JP7348334B2 - Ophthalmology imaging device - Google Patents

Description

The present invention relates to an ophthalmological imaging device.

Image diagnosis plays an important role in the field of ophthalmology, and in recent years scanning laser ophthalmoscopy (SLO) and optical coherence tomography have been increasingly utilized. SLO is a device that forms an image by scanning the fundus of the eye 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 technology called optical coherence tomography (OCT), which forms cross-sectional images, three-dimensional images, and functional images by scanning two-dimensional and three-dimensional areas of the fundus. do. Optical coherence tomography is also used to image the cornea and the like.

One of the ophthalmological examinations is a visual field test. Visual field testing is a test that measures the range and sensitivity of the visual field based on the subject's response to stimulating light projected onto various positions on the fundus of the eye, and is used to evaluate the progression of glaucoma. Patent Document 1 discloses a confocal imaging device that can perform a visual field test. This confocal imaging device includes an SLO/OCT system and a display. The display displays a bright spot used as stimulation light and a fixation target for causing the subject's eye to fixate. SLO/OCT systems perform SLO repeatedly during examinations using stimulating light. The confocal imaging device detects the movement of the subject's eye by comparing a series of SLO images acquired by the SLO/OCT system, and creates a visual field map accordingly.

In this way, conventional ophthalmological imaging devices capable of performing visual field tests include elements for projecting stimulating light (for example, a display) in addition to elements for imaging the fundus (for example, an SLO/OCT system). ) and an element (for example, a display) for presenting a fixation target. This has led to problems such as increased size and complexity of the device.

US Patent No. 7,690,791

An object of the present invention is to miniaturize and simplify an ophthalmological photographing apparatus capable of performing a visual field test.

The ophthalmologic imaging device according to the embodiment includes a scanning optical system, a control section, an image forming section, and an analysis section. The scanning optical system includes a light source unit containing a single visible light source and infrared light, and an optical scanner, and scans the eye to be examined by deflecting the light output from the single visible light source or infrared light source with the optical scanner. The fundus of the eye is scanned, and the light receiving unit receives the light returned from the fundus. The control unit controls the scanning optical system. The image forming section forms an image of the fundus based on a signal from a light receiving section that receives return light from the fundus of light output from a single visible light source or infrared light source. The analysis section analyzes the image formed by the image forming section. Furthermore, the control unit includes a first control unit that controls the single visible light source and the optical scanner to project visible light output from the single visible light source onto the fundus of the eye as fixation light for fixating the subject's eye. and a second control for controlling the single visible light source and the optical scanner so as to project visible light outputted from the single visible light source onto the fundus of the eye as stimulation light for visual field testing. In addition, the scanning optical system repeatedly performs scanning using the 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 section, and the image forming section receives the returned light from the fundus. The analysis unit repeatedly forms images of the fundus based on signals sequentially output from the image forming unit, the analysis unit analyzes the images repeatedly formed by the image forming unit to determine the displacement of the fundus, and the control unit uses While causing the scanning optical system to repeatedly scan, the lighting timing of the single visible light source in the first control and/or the lighting timing of the single visible light source in the second control is determined based on the displacement determined by the analysis unit. Control is performed in synchronization with repeated scanning by infrared light. The control unit causes the display device to display a composite image of the fundus image formed by the image forming unit and a visual field map based on a visual field test using stimulating light output from a single visible light source. The control unit aligns the image of the fundus with the visual field map based on the fixation position when scanning the fundus with the scanning optical system and the fixation position when performing the visual field test.

According to the embodiment, it is possible to downsize and simplify an ophthalmological photographing apparatus capable of performing a visual field test.

1 is a schematic diagram showing an example of the configuration of an ophthalmologic photographing apparatus according to an embodiment. 1 is a schematic diagram showing an example of the configuration of an ophthalmologic photographing apparatus according to an embodiment. 1 is a schematic diagram showing an example of the configuration of an ophthalmologic photographing apparatus according to an embodiment. 1 is a schematic diagram showing an example of the configuration of an ophthalmologic photographing apparatus according to an embodiment. FIG. 2 is a schematic diagram for explaining an example of the operation of the ophthalmologic photographing apparatus according to the embodiment. FIG. 2 is a schematic diagram for explaining an example of the operation of the ophthalmologic photographing apparatus according to the embodiment. FIG. 2 is a schematic diagram for explaining an example of the operation of the ophthalmologic photographing apparatus according to the embodiment. FIG. 2 is a schematic diagram for explaining an example of the operation of the ophthalmologic photographing apparatus according to the embodiment. 3 is a flowchart illustrating an example of the operation of the ophthalmologic imaging apparatus according to the embodiment. FIG. 2 is a schematic diagram for explaining an example of the operation of the ophthalmologic photographing apparatus according to the embodiment. FIG. 2 is a schematic diagram for explaining an example of the operation of the ophthalmologic photographing apparatus according to the embodiment. FIG. 2 is a schematic diagram showing an example of the configuration of an ophthalmologic imaging device according to another embodiment. FIG. 2 is a schematic diagram showing an example of the configuration of an ophthalmologic imaging device according to another embodiment.

Exemplary embodiments of the ophthalmological imaging device are described below. Contents of cited documents and known techniques can be incorporated into the embodiments.

The ophthalmologic imaging device according to the embodiment scans the posterior segment of the eye with a light beam to obtain a distribution of predetermined data (eg, an image, a layer thickness distribution, a lesion distribution). Examples of such ophthalmologic imaging devices include SLO and optical coherence tomography. Hereinafter, an ophthalmologic imaging apparatus that combines an SLO and an optical coherence tomography will be described as an example. The ophthalmologic imaging device according to the embodiment is used not only for imaging the fundus but also for visual field testing, and for example, uses light (visible light) for SLO to present a fixation target and apply optical stimulation. 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-back direction (depth direction) is the Z direction. The X, Y, and Z directions define a three-dimensional orthogonal coordinate system.

