JP2017195944A - Ophthalmologic imaging device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To downsize and simplify an ophthalmologic imaging device capable of performing a visual field examination.SOLUTION: An ophthalmologic imaging device includes a scanning optical system, a control part, and an image forming part. The scanning optical system scans the ocular fundus of an eye to be examined with light output from a light source part at least including a visible light source, and receives return light from the ocular fundus at a light reception part. The control part controls the scanning optical system. The image forming part forms an image of the ocular fundus based on a signal from the light reception part. The control part executes first control to control the scanning optical system so as to project visible light output from the visible light source onto the ocular fundus as fixation light for fixation of the eye to be examined, and second control to control the scanning optical system so as to project visible light output from the visible light source onto the ocular fundus as stimulus light for a visual field examination.SELECTED DRAWING: Figure 4

Description

  The present invention relates to an ophthalmologic photographing apparatus.

  Image diagnosis occupies an important position in the field of ophthalmology, and in recent years, the use of a scanning laser ophthalmoscope (SLO) and an optical coherence tomography is progressing. The SLO is an apparatus that forms an image by scanning the fundus at high speed with a weak laser beam using a confocal optical system, and is used for screening and diagnosis of eye diseases. Optical coherence tomography is an optical measurement device that applies a technique called optical coherence tomography (OCT), and forms cross-sectional images, three-dimensional images, and functional images by scanning two-dimensional and three-dimensional regions of the fundus. To do. Optical coherence tomography is also used for imaging the cornea and the like.

  Visual inspection is one of the ophthalmic examinations. The visual field examination is an examination that measures the range and sensitivity of the visual field based on the response of the subject to the stimulus light projected on various positions of the fundus, and is used for evaluating the progress of glaucoma. Patent Document 1 discloses a confocal imaging device capable of performing visual field inspection. This confocal imaging apparatus includes an SLO / OCT system and a display. The display displays a bright spot used as stimulation light and a fixation target for fixing the eye to be examined. The SLO / OCT system repeatedly performs SLO during examination using stimulus light. The confocal imaging device detects the movement of the eye to be examined by comparing a series of SLO images acquired by the SLO / OCT system, and creates a visual field map accordingly.

  As described above, in a conventional ophthalmologic photographing apparatus capable of performing a visual field examination, an element for projecting stimulation light (for example, a display) is provided separately from an element for imaging the fundus (for example, an SLO / OCT system). ) And an element (for example, a display) for presenting the fixation target. Therefore, problems such as an increase in size and complexity of the apparatus have occurred.

US Pat. No. 7,690,791

  An object of the present invention is to reduce the size and simplification of an ophthalmologic photographing apparatus capable of performing visual field inspection.

  The ophthalmologic photographing apparatus according to the embodiment includes a scanning optical system, a control unit, and an image forming unit. The scanning optical system scans the fundus of the eye to be examined with light output from a light source unit including at least a visible light source, and receives light returned from the fundus at a light receiving unit. The control unit controls the scanning optical system. The image forming unit forms a fundus image based on a signal from the light receiving unit. In addition, the control unit controls the scanning optical system so as to project visible light output from the visible light source as fixation light for fixing the eye to be inspected to the fundus, and stimulation for visual field examination. Second control for controlling the scanning optical system so as to project visible light output from the visible light source onto the fundus as light is executed.

  According to the embodiment, it is possible to reduce the size and simplification of an ophthalmologic photographing apparatus capable of performing visual field inspection.

It is the schematic which shows an example of a structure of the ophthalmologic imaging device which concerns on embodiment. It is the schematic which shows an example of a structure of the ophthalmologic imaging device which concerns on embodiment. It is the schematic which shows an example of a structure of the ophthalmologic imaging device which concerns on embodiment. It is the schematic which shows an example of a structure of the ophthalmologic imaging device which concerns on embodiment. It is the schematic for demonstrating an example of operation | movement of the ophthalmologic imaging device which concerns on embodiment. It is the schematic for demonstrating an example of operation | movement of the ophthalmologic imaging device which concerns on embodiment. It is the schematic for demonstrating an example of operation | movement of the ophthalmologic imaging device which concerns on embodiment. It is the schematic for demonstrating an example of operation | movement of the ophthalmologic imaging device which concerns on embodiment. It is a flowchart showing an example of operation | movement of the ophthalmologic imaging device which concerns on embodiment. It is the schematic for demonstrating an example of operation | movement of the ophthalmologic imaging device which concerns on embodiment. It is the schematic for demonstrating an example of operation | movement of the ophthalmologic imaging device which concerns on embodiment. It is the schematic which shows an example of a structure of the ophthalmologic imaging device which concerns on other embodiment. It is the schematic which shows an example of a structure of the ophthalmologic imaging device which concerns on other embodiment.

  An exemplary embodiment of an ophthalmic imaging device is described below. The contents of cited documents and known techniques can be incorporated into the embodiments.

  The ophthalmologic imaging apparatus according to the embodiment acquires a predetermined data distribution (eg, image, layer thickness distribution, lesion distribution) by scanning the posterior eye portion with a light beam. Examples of such an ophthalmic imaging apparatus include SLO and optical coherence tomography. Hereinafter, an ophthalmologic photographing apparatus combining an SLO and an optical coherence tomography will be described as an example. The ophthalmologic photographing apparatus according to the embodiment is used not only for imaging of the fundus but also for visual field inspection, for example, using a light for SLO (visible light) to present a fixation target and apply a light stimulus. be able to.

  Hereinafter, unless otherwise specified, the left-right direction as viewed from the subject is the X direction, the up-down direction is the Y direction, and the front-rear direction (depth direction) is the Z direction. The X direction, the Y direction, and the Z direction define a three-dimensional orthogonal coordinate system.

<Optical system 100>
Examples of the optical system of the ophthalmologic photographing apparatus are shown in FIGS. The ophthalmologic photographing apparatus can operate in a plurality of photographing modes. For example, there are a wide-angle shooting mode and a high-magnification shooting mode as operation modes related to the size (field angle, magnification) of the shooting range. The switching of the angle of view is realized, for example, by selectively using two or more objective lenses having different refractive powers. Or you may comprise so that an angle of view may be changed by changing the deflection angle of the light beam by an optical deflector (optical scanner). The method and configuration for changing the angle of view are not limited to these.

  FIG. 1 shows an example of an optical system in the wide-angle shooting mode. FIG. 2 shows an example of an objective lens system for switching the angle of view. FIG. 3 shows an example of an optical system of the ophthalmologic photographing apparatus in the high magnification photographing mode. 1 and 3 indicate a position optically conjugate with the fundus oculi Ef (fundus conjugate position), and Q indicates a position optically conjugate with the pupil of the eye E (pupil conjugate position). .

  The optical system 100 collects data by scanning the fundus oculi Ef using a light beam. For this purpose, the optical system 100 includes a projection system that projects a light beam onto the eye E through the objective lens system 110, and a light receiving system that receives the return light of the projected light beam through the objective lens system 110. Including. An image of the fundus oculi Ef is formed based on the output from the light receiving system (that is, the data collected by the data collecting unit). The optical system 100 includes an SLO optical system 130 and an OCT optical system 140. The SLO optical system 130 includes an SLO projection system and an SLO light receiving system. The OCT optical system 140 includes an OCT projection system and an OCT light receiving system.

