the projected image in FIG. This comparison processing is executed by a method similar to a known technique such as corneal topography or keratometry (keratography).

  According to such an embodiment, it is possible to suitably measure the three-dimensional shape of the patient's eye. For example, according to the present embodiment, processing can be performed more easily and more quickly than in the first embodiment. Further, the present invention can be applied to an ophthalmic microscope that does not have an OCT system.

<Third Embodiment>
In observation using an ophthalmic microscope, the observation field may be changed. For example, the retina may be observed after observing the anterior segment. Further, the anterior segment or the retina may be observed while moving the observation field. In such a case, it is necessary to change the form information corresponding to the change of the observation field and change the image presented to the observer based on the change. In this embodiment, the automation of such processing will be described.

  A configuration example of a processing system of the ophthalmic microscope according to the present embodiment is shown in FIG. The processing system shown in FIG. 11 is configured in the same manner as that of the first embodiment (or the second embodiment), except that an image change detection unit 250 is additionally provided in the first embodiment (or Different from the second embodiment).

  The image change detection unit 250 detects an image change based on an output from the light receiving system 20L (and / or 20R: the same applies hereinafter). The image change detection unit 250 receives an output (a moving image frame) from the light receiving system 20L at a predetermined rate. This input rate is synchronized with the imaging rate of the image sensor 23L.

  For example, the image change detection unit 250 sequentially analyzes frames input from the light receiving system 20L at a predetermined rate to specify a predetermined feature point, and obtains the position (pixel coordinates) of the specified feature point. When the state is changed from the state in which the feature point is specified to the state in which the feature point is not specified, it is determined that the image has changed due to the movement of the observation field.

  In the state in which the feature points are specified, the image change detection unit 250 compares the position of the feature point in the latest frame with the position of the feature point in the immediately preceding frame, and the displacement between them is a predetermined value. It is determined whether it is below the threshold. If the displacement is less than or equal to the threshold value, it is determined that the observation field has not moved (the image has not changed). On the other hand, when the displacement exceeds the threshold value, it is determined that the observation field has moved.

  When the state shifts from the state where the feature point is specified to the state where it is not specified, or when the displacement exceeds the threshold value, the image change detection unit 250 sends a predetermined signal to the form information generation unit 230. Upon receiving this signal, the morphological information generation unit 230 generates morphological information by executing the processing described in the first embodiment or the second embodiment, for example. Subsequent processes are the same as those of these embodiments.

  According to the present embodiment, it is possible to automatically update the form information in response to the change of the observation field, and to automatically update the information (image) in the depth direction presented to the observer. Therefore, the operability of the ophthalmic microscope is improved and observation can be performed smoothly.

  The plurality of embodiments described above 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.

1 Ophthalmic microscope 10L, 10R Illumination system 20L, 20R Light receiving system 23L, 23R Image sensor 30L, 30R, 35L, 35R Eyepiece system 31L, 31R, 36L, 36R Display unit 32L, 32R, 37L, 37R Eyepiece lens 100 Control unit 200 Data processing section

Claims (8)