<Optical system 100>
Examples of the optical system of an ophthalmological imaging device are shown in FIGS. 1 to 3. The ophthalmologic imaging device can operate in multiple imaging modes. For example, there are a wide-angle shooting mode and a high-magnification shooting mode as operation modes related to the size of the shooting range (angle of view, magnification). Switching of the angle of view is realized, for example, by selectively using two or more objective lenses having different refractive powers. Alternatively, the 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 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 an ophthalmologic imaging apparatus in high-magnification imaging mode. The symbol P in FIGS. 1 and 3 indicates a position optically conjugate with the fundus Ef (fundus conjugate position), and the symbol Q indicates a position optically conjugate with the pupil of the eye E (pupil conjugate position). .

The optical system 100 scans the fundus Ef using a light beam to collect data. 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 returned light of the projected light beam through the objective lens system 110. include. An image of the fundus Ef is formed based on the output from the light receiving system (that is, data collected by the data collection unit). Optical system 100 includes an SLO optical system 130 and an OCT optical system 140. SLO optical system 130 includes an SLO projection system and an SLO light receiving system. OCT optical system 140 includes an OCT projection system and an OCT light receiving system.

The ophthalmologic imaging apparatus is provided with an anterior segment imaging system 120 for observing and imaging the anterior segment of the eye. The optical system 100, objective lens system 110, and anterior segment imaging system 120 are moved in the X direction, Y direction, and 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 imaging mode, and the objective lens unit according to the selected imaging mode is selectively used. In this embodiment, as shown in FIG. 2, an objective lens unit 110A for wide-angle photography mode (for example, 100 degree angle of view) and an objective lens unit 110B for high magnification photography mode (for example, 50 degree angle of view) are provided. , are selectively arranged in the optical path of the optical system 100.

Objective lens system 110 includes a view angle changing mechanism 115 in addition to objective lens units 110A and 110B. The view angle changing mechanism 115 includes, for example, a known rotating mechanism or sliding mechanism, and selectively (mutually exclusively) arranges the objective lens units 110A and 110B in the optical path. The view angle changing mechanism 115 arranges the objective lens unit 110A (110B) on 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 view angle changing mechanism 115 may include a configuration for manually moving the objective lens units 110A and 110B. In this case, it is possible to provide a type detection section that detects the type of the objective lens unit arranged in the optical path, to specify the photographing mode from the detection result, and to execute control according to the identification result. The view angle changing mechanism 115 may include a configuration for electrically (or even automatically) moving the objective lens units 110A and 110B. In this case, the control unit 200, which will be described later, sends a control signal to the view angle changing mechanism 115 for arranging an objective lens unit corresponding to the selected photographing mode on the optical path.

The objective lens unit 110A for wide-angle photography mode includes lenses 111A and 112A, a dichroic mirror DM1A, and a concave lens 113A. Dichroic mirror DM1A couples the optical path of optical system 100 and the optical path of anterior 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 of the eye. A fundus conjugate position P is arranged between the dichroic mirror DM1A and the concave lens 113A.

The objective lens unit 110B for high-magnification photography mode includes a lens 111B and a dichroic mirror DM1B. Dichroic mirror DM1B has the same effect as dichroic mirror DM1A.

Dichroic mirror DM1A and dichroic mirror DM1B are arranged at (almost) the same position on the optical path of optical system 100. This eliminates the need to adjust the position and orientation of the anterior segment imaging system 120 when switching the imaging mode.

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, dichroic mirrors DM1A and DM1B may be the same member. That is, a configuration can be applied in which objective lens unit 110A including only lenses 111A and 112A and concave lens 113A and objective lens unit 110B including only lens 111B are selectively used.

Objective lens system 110 can be moved along 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, objective lens units for high-magnification photography mode, medium-magnification photography mode, and low-magnification photography mode, and an angle-of-view changing mechanism that selectively arranges these on the optical path may be provided.

The following will mainly describe the state in which the objective lens unit 110A is placed in the optical path. Descriptions of the same or similar matters in the state where the objective lens unit 110B is arranged will be omitted unless specified otherwise.

<Anterior segment 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. Beam splitter BS1 couples the optical path of the anterior segment illumination light and the optical path of its return light.

The anterior segment illumination light source 121 includes an infrared light source such as an infrared LED. The anterior eye illumination light emitted by the anterior eye illumination light source 121 is refracted by the lens 122, reflected by the beam splitter BS1 toward the dichroic mirror DM1A, and reflected toward the eye E by the dichroic mirror DM1A. Return light of the anterior segment illumination light from the subject's eye E is reflected by the dichroic mirror DM1A, passes through the beam splitter BS1, and is focused by the imaging lens 124 onto the anterior segment imaging camera 123 (detection surface of the imaging device). be done. The detection surface of the image sensor is arranged at the pupil conjugate position Q (or in the vicinity thereof). 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 an exemplary embodiment, at least a portion of SLO optics 130 is telecentric and at least a portion of OCT optics 140 is telecentric, and the optical paths of the telecentric optics are combined by dichroic mirror DM2. Ru. According to this example, even if the focal position of the optical system 100 is changed by moving the objective lens system 110, the aberration of the pupil (for example, the exit pupil caused by the objective lens system 110) does not increase, which facilitates 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 diaphragm 134, a detector 135, an optical scanner 136, and a lens 137. Beam splitter BS2 combines the optical path of the SLO light projected onto the eye E and the optical path of the returned light.