  The ophthalmologic photographing apparatus is provided with an anterior ocular segment imaging system 120 for observing and photographing the anterior ocular segment. The optical system 100, the objective lens system 110, and the anterior ocular segment imaging system 120 are moved in the X direction, the Y direction, and the Z direction. The anterior segment image obtained by the anterior segment imaging system 120 is used for alignment and tracking.

<Objective lens system 110>
In the exemplary embodiment, an objective lens (unit) is prepared for each shooting mode, and an objective lens unit corresponding to the selected shooting mode is selectively used. In this embodiment, as shown in FIG. 2, an objective lens unit 110A for a wide-angle shooting mode (for example, an angle of view of 100 degrees) and an objective lens unit 110B for a high-magnification shooting mode (for example, an angle of view of 50 degrees) are provided. The optical system 100 is selectively disposed in the optical path.

  The objective lens system 110 includes an angle-of-view changing mechanism 115 in addition to the objective lens units 110A and 110B. The angle-of-view changing mechanism 115 includes, for example, a known rotation mechanism or slide mechanism, and selectively places the objective lens units 110A and 110B (exclusively) in the optical path. The angle-of-view changing mechanism 115 arranges the objective lens unit 110A (110B) in the optical path so that the optical axis of the objective lens unit 110A (110B) substantially coincides with the optical axis O of the optical system 100.

  The angle-of-view changing mechanism 115 may have a configuration for manually moving the objective lens units 110A and 110B. In this case, it is possible to provide a type detection unit that detects the type of the objective lens unit arranged in the optical path, specify the photographing mode from the detection result, and execute control according to the specification result. The angle-of-view changing mechanism 115 may have a configuration for moving the objective lens units 110A and 110B electrically (or automatically). In this case, the control unit 200 described later sends a control signal for placing an objective lens unit corresponding to the selected photographing mode in the optical path to the view angle changing mechanism 115.

  The objective lens unit 110A for the wide-angle shooting mode includes lenses 111A and 112A, a dichroic mirror DM1A, and a concave lens 113A. The dichroic mirror DM1A couples the optical path of the optical system 100 and the optical path of the anterior ocular segment imaging system 120. The dichroic mirror DM1A transmits the light guided by the optical system 100 and reflects the light for photographing the anterior segment. A fundus conjugate position P is disposed between the dichroic mirror DM1A and the concave lens 113A.

  The objective lens unit 110B for the high magnification photographing mode includes a lens 111B and a dichroic mirror DM1B. The dichroic mirror DM1B has the same function as the dichroic mirror DM1A.

  The dichroic mirror DM1A and the dichroic mirror DM1B are disposed at (substantially) the same position in the optical path of the optical system 100. This eliminates the need to adjust the position and orientation of the anterior segment imaging system 120 when the imaging mode is switched.

  In an exemplary embodiment, a single dichroic mirror can be configured to be shared by multiple objective lens units. For example, in the example shown in FIG. 2, the dichroic mirrors DM1A and DM1B may be the same member. That is, a configuration in which the objective lens unit 110A including only the lenses 111A and 112A and the concave lens 113A and the objective lens unit 110B including only the lens 111B are selectively used can be applied.

  The objective lens system 110 can be moved along the optical axis O. That is, the objective lens system 110 can be moved in the Z direction with respect to the optical system 100. Thereby, the focal position of the SLO optical system 130 and the focal position of the OCT optical system 140 are changed.

  In exemplary embodiments, more than two objective lens units can be selectively used. For example, an objective lens unit for high-magnification shooting mode, medium-magnification shooting mode, and low-magnification shooting mode, and an angle-of-view changing mechanism that selectively arranges these in the optical path may be provided.

  Hereinafter, the state in which the objective lens unit 110A is disposed in the optical path will be mainly described. Description of similar or similar matters in the state in which the objective lens unit 110B is arranged will be omitted unless otherwise specified.

<Anterior Eye Imaging System 120>
The anterior segment imaging system 120 includes an anterior segment illumination light source 121, a lens 122, an anterior segment imaging camera 123, an imaging lens 124, and a beam splitter BS1. The beam splitter BS1 couples the optical path of the anterior segment illumination light and the optical path of the return light thereof.

  The anterior segment illumination light source 121 includes an infrared light source such as an infrared LED. The anterior segment illumination light emitted by the anterior segment illumination light source 121 is refracted by the lens 122, reflected by the beam splitter BS1 toward the dichroic mirror DM1A, and reflected by the dichroic mirror DM1A toward the eye E. The return light of the anterior segment illumination light from the eye E is reflected by the dichroic mirror DM1A, passes through the beam splitter BS1, and is collected by the imaging lens 124 on the anterior segment imaging camera 123 (detection surface of the image sensor). Is done. The detection surface of the image sensor is arranged at the pupil conjugate position Q (or its vicinity). The image sensor is, for example, a CCD image sensor or a CMOS image sensor.

<SLO optical system 130 and OCT optical system 140>
The optical path of the SLO optical system 130 and the optical path of the OCT optical system 140 are coupled by a dichroic mirror DM2. In the exemplary embodiment, at least a part of the SLO optical system 130 is a telecentric optical system, and at least a part of the OCT optical system 140 is a telecentric optical system, and the optical paths of these telecentric optical systems are coupled by a dichroic mirror DM2. The According to this example, even if the objective lens system 110 is moved and the focal position of the optical system 100 is changed, the aberration of the pupil (for example, the exit pupil by the objective lens system 110) does not increase, thereby facilitating focus adjustment. be able to.

<SLO optical system 130>
The SLO optical system 130 includes an SLO light source 131, a collimating lens 132, a beam splitter BS2, a condenser lens 133, a confocal stop 134, a detector 135, an optical scanner 136, and a lens 137. The beam splitter BS2 couples the optical path of the SLO light projected on the eye E and the optical path of the return light.

  The SLO light source 131 includes a laser diode, a super luminescent diode, a laser driven light source, and the like. The SLO light source 131 outputs light having a wavelength that can be used for SLO. The SLO light source 131 includes at least a visible light source. The SLO light source 131 may be configured to selectively output light in different wavelength bands. Further, two or more lights having different wavelength bands may be output in parallel. An example in which the SLO light source 131 can output infrared light, red light, green light, and blue light will be described later. The SLO light source 131 is disposed at the fundus conjugate position P (or in the vicinity thereof).

  The optical scanner 136 includes an optical scanner 136X that deflects light in the X direction and an optical scanner 136Y that deflects light in the Y direction. One of the optical scanners 136X and 136Y is a low-speed scanner (such as a galvano mirror), and the other is a high-speed scanner (such as a resonant mirror, a polygon mirror, or a MEMS mirror). The reflection surface of the optical scanner 136Y is disposed at the pupil conjugate position Q (or in the vicinity thereof).

  The opening formed in the confocal stop 134 is disposed at the fundus conjugate position P (or in the vicinity thereof). The detector 135 includes, for example, an avalanche photodiode or a photomultiplier tube.