An illumination system that emits illumination light to the patient's eyes;
A light receiving system for guiding the return light of the illumination light from the patient's eye to each of the left and right imaging elements;
An eyepiece system including a left display unit, a left eyepiece lens disposed on the display surface side of the left display unit, a right display unit, and a right eyepiece lens disposed on the display surface side of the right display unit;
A processing unit that generates morphological information representing a three-dimensional form of the patient's eye by processing an image based on outputs from the left imaging element and the right imaging element;
A display control unit that displays an image based on the form information on the left display unit and the right display unit ,
The light receiving system outputs at a predetermined rate,
The processing unit includes a detection unit that sequentially analyzes an image based on the output at the predetermined rate to obtain a displacement of a predetermined feature point and compares the displacement with a predetermined threshold, and the displacement exceeds the threshold When it is determined, new form information is generated,
The display control unit updates an image based on the form information displayed on the left display part and the right display part to a new image based on the new form information.
An ophthalmic microscope characterized by that . An illumination system that emits illumination light to the patient's eyes;
A light receiving system for guiding the return light of the illumination light from the patient's eye to each of the left and right imaging elements;
An eyepiece system including a left display unit, a left eyepiece lens disposed on the display surface side of the left display unit, a right display unit, and a right eyepiece lens disposed on the display surface side of the right display unit;
A processing unit that generates morphological information representing a three-dimensional form of the patient's eye by processing an image based on outputs from the left imaging element and the right imaging element;
A display control unit that displays an image based on the form information on the left display unit and the right display unit ,
The light receiving system outputs at a predetermined rate,
The processing unit includes a detecting unit that sequentially analyzes an image based on the output at the predetermined rate to identify a predetermined feature point, and the feature point is not identified from a state in which the feature point is identified Generate new morphological information when transitioning to a state,
The display control unit updates an image based on the form information displayed on the left display part and the right display part to a new image based on the new form information.
An ophthalmic microscope characterized by that . An illumination system that emits illumination light to the patient's eyes;
A light receiving system for guiding the return light of the illumination light from the patient's eye to each of the left and right imaging elements;
An eyepiece system including a left display unit, a left eyepiece lens disposed on the display surface side of the left display unit, a right display unit, and a right eyepiece lens disposed on the display surface side of the right display unit;
An OCT system that splits light from an OCT light source into measurement light and reference light, and detects interference light between the return light of the measurement light from the patient's eye and the reference light;
A processing unit that generates morphological information representing the three-dimensional morphologies of the patient's eyes by processing the output from the OCT system;
A display control unit that displays an image based on the form information on the left display unit and the right display unit ,
The OCT system outputs at a predetermined rate,
The processing unit includes a detection unit that sequentially analyzes the output at the predetermined rate to obtain a displacement of a predetermined feature point and compares it with a predetermined threshold value, and it is determined that the displacement exceeds the threshold value New form information is generated,
The display control unit updates an image based on the form information displayed on the left display part and the right display part to a new image based on the new form information.
An ophthalmic microscope characterized by that . An illumination system that emits illumination light to the patient's eyes;
A light receiving system for guiding the return light of the illumination light from the patient's eye to each of the left and right imaging elements;
An eyepiece system including a left display unit, a left eyepiece lens disposed on the display surface side of the left display unit, a right display unit, and a right eyepiece lens disposed on the display surface side of the right display unit;
An OCT system that splits light from an OCT light source into measurement light and reference light, and detects interference light between the return light of the measurement light from the patient's eye and the reference light;
A processing unit that generates morphological information representing the three-dimensional morphologies of the patient's eyes by processing the output from the OCT system;
A display control unit that displays an image based on the form information on the left display unit and the right display unit ,
The OCT system outputs at a predetermined rate,
The processing unit includes a detection unit that sequentially analyzes the output at the predetermined rate to identify a predetermined feature point, and shifts from a state in which the feature point is specified to a state in which the feature point is not specified New form information is generated,
The display control unit updates an image based on the form information displayed on the left display part and the right display part to a new image based on the new form information.
An ophthalmic microscope characterized by that . The processing unit includes a model creation unit that creates a shape model representing a three-dimensional shape of the tissue of the patient's eye based on the morphological information,
The display control unit displays an enlarged image of the patient's eye based on an output from the light receiving system on the left display unit and the right display unit, and displays the shape model together with the enlarged image. The ophthalmic microscope according to any one of claims 1 to 4 . The processing unit includes an image processing unit that processes an enlarged image of the patient's eye based on the output from the light receiving system based on the form information,
The said display control part displays the image produced by the said image process part on the said left display part and the said right display part. The ophthalmic use as described in any one of Claims 1-4 characterized by the above-mentioned. microscope. The image processing unit generates a viewpoint conversion image by converting a viewpoint of the enlarged image based on the form information,
The ophthalmic microscope according to claim 6 , wherein the display control unit displays the viewpoint conversion image on the left display unit and the right display unit. Comprising two or more eyepiece systems including a main eyepiece system and one or more secondary eyepiece systems;
The display controller according to claim 1 to claim 7, characterized in that to display an image based on the form information only to the left display unit and said right display unit of the at least a portion of the one or more sub-eyepiece system The ophthalmic microscope according to any one of the above.