SLO light source 131 includes a laser diode, a superluminescent diode, a laser-driven light source, and the like. The SLO light source 131 outputs light with a wavelength usable for SLO. SLO light source 131 includes at least a visible light source. The SLO light source 131 may be configured to be able to selectively output light in different wavelength bands. Further, it may be configured such that two or more lights having different wavelength bands can 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 arranged at a 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, polygon mirror, MEMS mirror, etc.). The reflective surface of the optical scanner 136Y is arranged at the pupil conjugate position Q (or in the vicinity thereof).

The aperture formed in the confocal diaphragm 134 is arranged at the fundus conjugate position P (or in the vicinity thereof). 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 collimated 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. , are projected onto the fundus Ef via the objective lens system 110. The return light of the SLO light projected onto the fundus 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 condensed by the condensing lens 133, and is focused by the confocal diaphragm 134. The light passes through the aperture and is detected by the detector 135.

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

Focusing lens 141 is moved along the optical axis of 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 moving the objective lens system 110, the focusing state of the OCT optical system 140 can be finely adjusted by moving 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 collimating 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 beam, and focuses the return light of the measurement light from the fundus Ef toward the fiber end c3. Shine.

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

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

The reference light LR exits from the fiber output end c1 through the optical fiber f2, is made into a parallel light beam by the collimating lens 156, is turned back by the reference prism 154, is made into a convergent light beam by the collimator lens 157, and enters the fiber input end c2, It is led 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 conventional case. 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 made into a parallel light beam by the collimator lens 143, passes through the optical scanner 142 and the focusing lens 141, and is sent to the dichroic mirror DM2. It is reflected, refracted by the objective lens system 110, and projected onto the fundus Ef. The measurement light LS is reflected and scattered at various depth positions of the fundus Ef. The return light of the measurement light LS including the backscattered light travels in the opposite direction along 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 that has entered through the optical fiber f5 and the reference light LR that has entered through the optical fiber f3. FIG. 1 and the like represent the case of swept source OCT. The fiber coupler 153 branches the interference light at a predetermined branching ratio (for example, 1:1) to generate a pair of interference lights LC. A pair of interference lights LC are detected by a detector 155 (balanced photodiode). Note that in the case of spectral domain OCT, the detector 155 (spectroscope) separates the interference light generated by the fiber coupler 153 into a plurality of wavelength components and detects them.

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

<Processing system>
FIG. 4 shows an example of the configuration of the processing system of the ophthalmologic imaging apparatus according to the embodiment. The processing system includes a processor for performing various data processing (signal processing, image processing, calculation, control, storage, etc.).

Note that "processor" refers to, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an ASIC (Application Specific Integrated Circuit), a programmable logic device (for example, SPLD (Simple Programmable Logic Device), CPLD (Complex Programmable Logic Device), FPGA (Field Programmable Gate Array), and other circuits. The processor realizes the functions according to the embodiment by, for example, reading and executing a program stored in a storage circuit or a storage device.

<Control unit 200>
The control section 200 includes a configuration for controlling each section of the ophthalmologic imaging apparatus. The control section 200 includes a main control section 201, a storage section 202, and an examination data recording section 203. The functions of the main control section 201 and the inspection data recording section 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 performed by the ophthalmologic imaging device is realized through cooperation between hardware resources (such as a processor) and software (such as a computer program). Furthermore, actuators are provided in at least some of the various mechanisms provided in the ophthalmologic imaging apparatus, and the main control unit 201 sends control signals to the actuators.

<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 to place one of the objective lens units 110A and 110B on the optical path, and controls the objective lens system 110 along the optical axis O. It is possible to control a moving mechanism (not shown) for moving the object.

As an example of control regarding the SLO optical system 130, the main control unit 201 can control the SLO light source 131, the optical scanner 136, and the detector 135. Control of the SLO light source 131 includes turning on, turning off, adjusting light amount, adjusting aperture, and the like. Control of the optical scanner 136 includes control of the scanning position, control of the scanning range, control of the scanning pattern, control of the scanning speed, and the like. Control of the detector 135 includes exposure adjustment, gain adjustment, detection rate adjustment, etc. of the detection element.

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

As an example of control regarding the anterior eye imaging system 120, the main control unit 201 can control the anterior eye illumination light source 121, the anterior eye imaging camera 123, and the like. Control of the anterior segment illumination light source 121 includes turning on, turning off, adjusting the amount of light, adjusting the aperture, and the like. Control of the anterior segment imaging camera 123 includes exposure adjustment, gain adjustment, imaging rate adjustment, etc. of the image sensor.

An example of control regarding the optical system 100 includes control of the optical system moving mechanism 100A for moving the optical system 100 in the X direction, Y direction, and Z direction.

When performing SLO photography, 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 the photographing control as described above and uses visible light (different from the visible light for photographing) only at a timing corresponding to a predetermined fixation position (fixation timing). The SLO light source 131 is controlled to output visible light for visual fixation. At the fixation timing, the output of the visible light for imaging may be stopped and the visible light for fixation may be output. Alternatively, both visible light for photographing and 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 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 turning on (flashing) the OCT light source 151 at a predetermined timing.

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

Examples of operations for visual field testing are shown in FIGS. 5A and 5B. FIG. 5A shows a fixation target and stimulation light projected onto the fundus Ef. FIG. 5B is a timing chart showing control for projecting the fixation target and stimulation light onto the fundus Ef. In FIG. 5B, the horizontal axis is the time axis.