  The light beam (SLO light) output from the SLO light source 131 is converted into a parallel light beam by the collimating lens 132, transmitted through the beam splitter BS2, deflected by the optical scanner 136, refracted by the lens 137, and transmitted through the dichroic mirror DM2. And is projected onto the fundus oculi Ef via the objective lens system 110. The return light of the SLO light projected on the fundus oculi Ef travels in the same optical path in the opposite direction, is guided to the beam splitter BS2, is reflected by the beam splitter BS2, is collected by the condenser lens 133, and is collected by the confocal stop 134. It passes through the aperture and is detected by detector 135.

<OCT optical system 140>
The OCT optical system 140 includes a focusing lens 141, an optical scanner 142, a collimating lens 143, and an interference optical system 150.

  The focusing lens 141 is moved along the optical axis of the OCT optical system 140. Thereby, the focal position of the OCT optical system 140 is changed independently of the SLO optical system 130. After the focusing state of the SLO optical system 130 and the OCT optical system 140 is adjusted by the movement of the objective lens system 110, the focusing state of the OCT optical system 140 can be finely adjusted by the movement of the focusing lens 141.

  The optical scanner 142 includes an optical scanner 142X that deflects light in the X direction and an optical scanner 142Y that deflects light in the Y direction. Each of the optical scanner 142X and the optical scanner 142Y is, for example, a galvanometer mirror. The intermediate position between the two optical scanners 142X and 142Y corresponds to the pupil conjugate position Q (or its vicinity).

  The collimator lens 143 guides the OCT light (measurement light) emitted from the fiber end c3 of the optical fiber f4 to the optical scanner 142 as a parallel light flux, and collects return light of the measurement light from the fundus oculi Ef toward the fiber end c3. Shine.

  The interference optical system 150 includes an OCT light source 151, fiber couplers 152 and 153, a reference prism 154, and a detector 155. The interference optical system 150 includes, for example, a configuration for executing swept source OCT or spectral domain OCT. In the swept source OCT, a variable wavelength light source is used as the OCT light source 151 and a balanced photodiode is used as the detector 155. In the spectral domain OCT, a low coherence light source (broadband light source) is used as the OCT light source 151, and a spectroscope is used as the detector 155.

  For example, the OCT light source 151 emits a light beam L0 that emits light having a center wavelength of 1050 nm. The light L0 is guided to the fiber coupler 152 through the optical fiber f1, and is divided into the measurement light LS and the reference light LR.

  The reference light LR is emitted from the fiber exit end c1 through the optical fiber f2, is converted into a parallel light beam by the collimator lens 156, is folded by the reference prism 154, is made a converged light beam by the collimator lens 157, and enters the fiber incident end c2. The light is guided to the fiber coupler 153 through the optical fiber f3. The reference prism 154 is moved in order to change the optical path length of the reference light LR as in the prior art. Furthermore, a polarization controller, an attenuator, an optical path length correction member, and a dispersion compensation member may be provided in the optical path of the reference light.

  On the other hand, the measurement light LS generated by the fiber coupler 152 is emitted from the fiber end c3 through the optical fiber f4, is converted into a parallel light beam by the collimator lens 143, passes through the optical scanner 142 and the focusing lens 141, and is then transmitted by the dichroic mirror DM2. The light is reflected, refracted by the objective lens system 110, and projected onto the fundus oculi Ef. The measurement light LS is reflected and scattered at various depth positions of the fundus oculi Ef. The return light of the measurement light LS including the backscattered light travels in the opposite direction on the same path, is guided to the fiber coupler 152, and reaches the fiber coupler 153 through the optical fiber f5.

  The fiber coupler 153 generates interference light by superimposing the measurement light LS incident through the optical fiber f5 and the reference light LR incident through the optical fiber f3. FIG. 1 shows the case of the swept source OCT. The fiber coupler 153 splits the interference light at a predetermined branching ratio (for example, 1: 1) to generate a pair of interference light LC. The pair of interference lights LC is detected by a detector 155 (balanced photodiode). In the case of spectral domain OCT, the detector 155 (spectrometer) detects the interference light generated by the fiber coupler 153 by decomposing it into a plurality of wavelength components.

  The detector 155 sends a result (detection signal) obtained by detecting the pair of interference lights LC to a not-shown DAQ (Data Acquisition System). A clock is supplied to the DAQ from the OCT light source 151. This clock is generated in synchronism with the output timing of each wavelength swept within a predetermined wavelength range by the wavelength variable light source. DAQ samples the detection signal based on this clock. The sampling result is sent to a processor for forming an OCT image.

<Processing system>
A configuration example of a processing system of the ophthalmologic photographing apparatus according to the embodiment is shown in FIG. The processing system includes a processor for executing various data processing (signal processing, image processing, calculation, control, storage, etc.).

  The “processor” is, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an ASIC (Application Specific Integrated Circuit), or a programmable logic device (for example, SPLD (Simple ProgramLD). Device), FPGA (Field Programmable Gate Array)) and the like. For example, the processor implements the functions according to the embodiment by reading and executing a program stored in a storage circuit or a storage device.

<Control unit 200>
The control unit 200 includes a configuration for controlling each unit of the ophthalmologic photographing apparatus. The control unit 200 includes a main control unit 201, a storage unit 202, and an inspection data recording unit 203. The functions of the main control unit 201 and the inspection data recording unit 203 are realized by a processor. The storage unit 202 stores various data, various information, and various computer programs. The storage unit 202 includes a semiconductor memory and a magnetic storage device.

  The processing executed by the ophthalmologic photographing apparatus is realized by cooperation between hardware resources (such as a processor) and software (such as a computer program). In addition, an actuator is provided in at least a part of various mechanisms provided in the ophthalmologic photographing apparatus, and the main control unit 201 sends a control signal to the actuator.

<Main control unit 201>
As an example of control related to the objective lens system 110, the main control unit 201 controls the angle-of-view changing mechanism 115 for arranging one of the objective lens units 110A and 110B in the optical path, or moves the objective lens system 110 along the optical axis O. Thus, it is possible to execute control of a moving mechanism (not shown) for movement.

  As an example of control related to the SLO optical system 130, the main control unit 201 can execute control of the SLO light source 131, control of the optical scanner 136, and control of the detector 135. Control of the SLO light source 131 includes lighting, extinguishing, light amount adjustment, aperture adjustment, and the like. Control of the optical scanner 136 includes scanning position control, scanning range control, scanning pattern control, scanning speed control, and the like. Control of the detector 135 includes exposure adjustment of the detection element, gain adjustment, detection rate adjustment, and the like.

  As an example of control related to the OCT optical system 140, the main control unit 201 executes control of the OCT light source 151, control of the optical scanner 142, movement control of the focusing lens 141, movement control of the reference prism 154, and control of the detector 155. can do. The control of the OCT light source 151 includes turning on / off, light amount adjustment, aperture adjustment, and the like. Control of the optical scanner 142 includes scanning position control, scanning range control, scanning pattern control, scanning speed control, and the like. The control of the detector 155 includes exposure adjustment of the detection element, gain adjustment, detection rate adjustment, and the like.