In the example shown in FIG. 5A, a raster scan consisting of a plurality (M) of parallel line scans L _m (m=1, 2, . . . , M) is applied. Each line scan L _m includes a plurality of scan points (light beam irradiation points) arranged in a straight line. The main control unit 201 causes the optical scanner 136 to repeatedly perform operations corresponding to this raster scan.

Furthermore, the main control unit 201 turns on the SLO light source 131 (visible light source) at a preset fixation timing. Fixation timing is synchronized to the raster scan. In this example, the fixation timing includes at least the timing at which the optical scanner 136 is placed at the position (orientation) corresponding to the nj-th scan point in the mj-th line scan L _mj . When the fixation timing includes only this timing, the fixation target T(mj, nj) as a bright spot is projected onto the fundus 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 Ef. As stimulation light projection control, the main control unit 201 turns on the SLO light source 131 (visible light source) at a preset stimulation timing. Stimulus timing is synchronized to the raster scan. In this example, the stimulation timing is the timing at which the optical scanner 136 is placed at a position (orientation) corresponding to the ni-th scan point in the mi-th line scan _Lmi . Thereby, the stimulation light S _i (mi, ni) is projected onto the fundus Ef.

Note that the fixation timing and stimulation timing are not limited to timing corresponding to a single scan point. For example, the SLO light source 131 (visible light source) can be turned on at timings corresponding to each of a plurality of spatially adjacent scan points. As an example, the SLO light source 131 (visible light source) can be turned on at timings corresponding to each of a plurality of scan points included in a two-dimensional area such as a disk-shaped area or a cross-shaped area. This two-dimensional region is typically a connected region, more typically a simply 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 centered 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 nj-th 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 mj-th 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 applicable scan points in each applicable 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 applicable line scans and the number of applicable scan points on line scan L _mj can be set so that the vertical size and horizontal size of the cross-shaped fixation target are equal ( However, this is not limited to). Even when a fixation target of another two-dimensional shape is presented, it is possible to similarly set a group of scan points corresponding to the fixation timing.

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

Further, the main control unit 201 repeatedly executes the same raster scan and the control for projecting the fixation target at the first fixation position, sequentially projects the stimulation light to a predetermined number of positions, and terminates the process. Afterwards, the fixation position can be switched, and the stimulation light can be sequentially projected onto a predetermined number of positions while repeating the same raster scan and control for projecting the fixation target to the second fixation position. Such control can be applied sequentially to a plurality of fixation positions. The plurality of positions serving as projection targets of the stimulation light and the plurality of fixation positions including the first fixation position and the second fixation position are set in advance as a protocol for the visual field test. It is also possible to manually set or change the fixation position.

Instead of controlling the raster scan and moving the fixation position alternately in this way, it is also possible to apply control to repeatedly perform the raster scan while moving the fixation position continuously or stepwise. .

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. Note that when two or more frames are combined to create one frame, the combined frame may be a single frame _Fk .

One operation of the optical scanner 136X (X scanner) corresponds to one line scan _Lm . Further, one operation of the optical scanner 136Y (Y scanner) corresponds to movement of the light beam projection position from line scan _L1 to line scan _LM in the direction orthogonal to line scan _Lm . The main control unit 201 realizes the operation of the optical scanner 136 corresponding to the raster scan shown in FIG. 5A by controlling the optical scanner 136X and the optical scanner 136Y in a coordinated manner. Further, the main control unit 201 repeatedly executes such cooperative control of the optical scanner 136X and the optical scanner 136Y. As a result, a plurality of frames F ₁ , F ₂ , . . . are sequentially acquired.

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

There is a possibility that the stimulation light will not be projected to the target position due to the effects of eye movement or blinking. To deal with such a situation, the occurrence of eye movement or blinking can be detected by analyzing frames F _k that are sequentially acquired. Eye movement detection is performed, for example, based on changes over time in the positions of characteristic parts (optic disc, macula, blood vessels, lesions, scars from laser treatment, etc.) in frame _Fk . Blink detection is performed, for example, by determining whether or not the fundus Ef (for example, a characteristic region) is depicted in the frame _Fk , or by referring to a predetermined image quality parameter (for example, contrast). If an abnormality such as eye movement or blinking is detected, the main control unit 201 can project the stimulation light to the target position again. At this time, the stimulation light may be re-projected after detecting that the abnormality has been resolved. Alternatively, the fact that an abnormality has been detected may be added to the visual field test result data.

<Storage unit 202>
The storage unit 202 stores information, data, programs, etc. used by the ophthalmological imaging device. The storage unit 202 also acquires data (SLO images, OCT images, anterior segment images, etc.) acquired by the ophthalmologic imaging device.

<Inspection data recording unit 203>
In the visual field test, stimulating light is projected onto the fundus Ef, and the content of the subject's reaction to it (whether or not the subject has recognized the stimulating light) is recorded. Such processing is sequentially performed on a plurality of positions on the fundus Ef. The test data recording unit 203 stores sets of stimulation light projection positions and reaction contents. Thereby, the distribution of reaction contents at a plurality of positions on the fundus Ef, that is, the distribution of visual field range and the distribution of visual field sensitivity can be obtained.

The projection position of the stimulation light is obtained from the stimulation 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). Further, the reaction of the subject is input using, for example, the UI section 230. Alternatively, if the ophthalmologic imaging apparatus is provided with a function of detecting retinal reactions or changes in biological signals, the content of the subject's reaction can be obtained from the detection results. This function is realized using, for example, OCT (polarized OCT, etc.), time-series analysis of SLO images, fluorescence photography, and the like.

FIG. 6A shows a plurality of test positions (stimulation positions) in a visual field test of the eye E to be examined. 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), . . . , _SN (mN, nN) arranged in a grid are set.

FIG. 6B shows an example of a visual field map based on the results of a visual field test performed for a plurality of stimulation positions S _i (mi, ni) (i=1, 2, . . . , N). The visual field map in this example is a stimulus position where there was no response to the light stimulus (that is, a stimulus position where the subject could not recognize the stimulus light. This is called a scotoma) Ur (r = 1, 2, . . . ) represents the distribution of Note that the visual field map is not limited to this. For example, it is possible to create a visual field map that represents the distribution of stimulus positions where there was a response to a light stimulus, or a visual field map in which the representation mode of the stimulus positions differs depending on whether there is a response to the light stimulus. Furthermore, when stimulation conditions such as the intensity of optical stimulation (the amount of light beam), the stimulation time, and the number of times of stimulation are variable, a visual field map representing the distribution of the perceivable limit amount of light (sensitivity) can be created.

<Image forming section 210>
The image forming unit 210 forms an image of the fundus Ef based on the data collected by the optical system 100. Since the ophthalmologic imaging apparatus 1 is capable of performing both SLO and OCT, the image forming section 210 includes an SLO image forming section 211 and an OCT image forming section 212.

The SLO image forming unit 211 forms an SLO image based on 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, similar to the conventional SLO. do.

The OCT image forming unit 212 forms an OCT image based on 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. As in the conventional case, the OCT image forming unit 212 generates a spectral distribution from the output from the detector 155 for each series of wavelength scans (for each A line), and performs Fourier transform or the like on this. Thereby, a reflection intensity profile at each A-line is obtained. Furthermore, 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 (three-dimensional data set such as stack data or volume data) based on a plurality of B-scan images. Further, the OCT image forming unit 212 can form a display image by rendering the 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 performs various data processing. An example of data processing is processing on 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 section 230>
The user interface (UI) unit 230 has a function for exchanging information between the user and the ophthalmologic imaging device. 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 operating device includes various hardware keys and/or software keys. The control unit 200 receives the operation details of the operating device, and outputs control signals corresponding to the operation details to each unit. It is possible to integrally configure at least part of the operating device and at least part of the display device. A touch panel display is one example.

<Operation>
An example of the operation of the ophthalmologic imaging 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 controller 201 or the user places the objective lens unit 110A on the optical path.

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

(S3: Alignment)
The main control unit 201 performs alignment with reference to the anterior segment image obtained by the anterior segment imaging system 120. Alignment includes, for example, including alignment. The alignment is automatic alignment or manual alignment performed using a known method. After alignment is completed, focusing, OCT optical path length adjustment, polarization state adjustment, etc. may be performed.

(S4: Photographing the fundus)
After the alignment is completed, the main control unit 201 collects data of the fundus Ef using the SLO optical system 130 and the OCT optical system 140. The SLO image forming unit 211 forms an SLO image based on data collected by the SLO optical system 130. The OCT image forming unit 212 forms an OCT image based on 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 of a different wavelength or a different amount of light.

Note that the timing of photographing the fundus Ef is not limited to the timing of this example. For example, it is possible to perform fundus photography after a visual field test, or to perform fundus photography during a visual field test. Furthermore, fundus photography may be continuously performed during at least part of the period when the visual field test is being performed and/or at least part of the period when the visual field test is not being performed. Continuous fundus photography may be, for example, infrared video observation using the SLO optical system 130. Note that an ophthalmological imaging device that can perform infrared video observation and visual field testing in parallel will be described later.

(S5: Visual field test)
In this example, a visual field test is performed after fundus photography is completed. In the visual field test, the main control unit 201 controls the SLO optical system 130 to project the fixation target and project the stimulation light at predetermined timings. The test data recording unit 203 accumulates sets of stimulation light projection positions and reaction contents to create a visual field map.

(S6: Display test results)
The main control unit 201 causes the UI unit 230 (display device) to display the SLO image and 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 overlay and display a visual field map on the SLO image. The alignment between the SLO image and the visual field map is performed, for example, based on the fixation position during the SLO scan and the fixation position during the visual field test. Note that it is also possible to display a composite image of a plane image formed from data (three-dimensional image) collected by OCT scanning of a three-dimensional region of the fundus Ef and a visual field map.

(S7: Do you want to conduct a detailed inspection?)
By observing the image displayed in step S6, the user can determine whether to change the angle of view and perform further photography. For example, if a wide range of screening is performed by observing SLO images, OCT images, and visual field maps acquired in wide-angle imaging mode, and a region to be observed in more detail is found, it is possible to shift to high-magnification imaging of that region.

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

If detailed inspection is not performed (S7: No), the process ends (End). On the other hand, if a detailed inspection is to be performed (S7: Yes), the process moves to step S11.

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

(S12: Specify the inspection site)
The user or the ophthalmological imaging device specifies a region to be subjected to detailed examination. For example, the inspection site can be specified by specifying a desired position or range in the SLO image (composite image) displayed in step S6 using the UI section 230 (operation device). Further, the examination region can be specified so as to include the scotoma and characteristic regions of the fundus Ef (optic disc, macula, etc.) represented by the visual field map. When the composite image shown in FIG. 8A is obtained, for example, a range A1 including the scotoma Sc1, the optic disc, and the macula is designated as a target for high-magnification imaging.

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

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

(S15: Photographing the fundus)
An SLO image and an OCT image of the fundus Ef are acquired in the same manner as in step S4. The SLO image and OCT image are based on data collected by scanning range A1 shown in FIG. 8A, for example.

(S16: Visual field test)
A visual field test is performed in the same manner as step S5. This visual field test targets at least a portion of range A1.