  As an example of control related to the anterior segment imaging system 120, the main control unit 201 can execute control of the anterior segment illumination light source 121, control of the anterior segment imaging camera 123, and the like. Control of the anterior segment illumination light source 121 includes lighting, extinguishing, light amount adjustment, aperture adjustment, and the like. The control of the anterior eye photographing camera 123 includes exposure adjustment of the image sensor, gain adjustment, photographing rate adjustment, and the like.

  As an example of control related to the optical system 100, there is control of the optical system moving mechanism 100A for moving the optical system 100 in the X direction, the Y direction, and the Z direction.

  When shooting as an SLO, the main control unit 201 controls the optical scanner 136 according to a predetermined scanning pattern while turning on (flashing) the SLO light source 131 at a predetermined timing.

  When photographing with visible light, the main control unit 201 performs visible light control that is different from visible light for photographing (fixation timing) only at the timing corresponding to a predetermined fixation position (fixation timing). The SLO light source 131 is controlled to output (fixed visible light). At the fixation timing, the output of the visible light for photographing may be stopped and the visible light for fixation may be output. Alternatively, both the visible light for photographing and the visible light for fixation may be output at the fixation timing.

  When photographing with invisible light (infrared light), the main control unit 201 controls the SLO light source 131 so as to output visible light only at a predetermined fixation timing while performing the photographing control as described above.

  When performing OCT, the main control unit 201 controls the optical scanner 142 according to a predetermined scanning pattern while lighting (flashing) the OCT light source 151 at a predetermined timing.

  When performing the visual field inspection, the main control unit 201 repeatedly controls the optical scanner 136 according to a predetermined pattern (for example, raster scan), while corresponding to a predetermined fixation position (fixation timing) and a predetermined The SLO light source 131 (visible light source) is turned on at the timing corresponding to the stimulation position (stimulation timing).

  An example of an operation for visual field inspection is shown in FIGS. 5A and 5B. FIG. 5A shows a fixation target and stimulation light projected on the fundus oculi Ef. FIG. 5B is a timing chart showing control for projecting a fixation target and stimulation light to the fundus oculi Ef. In FIG. 5B, the horizontal axis is the time axis.

In the example shown in FIG. 5A, a raster scan including a plurality of (M) line scans L _m (m = 1, 2,..., M) in parallel is applied. Each line scan L _m comprises a plurality of scan points which are arranged in a straight line (the irradiation point of the light beam). The main control unit 201 causes the optical scanner 136 to repeatedly execute an operation corresponding to the raster scan.

Further, the main control unit 201 turns on the SLO light source 131 (visible light source) at a preset fixation timing. Fixation timing is synchronized with the raster scan. In this example, the fixation timing includes at least a timing at which the optical scanner 136 is arranged at a position (orientation) corresponding to the njth scan point in the _mjth line scan _Lmj . When the fixation timing includes only this timing, a fixation target T (mj, nj) as a bright spot is projected onto the fundus oculi Ef.

In parallel with such fixation target projection control, the main control unit 201 executes control for projecting stimulation light for stimulating the retina onto the fundus oculi Ef. As the stimulus light projection control, the main control unit 201 turns on the SLO light source 131 (visible light source) at a preset stimulus timing. Stimulation timing is synchronized to the raster scan. In this example, the timing at which the optical scanner 136 is arranged at the position (orientation) corresponding to the ni-th scan point in the mi-th line scan L _mi is the stimulation timing. Thereby, the stimulation light S _i (mi, ni) is projected onto the fundus oculi Ef.

  Note that the fixation timing and the stimulation timing are not limited to the timing corresponding to a single scan point. For example, the SLO light source 136 (visible light source) can be turned on at a timing corresponding to each of a plurality of spatially adjacent scan points. As an example, the SLO light source 136 (visible light source) can be turned on at a timing corresponding to each of a plurality of scan points included in a two-dimensional region such as a disk-shaped region or a cross-shaped region. This two-dimensional region is typically a connected region, and more typically a single connected region.

FIG. 5A shows an example in which a cross-shaped fixation target is presented. More specifically, in the example shown in FIG. 5A, a cross-shaped fixation target centering on the nj-th scan point in the mj-th line scan L _mj is presented. The group of scan points corresponding to this fixation timing includes, for example, a plurality of scan points centered on the njth scan point in the line scan L _mj . That is, an odd number of scan points from the (nj−v) th to the (nj + v) th in the line scan L _mj are included. Here, v is an integer of 1 or more. Further, the group of scan points includes, for example, scan points on a plurality of line scans centered on the line scan L _mj . That is, scan points on an odd number of line scans from the (mj−w) th to the (mj + w) th are included. Here, w is an integer of 1 or more. Further, the number of corresponding scan points on the _mjth line scan L _mj is 2v + 1 as described above. On the other hand, the number of corresponding scan points on the corresponding line scan other than the line scan L _mj is less than 2v + 1. The number of corresponding scan points in each corresponding line scan other than the line scan L _mj may be equal or different. Further, the vertical size of the cross-shaped fixation target is determined by the number of corresponding line scans, and the horizontal size is determined by the number of corresponding scan points on the line scan L _mj . These are set arbitrarily. For example, the number of corresponding line scans and the number of corresponding scan points on the line scan L _mj can be set so that the vertical size and the horizontal size of the cross-shaped fixation target are equal to each other ( However, it is not limited to this). Even when another two-dimensional fixation target is presented, a group of scan points corresponding to the fixation timing can be set in the same manner.

  Further, the main control unit 201 can sequentially project stimulation light to a predetermined number of positions while repeatedly executing the same raster scan and the same fixation target projection control. A plurality of positions that are the targets for the stimulation light projection are set in advance as a protocol for visual field inspection.

  In addition, the main control unit 201 sequentially projects the stimulation light to a predetermined number of positions while repeatedly executing the same raster scan and the control for projecting the fixation target to the first fixation position, and the end. Later, the fixation position can be switched, and the stimulation light can be sequentially projected to a predetermined number of positions while repeatedly executing the same raster scan and the control for projecting the fixation target to the second fixation position. Such control can be sequentially applied to a plurality of fixation positions. A plurality of positions serving as stimulation light projection targets and a plurality of fixation positions including the first fixation position and the second fixation position are set in advance as a protocol for visual field inspection. It is also possible to manually set or change the fixation position.

  As described above, it is also possible to apply the control so that the raster scan is repeatedly performed while moving the fixation position continuously or stepwise instead of the control of alternately performing the raster scan and the fixation position movement. .

F _k (k = 1, 2,...) Shown in FIG. 5B indicates each frame of the SLO image. Each frame F _k is an SLO image created from data collected by one raster scan (a series of line scans L _{1 to} L _M ) shown in FIG. 5A. In the case of creating a single frame by combining two or more frames, the synthesized frame may be a single frame F _k.