(S17: Display test results)
The main control unit 201 causes the UI unit 230 (display device) to display the SLO image and 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. The symbol G2 represents (a part of) an SLO image obtained in high-magnification imaging mode. The code Sc2 represents the scotoma obtained in the visual field test in step S16. This dark spot Sc2 indicates the detailed position of the dark spot Sc1 obtained in the wide-angle shooting mode.

(S18: Do you want to test other parts?)
If other parts are not to be inspected in detail (S18: No), the process ends (End). On the other hand, if a detailed inspection of another part is to be performed (S18: Yes), the process returns to step S12. Detailed examination of other parts is performed, for example, when scotomas exist in separate positions. When all the detailed inspections of the desired parts are completed (S18: No), the process ends (End).

<Other embodiments>
A case will be described in which a visual field test is performed using an ophthalmologic photographing device that can output light beams in a plurality of wavelength bands. FIG. 9 shows an example of a part of the optical system of such an ophthalmological photographing apparatus. Note that unless otherwise specified, reference will be made to the drawings and descriptions of the above embodiments.

The optical system shown in FIG. 9 represents an SLO light source unit 131A applied in place of the SLO light source 131 and collimating lens 132 in FIGS. 1 and 3. Other parts may be the same as those 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 light beam in the (near) infrared band. The red light source 131r outputs a light beam in the red band. The green light source 131g outputs a light beam in the green band. 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 collimator 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 blue external light output from the blue light source 131b is converted into a parallel light beam by the collimating lens 132b.

The beam splitter BSr combines the red light that has been made into a parallel beam by the collimating lens 132r into the optical path of the infrared light that has been made into a parallel beam by the collimating lens 132a. The beam splitter BSg combines the green light, which has been made into a parallel beam by the collimating lens 132g, into the optical path of the infrared light, which has been made into a parallel beam by the collimating lens 132a. The beam splitter BSb combines the blue light, which has been made into a parallel beam by the collimating lens 132b, into the optical path of the infrared light, which has been made into a parallel beam by the collimating lens 132a. The three beam splitters BSr, BSg, and BSb combine the optical paths of four light beams with different wavelength bands. This combined optical path is guided to a beam splitter BS2.

FIG. 10 shows an example of the control system of the ophthalmologic imaging apparatus according to this embodiment. 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 synchronous circuit for synchronously controlling these light sources 131a, 131r, 131g, and 131b. This synchronization circuit may be configured to synchronize control of these light sources 131a, 131r, 131g, and 131b and control of optical scanner 136.

According to such an ophthalmological imaging device, 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, infrared video observation and Projection of the fixation target and application of optical stimulation can be performed in parallel.

Infrared video observation is performed, for example, as follows. The main control unit 201 repeatedly controls the optical scanner 136 corresponding to a predetermined scan pattern (raster scan, etc.) and controls the infrared light source 131a to output infrared light at predetermined time intervals. 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 video observation, the main control unit 201 executes control for projecting a fixation target and control for applying optical stimulation. The projection control of the fixation target and the application control of the optical stimulus are executed in the same manner as in the timing chart of FIG. 5B of the above embodiment, for example. That is, the main control unit 201 projects a fixation target onto the fundus Ef during a control period corresponding to each frame at a fixation timing synchronized with control for infrared video observation. Further, when the main control unit 201 or the user issues a trigger Trg for applying optical stimulation, the main control unit 201 projects stimulation light onto the fundus Ef at a stimulation timing corresponding to a preset application position.

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

The analysis unit 221 obtains the displacement of the fundus Ef by analyzing frames repeatedly formed by the image forming unit 210 (SLO image forming unit 211). This analysis process includes, for example, the process of analyzing the pixel values of a frame to find the position (coordinates in the frame) of a feature part (optic disc, blood vessel, diseased area, etc.), and the process of determining the position of a feature part between different frames. This includes processing for determining series changes.

The time-series displacement of the characteristic region identified in this manner corresponds to a change in the fixation state of the eye E to be examined. When the displacement of the characteristic region exceeds a predetermined threshold value, the analysis unit 221 determines that a fixation shift has occurred. The displacement at that time (displacement direction, displacement amount) is sent to the main control section 201.

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

The main control unit 201 can reflect the displacement determined by the analysis unit 221 in the application control of optical stimulation. This displacement represents the direction and amount of fixation shift of the eye E to be examined. The main control unit 201 controls the lighting timing of the visible light source (one or more of the red light source 131r, green light source 131g, and blue light source 131b that outputs light used as stimulation light) so as to cancel this displacement. . That is, the main control unit 201 converts a shift in spatial position, which is a fixation shift, into a shift in temporal position, which is a change in stimulation timing. The relationship between spatial and temporal positions is clear from FIGS. 5A and 5B and their description.

Similarly, the main control unit 201 can reflect the displacement determined by the analysis unit 221 in the display control of the fixation target. For example, the main control unit 201 controls the lighting timing of the visible light source (one or more of the red light source 131r, green light source 131g, and blue light source 131b that outputs light used as fixation light) so as to cancel this displacement. It is possible to control the

The inspection data recording unit 203 can record information based on the displacement determined by the analysis unit 221. For example, the test data recording unit 203 stores information indicating that a fixation shift occurred during the visual field test, information indicating the application position of optical stimulation when a fixation shift occurred, and information indicating that a fixation shift occurred during the visual field test. Information indicating that the application position of optical stimulation has been corrected, information indicating time-series changes in the fixation direction during the visual field test, etc. can be recorded. This information is recorded in association with the visual field map. Alternatively, this information is written into the field of view map.

<Action/Effect>
Some examples of actions and effects that can be provided by the ophthalmologic imaging apparatus according to the embodiments will be described below.