A single operation of the optical scanner 136X (X scanner) corresponds to one line scanning _{L m.} Further, once the operation of the optical scanner 136Y (Y scanner) corresponds to the movement of the light beam projection position from the line scan L ₁ in the direction orthogonal to the line scan L _m to the line scan L _M. The main control unit 201 realizes the operation of the optical scanner 136 corresponding to the raster scan illustrated in FIG. 5A by cooperatively controlling the optical scanner 136X and the optical scanner 136Y. Further, the main control unit 201 repeatedly executes such linked control of the optical scanner 136X and the optical scanner 136Y. Thereby, a plurality of frames F ₁ , F ₂ ,... Are acquired sequentially.

The main control unit 201, the control synchronized with fixation timing of such an optical scanner 136, to project the fixation target onto the fundus oculi Ef in the control period corresponding to each frame F _k. Furthermore, when the main control unit 201 or the user issues a trigger Trg for applying a light stimulus, the main control unit 201 projects stimulation light onto the fundus oculi Ef at a stimulation timing corresponding to a preset application position. It should be noted that the time from the generation of the trigger Trg to the projection of the stimulation light may be the shortest time considering the time required for control.

Stimulation light may not be projected onto the target position due to the effects of eye movement and blinking. In order to deal with such a situation, it is possible to detect the occurrence of eye movements and blinks by analyzing sequentially acquired frames F _k . Detection of eye movement, for example, the characteristic site in the frame F _k is performed based on the change with time of the position of (the optic papilla, macula, blood vessels, lesions, scars, etc. of the laser treatment). Detection of blinking, for example, fundus oculi Ef (the fundus eg characteristic site) to the frame F _k is the whether it is rendered, or, is performed by referring to a predetermined image quality parameters (e.g., contrast). When an abnormality such as eye movement or blinking is detected, the main control unit 201 can project the stimulation light on the target position again. At this time, the stimulation light may be re-projected after detecting that the abnormality has been eliminated. Or you may make it add that abnormality was detected to the result data of a visual field inspection.

<Storage unit 202>
The storage unit 202 stores information, data, programs, and the like used by the ophthalmologic photographing apparatus. Further, the storage unit 202 acquires data (SLO image, OCT image, anterior eye image, etc.) acquired by the ophthalmologic photographing apparatus.

<Inspection data recording unit 203>
In the visual field inspection, stimulation light is projected onto the fundus oculi Ef, and the content of the subject's reaction to it (whether or not the stimulation light has been recognized) is recorded. Such processing is sequentially performed on a plurality of positions of the fundus oculi Ef. The examination data recording unit 203 accumulates a set of the projection position of the stimulus light and the content of the reaction. Thereby, the distribution of reaction contents at a plurality of positions of the fundus oculi Ef, that is, the distribution of the visual field range and the distribution of visual field sensitivity are obtained.

The projection position of the stimulus light is obtained from the stimulus timing. In the above example, the projection position of the stimulation light S _i (mi, ni) shown in FIG. 5A is recorded (i = 1, 2,..., N). In addition, the reaction of the subject is input using the UI unit 230, for example. Or when the function which detects the reaction of a retina and a change of a biological signal is provided in the ophthalmologic imaging device, the reaction content of a subject can be acquired from the detection result. This function is realized using, for example, OCT (polarized light OCT, etc.), time-series analysis of SLO images, fluorescence imaging, and the like.

6A shows a plurality of inspection positions (stimulation positions) in the visual field inspection of the eye E. FIG. These stimulation positions are represented by the same symbols S _i (mi, ni) as the stimulation light in FIG. In this example, a plurality of stimulation positions S ₁ (m1, n1), S ₂ (m2, n2),..., S _N (mN, nN) arranged in a grid pattern are set.

FIG. 6B shows an example of a visual field map based on the result of visual field inspection performed on a plurality of stimulation positions S _i (mi, ni) (i = 1, 2,..., N). The field-of-view map of this example shows a stimulus position that did not respond to the light stimulus (that is, a stimulus position at which the subject could not recognize the stimulus light, called a dark spot) Ur (r = 1, 2,... ) Distribution. The visual field map is not limited to this. For example, it is possible to create a visual field map representing a distribution of stimulation positions having a response to a light stimulus, or a visual field map having a different representation mode of the stimulation position depending on the presence or absence of a response to the light stimulus. In addition, when the stimulation conditions such as the intensity of light stimulation (light amount of light beam), the stimulation time, and the number of stimulations are variable, it is possible to create a visual field map representing the distribution of recognizable limit light amount (sensitivity).

<Image Forming Unit 210>
The image forming unit 210 forms an image of the fundus oculi Ef based on the data collected by the optical system 100. Since the ophthalmologic photographing apparatus 1 can execute both SLO and OCT, the image forming unit 210 includes an SLO image forming unit 211 and an OCT image forming unit 212.

  The SLO image forming unit 211 forms an SLO image based on the data collected by the SLO optical system 130. More specifically, the SLO image forming unit 211 forms an SLO image based on the detection signal input from the detector 135 and the pixel position signal input from the control unit 200, as in the conventional SLO. To do.

  The OCT image forming unit 212 forms an OCT image based on the data collected by the OCT optical system 140. More specifically, the OCT image forming unit 212 forms an OCT image based on the detection signal input from the detector 155 and the pixel position signal input from the control unit 200. The OCT image forming unit 212 generates a spectrum distribution from the output from the detector 155 for each series of wavelength scans (for each A line) as in the conventional case, and performs Fourier transform or the like on the spectrum distribution. Thereby, the reflection intensity profile in each A line is obtained. Further, the OCT image forming unit 212 forms a cross-sectional image (B scan image) by imaging the reflection intensity profile of each A line.

  The OCT image forming unit 212 can form a three-dimensional image (a three-dimensional data set such as stack data and volume data) based on a plurality of B scan images. Furthermore, the OCT image forming unit 212 can form a display image by rendering a three-dimensional data set.

  The image forming unit 210 can form an anterior segment image based on the output from the anterior segment imaging camera 123. Various images (image data) formed by the image forming unit 210 are stored in the storage unit 202, for example.

<Data processing unit 220>
The data processing unit 220 executes various data processing. As an example of data processing, there is processing for image data formed by the image forming unit 210 or another device. Examples of this processing include various types of image processing, image analysis processing, and diagnostic support processing such as image evaluation based on image data.

<User interface unit 230>
The user interface (UI) unit 230 has a function for exchanging information between the user and the ophthalmologic photographing apparatus. The UI unit 230 includes a display device and an operation device (input device). The display device includes, for example, a liquid crystal display (LCD). The operation device includes various hardware keys and / or software keys. The control unit 200 receives an operation content for the operation device and outputs a control signal corresponding to the operation content to each unit. 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.

<Operation>
An example of the operation of the ophthalmologic photographing apparatus according to the embodiment will be described. An example of the operation is shown in FIG.

(S1: Select wide-angle shooting mode)
In this example, the wide-angle shooting mode is selected first. The main control unit 201 or the user places the objective lens unit 110A in the optical path.

(S2: observe the anterior segment)
In response to a predetermined trigger, the main control unit 201 controls the anterior ocular segment imaging system 120 to start acquisition of an anterior ocular segment observation image (moving image).

(S3: Alignment)
The main control unit 201 performs alignment with reference to the anterior segment image obtained by the anterior segment imaging system 120. The alignment is performed by, for example, XY alignment in which the optical axis O of the optical system 100 coincides with the pupil center of the eye E, and Z for disposing the optical system 100 at a position away from the eye E by a predetermined distance (working distance). Alignment. The alignment is auto alignment or manual alignment performed by a known method. After completion of alignment, focusing, OCT optical path length adjustment, polarization state adjustment, or the like may be performed.

(S4: photographing the fundus)
After completing the alignment, the main control unit 201 collects data of the fundus oculi Ef by the SLO optical system 130 and the OCT optical system 140. The SLO image forming unit 211 forms an SLO image based on the data collected by the SLO optical system 130. The OCT image forming unit 212 forms an OCT image based on the data collected by the OCT optical system 140. At this time, a different light beam can be projected at a timing corresponding to a predetermined fixation position. For example, it is possible to project light having a wavelength different from others or light having a light amount different from others.

  Note that the timing of photographing the fundus oculi Ef is not limited to the timing of this example. For example, fundus photographing can be performed after visual field inspection, or fundus photographing can be performed during visual field inspection. Further, fundus imaging may be continuously performed in at least a part of a period during which the visual field inspection is performed and / or at least a part of a period during which the visual field inspection is not performed. The continuous fundus photographing may be, for example, infrared moving image observation using the SLO optical system 130. An ophthalmologic photographing apparatus capable of performing infrared moving image observation and visual field inspection in parallel will be described later.

(S5: Field inspection)
In this example, the visual field inspection is performed after the fundus photographing is completed. In the visual field inspection, the main control unit 201 controls the SLO optical system 130 in order to perform fixation target projection and stimulation light projection at predetermined timings, respectively. The examination data recording unit 203 creates a visual field map by accumulating a set of stimulation light projection positions and reaction contents.

(S6: Display test results)
The main control unit 201 causes the UI unit 230 (display device) to display the SLO image and the OCT image acquired in step S4 and the visual field map created in step S5. At this time, the main control unit 201 can display a composite image of the SLO image and the visual field map. For example, the main control unit 201 can display the field-of-view map as an overlay on the SLO image. The alignment between the SLO image and the visual field map is performed based on, for example, a fixation position at the time of SLO scanning and a fixation position at the time of visual field inspection. It is also possible to display a composite image of a planar image formed from data (three-dimensional image) collected by OCT scanning of a three-dimensional region of the fundus oculi Ef and a visual field map.

(S7: Do you perform detailed inspection?)
The user can determine whether or not to perform further photographing by changing the angle of view by observing the image displayed in step S6. For example, when a wide area screening is performed by observing an SLO image, an OCT image, or a visual field map acquired in the wide-angle imaging mode, and a part to be observed in more detail is found, it is possible to shift to high magnification imaging of the part.

  An example of information displayed in step S6 is shown in FIG. 8A. A symbol G1 represents (a part of) an SLO image obtained in the wide-angle shooting mode. Reference numeral Sc1 represents a dark spot indicated by the visual field map. The user can grasp the position of the dark spot Sc1 on the fundus oculi Ef from the composite image shown in FIG. 8A. When it is desired to grasp the detailed position of the dark spot Sc1, or when it is desired to observe the dark spot Sc1 and its surroundings in detail, the process shifts to the high magnification photographing of the dark spot Sc1 and its surroundings.

  When the detailed inspection is not performed (S7: No), the process ends (end). On the other hand, when a detailed inspection is performed (S7: Yes), the process proceeds to step S11.

(S11: Select high-magnification shooting mode)
When the detailed inspection is performed (S7: Yes), the objective lens unit 110B corresponding to the high magnification photographing mode is arranged in the optical path.

(S12: Specify the inspection site)
The user or the ophthalmologic imaging apparatus designates a part to be subjected to a detailed examination. For example, the examination site can be designated by designating a desired position or range in the SLO image (composite image) displayed in step S6 using the UI unit 230 (operation device). In addition, the examination site can be specified so as to include the dark spot represented by the visual field map and the characteristic site of the fundus oculi Ef (optic nerve head, macular, etc.). When the composite image shown in FIG. 8A is obtained, for example, a range A1 including the dark spot Sc1, the optic disc, and the macula is designated as a target for high-magnification imaging.

(S13: Observe the anterior segment)
Similar to step S2, the main control unit 201 controls the anterior ocular segment imaging system 120 to acquire an anterior ocular segment observation image.

(S14: Alignment)
Alignment is performed in the same manner as in step S3.

(S15: photographing the fundus)
Similar to step S4, an SLO image and an OCT image of the fundus oculi Ef are acquired. The SLO image and the OCT image are based on data collected by scanning a range A1 shown in FIG. 8A, for example.

(S16: Field inspection)
A visual field inspection is performed in the same manner as in step S5. This visual field inspection covers at least a part of the range A1.

(S17: Display test results)
The main control unit 201 causes the UI unit 230 (display device) to display the SLO image and the OCT image acquired in step S15 and the visual field map created in step S16. For example, a composite image as shown in FIG. 8B is displayed. A symbol G2 represents (a part of) an SLO image obtained in the high-magnification shooting mode. Reference numeral Sc2 represents a dark spot obtained by the visual field inspection in step S16. The dark spot Sc2 indicates the detailed position of the dark spot Sc1 obtained in the wide-angle shooting mode.

(S18: Do you examine other parts?)
When other detailed site inspections are not performed (S18: No), the process ends (END). On the other hand, when a detailed examination of another part is performed (S18: Yes), the process returns to step S12. The detailed inspection of other parts is performed, for example, when dark spots exist at distant positions. When all the detailed inspections of the desired part have been completed (S18: No), the process ends (END).

<Other embodiments>
A case where visual field inspection is performed using an ophthalmologic photographing apparatus that can output light beams of a plurality of wavelength bands will be described. An example of a part of the optical system of such an ophthalmologic photographing apparatus is shown in FIG. Note that the drawings and descriptions of the above embodiment are referred to unless otherwise specified.

  The optical system shown in FIG. 9 represents an SLO light source unit 131A applied in place of the SLO light source 131 and the collimating lens 132 shown in FIGS. Other portions may be the same as in the above embodiment.

  The SLO light source unit 131A can output both infrared light and visible light. The SLO light source unit 131A includes an infrared light source 131a, a red light source 131r, a green light source 131g, and a blue light source 131b. The infrared light source 131a outputs a (near) infrared light beam. The red light source 131r outputs a light beam in the red band. The green light source 131g outputs a green band light beam. The blue light source 131b outputs a light beam in the blue band. Each of these light sources 131a, 131r, 131g, and 131b is, for example, a semiconductor laser.

  The infrared light output from the infrared light source 131a is converted into a parallel light beam by the collimating lens 132a. The red light output from the red light source 131r is converted into a parallel light beam by the collimating lens 132r. The green light output from the green light source 131g is converted into a parallel light beam by the collimating lens 132g. The non-blue light output from the blue light source 131b is converted into a parallel light beam by the collimating lens 132b.