The ophthalmologic imaging device according to the embodiment includes a scanning optical system, a control section, and an image forming section. The scanning optical system scans the fundus of the eye to be examined using light output from a light source section including at least a visible light source, and receives return light from the fundus at a light receiving section. 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 section. 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 section. The control unit controls the scanning optical system. The main control section 201 in the above embodiment corresponds to a control section. The image forming section forms an image of the fundus based on the signal from the light receiving section. The SLO image forming section 211 in the above embodiment corresponds to an image forming section.

Furthermore, the control unit executes first control and second control. In the first control, the control unit controls the scanning optical system to project visible light output from the visible light source onto the fundus of the eye as fixation light for causing the subject's eye to fixate. That is, the first control is a control for projecting a fixation target onto the fundus of the eye. On the other hand, in the second control, the control unit controls the scanning optical system to project visible light output from the visible light source onto the fundus of the eye as stimulation light for visual field testing. That is, the second control is a control for applying optical stimulation to the fundus in a visual field test.

According to such a configuration, it is possible to project the fixation target using visible light output from the visible light source for photographing, and to apply optical stimulation. In other words, in a conventional ophthalmological imaging device, in addition to an element for imaging the fundus (for example, an SLO/OCT system), an element for projecting stimulating light and an element for presenting a fixation target are provided. However, in the ophthalmologic photographing apparatus according to the embodiment, it is possible to project stimulation light and present a fixation target using elements for imaging the fundus. Therefore, according to the embodiment, it is possible to downsize and simplify an ophthalmological photographing apparatus capable of performing a visual field test.

Note that when the light source section includes only one visible light source, both the projection of the fixation target and the application of optical stimulation are performed using the same visible light source. On the other hand, when the light source section includes two or more visible light sources, the same visible light source may be used for both projection of the fixation target and application of optical stimulation, or a configuration in which both projection of the fixation target and application of optical stimulation are performed. It is possible to apply a configuration in which the steps are performed using different visible light sources. Alternatively, if at least one of the projection of the fixation target and the application of optical stimulation is performed using two or more visible light sources, a group of visible light sources used for projecting the fixation target and a group of visible light sources used for application of optical stimulation may be used. The group of light sources may be completely different, some of them may be the same, or all of the light sources may be the same. Furthermore, a configuration in which the visible light source used to project the fixation target can be changed or a configuration in which the visible light source used in applying optical stimulation can be applied can also be applied. 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 their emitted light amounts. For example, when the infrared light source 131a, the red light source 131r, and the green light source 131g are included as described above, the amounts of light emitted by these light sources can be changed independently of each other. According to the embodiment configured in this way, it is possible to perform a color-based visual field test, a color blindness test, a color vision experiment, and the like.

The ophthalmologic imaging device according to the embodiment may include a first recording section for recording the results of the visual field test. The first recording unit is configured to associate and record the position of the stimulation light projected by the second control and the content of the subject's reaction to the stimulation light. The inspection data recording section 203 of the above embodiment corresponds to the first recording section.

In the embodiment, the control unit can perform the first control and the second control in conjunction.

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

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

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

In the embodiment, the control unit sequentially projects the stimulation light at two or more different stimulation positions while repeatedly executing the first control so as to repeatedly project the fixation light corresponding to a predetermined fixation position onto the fundus of the eye. The second control can be repeatedly executed as follows.

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

In embodiments, 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 of the eye with 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 section. Further, the image forming section can form an image of the fundus based on a signal from a light receiving section that has received the returned infrared light.

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

In the embodiment, the scanning optical system can repeatedly perform scanning using the infrared light output from the infrared light source and repeatedly receive the return light of the infrared light from the fundus at the light receiving section. Furthermore, the image forming section can repeatedly form images of the fundus based on signals sequentially output from the light receiving section.

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

The ophthalmologic imaging apparatus according to the embodiment may include an analysis section that analyzes images repeatedly formed by the image forming section to determine the displacement of the fundus. The analysis section 221 in the above embodiment corresponds to an analysis section. Further, the control section can execute the second control according to the displacement determined by the analysis section.

According to such a configuration, it is possible to correct the position to which optical stimulation is applied in real time while monitoring the occurrence, direction, and amount of fixation deviation of the subject's eye.

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

According to such a configuration, information regarding the fixation shift of the subject's eye can be recorded (for example, together with the results of the visual field test).

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

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

The ophthalmologic imaging 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 of the above embodiment correspond to an optical unit.

According to such a configuration, the size of the scanning range can be changed. For example, in the embodiment described above, it is possible to selectively use the wide-angle photography mode and the high-magnification photography mode.

The embodiment shown above is only an example for implementing this invention. Those who wish to implement this invention can make arbitrary modifications, omissions, additions, etc. within the scope of the gist of this invention.

100 Optical systems 110A, 110B Objective lens unit 130 SLO optical system 131 SLO light source 135 Detector 136 Optical scanner 201 Main control section 203 Inspection data recording section 211 SLO image forming section 221 Analysis section

Claims (8)