  The beam splitter BSr synthesizes the red light converted into the parallel light beam by the collimating lens 132r into the optical path of the infrared light converted into the parallel light beam by the collimating lens 132a. The beam splitter BSg combines the green light converted into a parallel light beam by the collimator lens 132g into the optical path of the infrared light converted into a parallel light beam by the collimator lens 132a. The beam splitter BSb synthesizes the blue light converted into the parallel light beam by the collimating lens 132b into the optical path of the infrared light converted into the parallel light beam by the collimating lens 132a. Three beam splitters BSr, BSg, and BSb synthesize optical paths of four light beams having different wavelength bands. This combined optical path is guided to the beam splitter BS2.

  An example of a control system of the ophthalmologic photographing apparatus according to this embodiment is shown in FIG. The main control unit 201 controls each of the infrared light source 131a, the red light source 131r, the green light source 131g, and the blue light source 131b. The main control unit 201 may include a synchronization circuit for performing synchronization control of these light sources 131a, 131r, 131g, and 131b. The synchronization circuit may be configured to synchronize the control of the light sources 131a, 131r, 131g, and 131b with the control of the optical scanner 136.

  According to such an ophthalmologic photographing apparatus, by controlling the infrared light source 131a and the visible light source (at least one of the red light source 131r, the green light source 131g, and the blue light source 131b) in parallel, The projection of the fixation target and the application of the light stimulus can be executed in parallel.

  Infrared moving image observation is executed as follows, for example. The main control unit 201 controls the infrared light source 131a so as to output infrared light at predetermined time intervals while repeatedly controlling the optical scanner 136 corresponding to a predetermined scan pattern (raster scan or the like). The SLO image forming unit 211 forms one frame based on data collected in one scan pattern. The SLO image forming unit 211 sequentially creates frames in synchronization with the scan repetition rate.

  In parallel with such control for infrared moving image observation, the main control unit 201 executes control for projecting a fixation target and control for applying a light stimulus. The fixation target projection control and the light stimulus application control are executed, for example, in the same manner as the timing chart of FIG. 5B of the above embodiment. That is, the main control unit 201 projects a fixation target onto the fundus oculi Ef during a control period corresponding to each frame at a fixation timing synchronized with control for infrared moving image observation. Furthermore, when the main control unit 201 or the user issues a trigger Trg for applying a light stimulus, the main control unit 201 projects stimulation light onto the fundus oculi Ef at a stimulation timing corresponding to a preset application position.

  The ophthalmologic photographing apparatus according to the present embodiment can correct the projection position of the stimulation light in real time while monitoring the fixation disparity of the eye E. For this purpose, the data processing unit 230 of this embodiment includes an analysis unit 221.

  The analysis unit 221 obtains the displacement of the fundus oculi Ef by analyzing the frame repeatedly formed by the image forming unit 210 (SLO image forming unit 211). This analysis processing includes, for example, processing of obtaining the position (coordinate in the frame) of the characteristic part (optic nerve head, blood vessel, diseased part, etc.) by analyzing the pixel value of the frame, and the position of the characteristic part between different frames. Processing for obtaining a series change.

  The time-series displacement of the characteristic part specified in this way corresponds to a change in the fixation state of the eye E. When the displacement of the characteristic part is equal to or greater than the predetermined threshold, the analysis unit 221 determines that fixation disparity has occurred. The displacement (displacement direction, displacement amount) at that time is sent to the main control unit 201.

  The displacement of the characteristic part is calculated as a displacement with respect to a predetermined reference frame, for example. The reference frame is, for example, the first frame acquired after the shooting conditions are set. Further, the reference frame may be updated as appropriate while performing infrared moving image observation.

  The main control unit 201 can reflect the displacement obtained by the analysis unit 221 in the light stimulus application control. This displacement represents the direction and amount of fixation disparity of the eye E. The main control unit 201 controls the lighting timing of a visible light source (one or more light sources that output light used as stimulation light among the red light source 131r, the green light source 131g, and the blue light source 131b) so as to cancel this displacement. . That is, the main control unit 201 converts a spatial position shift called fixation disparity into a temporal position shift called stimulus timing change. The relationship between the spatial position and the temporal position is apparent from FIGS. 5A and 5B and their descriptions.

  Similarly, the main control unit 201 can reflect the displacement obtained by the analysis unit 221 in the fixation target presentation control. For example, the main control unit 201 turns on a visible light source (one or more light sources that output light used as fixation light among the red light source 131r, the green light source 131g, and the blue light source 131b) so as to cancel this displacement. Can be controlled.

  The inspection data recording unit 203 can record information based on the displacement obtained by the analysis unit 221. For example, the inspection data recording unit 203 responds to information indicating that fixation disparity has occurred during visual field inspection, information indicating an application position of a light stimulus when fixation disparity occurs, and fixation disparity. Information indicating that the application position of the light stimulus has been corrected, information indicating a time-series change in the fixation direction during the visual field inspection, and the like can be recorded. These pieces of information are recorded in association with the visual field map. Alternatively, this information is written in the view map.

<Action and effect>
Several examples of actions and effects that can be provided by the ophthalmologic photographing apparatus according to the embodiment will be described below.

  The ophthalmologic photographing apparatus according to the embodiment includes a scanning optical system, a control unit, and an image forming unit. The scanning optical system scans the fundus of the eye to be examined with light output from a light source unit including at least a visible light source, and receives light returned from the fundus at a light receiving unit. The SLO optical system 130 of the above embodiment corresponds to a scanning optical system. The SLO light source 131 corresponds to a light source unit. Each of the red light source 131r, the green light source 131g, and the blue light source 131b corresponds to a visible light source. The detector 135 corresponds to a light receiving unit. The control unit controls the scanning optical system. The main control unit 201 in the above embodiment corresponds to a control unit. The image forming unit forms a fundus image based on a signal from the light receiving unit. The SLO image forming unit 211 in the above embodiment corresponds to an image forming unit.

  Further, the control unit executes the first control and the second control. In the first control, the control unit controls the scanning optical system so as to project visible light output from the visible light source onto the fundus as fixation light for fixing the eye to be examined. That is, the first control is control for projecting the fixation target on the fundus. On the other hand, in the second control, the control unit controls the scanning optical system so as to project visible light output from the visible light source as stimulation light for visual field inspection onto the fundus. That is, the second control is a control for applying a light stimulus in the visual field examination to the fundus.

  According to such a configuration, it is possible to project a fixation target using visible light output from a visible light source for photographing and apply a light stimulus. That is, in a conventional ophthalmologic photographing apparatus, an element for projecting stimulus light and an element for presenting a fixation target are provided separately from an element for imaging the fundus (for example, an SLO / OCT system). However, in the ophthalmologic photographing apparatus according to the embodiment, it is possible to project stimulation light and present a fixation target using an element for imaging the fundus. Therefore, according to the embodiment, it is possible to reduce the size and simplification of the ophthalmologic photographing apparatus capable of performing the visual field inspection.

  When the light source unit includes only one visible light source, both the fixation target projection and the light stimulus application are performed using the same visible light source. On the other hand, when the light source unit includes two or more visible light sources, both the fixation target projection and the light stimulus application are performed using the same visible light source, or the fixation target projection and the light stimulus application. It is possible to apply a configuration in which these are performed using different visible light sources. Alternatively, when at least one of the fixation target projection and the light stimulus application is performed by using two or more visible light sources, the visible light source group used for the fixation target projection and the visible stimulus application. It may be completely different from the group of light sources, part of them may match, or all of them may match. Moreover, the structure which can change the visible light source used for projection of a fixation target, and the structure which can change the visible light source used for application of a light stimulus are also applicable. When two or more visible light sources are included, light of various colors can be applied to the eye to be examined by changing the ratio of the amount of emitted light. For example, when the infrared light source 131a, the red light source 131r, and the green light source 131g are included as described above, these light emission amounts can be changed independently of each other. According to the embodiment configured as described above, it is possible to perform a visual field inspection, a color vision abnormality test, a color vision experiment, and the like.

  The ophthalmologic imaging apparatus according to the embodiment may include a first recording unit for recording the result of the visual field inspection. The first recording unit is configured to record the position of the stimulation light projected by the second control in association with the content of the subject's reaction to the stimulation light. The inspection data recording unit 203 in the above embodiment corresponds to a first recording unit.

  In the embodiment, the control unit can execute the first control and the second control in a coordinated manner.

  According to such a configuration, it is possible to perform visual field inspection (application of light stimulus) using the scanning optical system while projecting the fixation target using the scanning optical system.

  In the embodiment, the control unit can repeatedly execute the first control and the second control.

  According to such a configuration, it is possible to apply a plurality of light stimuli while continuously fixing the eye to be examined.

  In the embodiment, the control unit sequentially projects the stimulation light to two or more different stimulation positions while repeatedly performing the first control so as to repeatedly project the fixation light corresponding to the predetermined fixation position onto the fundus. As described above, the second control can be repeatedly executed.

  According to such a configuration, two or more different positions can be inspected while fixing the eye to be examined in the same direction.

  In the embodiment, the light source unit may further include an infrared light source. The infrared light source 131a of the above embodiment corresponds to an infrared light source. The scanning optical system can scan the fundus with the infrared light output from the infrared light source, and can receive the return light of the infrared light from the fundus at the light receiving unit. Furthermore, the image forming unit can form an image of the fundus based on a signal from the light receiving unit that has received the return light of the infrared light.

  According to such a configuration, an infrared image of the fundus can be acquired.

  In the embodiment, the scanning optical system can repeatedly receive the return light of the infrared light from the fundus at the light receiving unit while repeatedly performing scanning with the infrared light output from the infrared light source. Furthermore, the image forming unit can repeatedly form fundus images based on signals sequentially output from the light receiving unit.

  According to such a configuration, infrared moving image observation of the fundus can be performed.

  The ophthalmologic photographing apparatus according to the embodiment may include an analysis unit that analyzes an image repeatedly formed by the image forming unit and obtains fundus displacement. The analysis unit 221 in the above embodiment corresponds to an analysis unit. Furthermore, the control unit can execute the second control according to the displacement obtained by the analysis unit.

  According to such a configuration, it is possible to correct in real time the position to which the light stimulus is applied while monitoring the occurrence, direction and amount of fixation disparity of the eye to be examined.

  The ophthalmologic imaging apparatus according to the embodiment may further include a second recording unit that records information based on the displacement obtained by the analysis unit. The inspection data recording unit 203 in the above embodiment corresponds to a second recording unit.

  According to such a configuration, information on fixation disparity of the eye to be examined can be recorded (for example, along with the result of visual field inspection).

  In the embodiment, the scanning optical system can scan the fundus with the visible light output from the visible light source, and receive the return light of the visible light from the fundus with the light receiving unit. The image forming unit can form an image of the fundus based on a signal from the light receiving unit that has received the return light of the visible light.

  According to such a configuration, at least one of the fixation target projection and the light stimulus application and the visible fundus photographing can be performed using the same visible light source (group).

  The ophthalmologic photographing apparatus according to the embodiment may include an optical unit for changing the size of the scanning range by the scanning optical system. The objective lens units 110A and 110B in the above embodiment correspond to optical units.

  According to such a configuration, the size of the scanning range can be changed. For example, in the above embodiment, the wide-angle shooting mode and the high-magnification shooting mode can be selectively used.

  The embodiment described above is merely an example for carrying out the present invention. A person who intends to implement the present invention can make arbitrary modifications, omissions, additions and the like within the scope of the present invention.

DESCRIPTION OF SYMBOLS 100 Optical system 110A, 110B Objective lens unit 130 SLO optical system 131 SLO light source 135 Detector 136 Optical scanner 201 Main control part 203 Inspection data recording part 211 SLO image formation part 221 Analysis part

Claims (11)

A scanning optical system that scans the fundus of the eye to be inspected with light output from a light source unit including at least a visible light source, and receives light returned from the fundus at a light receiving unit;
A control unit for controlling the scanning optical system;
An image forming unit that forms an image of the fundus based on a signal from the light receiving unit,
The control unit controls the scanning optical system so as to project visible light output from the visible light source onto the fundus as fixation light for fixing the eye to be inspected, and visual field inspection. And a second control for controlling the scanning optical system so as to project the visible light output from the visible light source onto the fundus as stimulation light for the purpose. The first recording unit that records the position of the stimulation light projected by the second control and the content of the subject's reaction to the stimulation light in association with each other. Ophthalmic photography device. The ophthalmologic photographing apparatus according to claim 1, wherein the control unit executes the first control and the second control in a coordinated manner. The ophthalmologic photographing apparatus according to claim 3, wherein the control unit repeatedly executes the first control and the second control. The control unit sequentially executes the first control so as to repeatedly project fixation light corresponding to a predetermined fixation position onto the fundus, and sequentially project stimulation light to two or more different stimulation positions. The ophthalmic imaging apparatus according to claim 4, wherein the second control is repeatedly executed. The light source unit further includes an infrared light source,
The scanning optical system scans the fundus with infrared light output from the infrared light source, and receives the return light of the infrared light from the fundus at the light receiving unit,
The ophthalmologic imaging according to claim 1, wherein the image forming unit forms an image of the fundus oculi based on a signal from the light receiving unit that has received the return light of the infrared light. apparatus. The scanning optical system repeatedly performs scanning with infrared light output from the infrared light source, and repeatedly receives the return light of the infrared light from the fundus at the light receiving unit,
The ophthalmologic photographing apparatus according to claim 6, wherein the image forming unit repeatedly forms the fundus image based on signals sequentially output from the light receiving unit. An analysis unit for analyzing the image repeatedly formed by the image forming unit and obtaining the displacement of the fundus;
The ophthalmologic photographing apparatus according to claim 7, wherein the control unit executes the second control in accordance with the displacement obtained by the analysis unit. The ophthalmologic photographing apparatus according to claim 8, further comprising a second recording unit that records information based on the displacement obtained by the analyzing unit. The scanning optical system scans the fundus with visible light output from the visible light source, and receives the return light of the visible light from the fundus at the light receiving unit,
The ophthalmologic photographing apparatus according to claim 1, wherein the image forming unit forms an image of the fundus based on a signal from the light receiving unit that has received the return light of the visible light. . The ophthalmologic photographing apparatus according to claim 1, further comprising an optical unit for changing a size of a scanning range by the scanning optical system.