The method includes a light source unit including a single visible light source and an infrared light source, and a light scanner, and the fundus of the eye to be examined is scanned by deflecting the light output from the single visible light source or the infrared light source with the light scanner. a scanning optical system that scans and receives return light from the fundus at a light receiving section;
a control unit that controls the scanning optical system;
an image forming unit that forms an image of the fundus based on a signal from the light receiving unit that receives the return light of the light output from the single visible light source or the infrared light source;
an analysis section that analyzes the image formed by the image forming section;
The control unit controls the single visible light source and the optical scanner to project visible light output from the single visible light source onto the fundus of the eye as fixation light for fixating the eye to be examined. and a second control that controls the single visible light source and the optical scanner to project visible light output from the single visible light source onto the fundus as stimulation light for visual field testing. and run
The scanning optical system repeatedly performs scanning using the infrared light output from the infrared light source, and repeatedly receives return light of the infrared light from the fundus at the light receiving unit,
The image forming unit repeatedly forms images of the fundus based on signals sequentially output from the light receiving unit,
The analysis unit analyzes the images repeatedly formed by the image forming unit to determine the displacement of the fundus;
The control unit controls the lighting timing of the single visible light source in the second control based on the displacement determined by the analysis unit while causing the scanning optical system to repeatedly scan using the infrared light. Control is performed in synchronization with the repetitive scanning,
The control unit is based on the image of the fundus formed by the image forming unit and the visual field test using the stimulation light output from the single visible light source at a lighting timing synchronized with the repeated scanning. Display the composite image with the visual field map on the display device ,
The control unit is configured to control the image of the fundus and the visual field map based on a fixation position when the fundus is scanned by the scanning optical system and a fixation position when the visual field test is performed. Align the
An ophthalmological imaging device characterized by the following. The method includes a light source unit including a single visible light source and an infrared light source, and a light scanner, and the fundus of the eye to be examined is scanned by deflecting the light output from the single visible light source or the infrared light source with the light scanner. a scanning optical system that scans and receives return light from the fundus at a light receiving section;
a control unit that controls the scanning optical system;
an image forming unit that forms an image of the fundus based on a signal from the light receiving unit that receives the return light of the light output from the single visible light source or the infrared light source;
an analysis section that analyzes the image formed by the image forming section;
The control unit controls the single visible light source and the optical scanner to project visible light output from the single visible light source onto the fundus of the eye as fixation light for fixating the eye to be examined. and a second control that controls the single visible light source and the optical scanner to project visible light output from the single visible light source onto the fundus as stimulation light for visual field testing. and run
The scanning optical system repeatedly performs scanning using the infrared light output from the infrared light source, and repeatedly receives return light of the infrared light from the fundus at the light receiving unit,
The image forming unit repeatedly forms images of the fundus based on signals sequentially output from the light receiving unit,
The analysis unit analyzes the images repeatedly formed by the image forming unit to determine the displacement of the fundus;
The control unit controls the lighting timing of the single visible light source in the first control based on the displacement determined by the analysis unit while causing the scanning optical system to repeatedly scan using the infrared light. Control is performed in synchronization with the repetitive scanning,
The control unit displays, on a display device, a composite image of the fundus image formed by the image forming unit and a visual field map based on the visual field test using the stimulation light output from the single visible light source. display ,
The control unit is configured to control the image of the fundus and the visual field map based on a fixation position when the fundus is scanned by the scanning optical system and a fixation position when the visual field test is performed. Align the
An ophthalmological imaging device characterized by the following. The method includes a light source unit including a single visible light source and an infrared light source, and a light scanner, and the fundus of the eye to be examined is scanned by deflecting the light output from the single visible light source or the infrared light source with the light scanner. a scanning optical system that scans and receives return light from the fundus at a light receiving section;
a control unit that controls the scanning optical system;
an image forming unit that forms an image of the fundus based on a signal from the light receiving unit that receives the return light of the light output from the single visible light source or the infrared light source;
an analysis section that analyzes the image formed by the image forming section;
The control unit controls the single visible light source and the optical scanner to project visible light output from the single visible light source onto the fundus of the eye as fixation light for fixating the eye to be examined. and a second control that controls the single visible light source and the optical scanner to project visible light output from the single visible light source onto the fundus as stimulation light for visual field testing. and run
The scanning optical system repeatedly performs scanning using the infrared light output from the infrared light source, and repeatedly receives return light of the infrared light from the fundus at the light receiving unit,
The image forming unit repeatedly forms images of the fundus based on signals sequentially output from the light receiving unit,
The analysis unit analyzes the images repeatedly formed by the image forming unit to determine the displacement of the fundus;
The control unit controls the lighting timing of the single visible light source in the first control based on the displacement determined by the analysis unit while causing the scanning optical system to repeatedly scan using the infrared light. control and control of the lighting timing of the single visible light source in the second control in synchronization with the repetitive scanning,
The control unit is based on the image of the fundus formed by the image forming unit and the visual field test using the stimulation light output from the single visible light source at a lighting timing synchronized with the repeated scanning. Display the composite image with the visual field map on the display device ,
The control unit is configured to control the image of the fundus and the visual field map based on a fixation position when the fundus is scanned by the scanning optical system and a fixation position when the visual field test is performed. Align the
An ophthalmological imaging device characterized by the following. The ophthalmology clinic according to any one of claims 1 to 3, wherein the control unit displays the visual field map as an overlay on the image of the fundus formed by the image forming unit as the display of the composite image. Photography equipment. further comprising an OCT optical system that collects data by applying an optical coherence tomography (OCT) scan to a three-dimensional region of the fundus;
The image forming unit forms a planar image from the data collected by the OCT optical system,
The ophthalmologic photographing apparatus according to any one of claims 1 to 4 , wherein the control unit causes the display device to display a composite image of the planar image and the visual field map. The control unit controls the scanning optical system for scanning a range including a scotoma indicated by the visual field map and for visual field inspection for the range . Ophthalmology imaging equipment. The ophthalmologic imaging apparatus according to claim 6 , wherein the range further includes a characteristic part of the fundus. The control unit causes the display device to display a composite image of an image of the range formed by the image forming unit based on the scanning of the range and a visual field map of the range based on the visual field test for the range. The ophthalmologic photographing apparatus according to claim 6 or 7 , characterized in that:

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