JP7302924B2 - ophthalmic imaging equipment - Google Patents

Description

The present invention relates to an ophthalmic imaging apparatus.

When photographing the fundus, the amount of light of photographing illumination applied to the fundus is adjusted (see Patent Documents 1 and 2, for example).

JP 2005-279154 A Japanese Patent No. 5602501

Imaging of the fundus is affected by pupil size. Therefore, in photographing the fundus, the amount of light reflected from the fundus by infrared light is measured in advance in order to adjust the amount of lighting for photographing that irradiates the fundus. Amount of light is determined.

As the measurement light used for measuring the amount of light reflected from the fundus, for example, infrared light obtained by inserting an infrared cut filter in the optical path of a flash lamp that emits instantaneous light and causing the flash lamp to emit light as a test. is used as the measuring light, and infrared light that is continuously irradiated to the fundus to obtain moving images for observation is used as the measuring light. However, in the former case, it is technically difficult to fire the flash lamp continuously without interruption. there's a possibility that. In the latter case, since the amount of infrared light is constantly changing due to the moving image, there is a possibility that the amount of light of the shooting illumination determined based on the reflected light of the infrared light will be excessive or insufficient. There is

Therefore, the present application discloses an ophthalmologic imaging apparatus that can accurately determine the amount of light for imaging illumination.

In order to solve the above problems, in the present invention, when an imaging request is received while the fundus illuminated with invisible light is being imaged, the amount of light is changed to a reference amount of light, and based on the reflected light from the fundus in that state, We decided to determine the amount of light emitted at the time of shooting.

Specifically, the present invention is an ophthalmologic imaging apparatus comprising an imaging device sensitive to visible light and invisible light, a first illumination means for illuminating the fundus of the subject's eye with invisible light, and and the fundus illuminated by the first illumination means is being imaged by the imaging device. and a control means for causing the second illuminating means to emit light with an amount of light determined based on reflected light from the fundus illuminated with a reference light amount of invisible light, and photographing the fundus with an imaging element.

Here, the fundus is a region inside the eyeball including the surface of the retina. In the ophthalmologic imaging apparatus described above, the imaging device images the fundus illuminated through the pupil. Further, the above-described ophthalmologic photographing apparatus is provided with first illumination means for emitting invisible light and second illumination means for emitting visible light as illumination means for illuminating the fundus. Invisible light is light that cannot be detected by the human eye, and includes infrared light, for example. Visible light is light that is perceived by the human eye, and includes, for example, light with a wavelength range of approximately 400 nm to approximately 800 nm.

In the above-described ophthalmologic photographing apparatus, the fundus is illuminated by the first illumination means that emits invisible light, and when there is a request for photographing while the fundus is being imaged by light reflected from the fundus, the amount of light emitted from the first illumination means is adjusted to a predetermined value. change to the reference light intensity of Here, imaging refers to capturing a moving image or a still image, and capturing refers to capturing a still image. A photographing request is a request issued when obtaining a still image of the fundus illuminated by visible light is requested. signal of a processing device that automatically performs the above, and other various types of requests. Further, the reference light amount is a predetermined light amount, and is a light amount different from the light amount for illumination during observation of the fundus.

In the ophthalmologic imaging apparatus described above, when there is an imaging request, the amount of light emitted from the first illumination means is changed to the reference amount of light. Therefore, the amount of light reflected from the fundus illuminated with the invisible light of the reference light amount reflects the condition of the subject's eye such as the size of the pupil. It becomes a stable one that does not include changes in illumination light that constantly increases and decreases. Therefore, according to the above-described ophthalmologic imaging apparatus, since the light amount of the imaging illumination is determined using such stable reflected light, there is no possibility that the determined light amount of the imaging illumination will be excessive or insufficient. can be suppressed as much as possible.

By the way, when the control means receives a photographing request while the fundus illuminated by the first illumination means is being imaged by the imaging device, the control means controls the first illumination means while stopping the display of the image of the fundus oculi on the display means. is increased to the reference light quantity, and the second illuminating means is caused to emit light with a light emission quantity determined based on the reflected light of the fundus illuminated with the invisible light of the reference light quantity, and the fundus is photographed by the imaging device. good.

With such an ophthalmologic photographing apparatus, the fundus image is not displayed when the light emission amount of the first illumination means is increased to the reference light amount, so that the observer of the fundus does not feel the change in the light amount.

Further, when receiving a photographing request while the fundus illuminated by the first illumination means is being imaged by the imaging device, the control means changes the light emission amount of the first illumination means to the reference light amount, and detects the invisible light of the reference light amount. The fundus of the eye may be photographed by the imaging device by causing the second illumination means to emit light with a light emission amount determined based on the brightness of the image of the fundus projected on the imaging device by the reflected light of the fundus illuminated with light.

With such an ophthalmologic imaging apparatus, the amount of light emission can be determined by the brightness of the image obtained by the imaging device, so there is no need to provide a configuration for measuring the amount of reflected light separately from the imaging device. Therefore, the device configuration can be simplified.

Further, when receiving a photographing request while the fundus illuminated by the first illumination means is being imaged by the imaging device, the control means changes the light emission amount of the first illumination means to the reference light amount, and detects the invisible light of the reference light amount. The second lighting means emits light with an amount of light determined based on the average value of the brightness of a plurality of images of the fundus projected on the imaging device by reflected light from the fundus illuminated with light, and the fundus is photographed by the imaging device. may be

With such an ophthalmologic imaging apparatus, it is possible to suppress the possibility that an inappropriate light emission amount is determined as compared with the case where the light emission amount is determined based on the brightness of one image.

Further, when receiving a photographing request while the fundus illuminated by the first illumination means is being imaged by the imaging device, the control means changes the light emission amount of the first illumination means to the reference light amount, and detects the invisible light of the reference light amount. The fundus is photographed by the imaging device by causing the second illuminating means to emit light with an amount of light emission determined based on the brightness of a predetermined region of the image of the fundus projected on the imaging device by reflected light from the fundus illuminated with light. good too.

Here, the predetermined area is a partial area of the image of the fundus, such as an area slightly away from the center where the stray light is reflected. With such an ophthalmologic imaging apparatus, the brightness of the part where the stray light is reflected is not referred to in determining the light emission amount, so it is possible to suppress the possibility that the light emission amount is determined inappropriately.

With the ophthalmologic imaging apparatus described above, it is possible to accurately determine the amount of light for imaging illumination.

FIG. 1 is a diagram showing a schematic configuration of an optical system of an ophthalmologic imaging apparatus according to an embodiment. FIG. 2 is an example of a block diagram of an electric circuit provided in the ophthalmologic imaging apparatus. FIG. 3 is a diagram showing a timing chart of each process before and after photographing the fundus. FIG. 4 is a diagram showing a processing flow realized by the ophthalmologic imaging apparatus. FIG. 5 is a diagram showing an example of a region in which luminance values are referred to when determining the amount of light emitted during shooting. FIG. 6 is a diagram showing an example of changes in the amount of light emitted by observation illumination.

Embodiments of the present invention will be described below. The embodiments shown below are examples of the embodiments of the present invention, and the technical scope of the present invention is not limited to the following aspects.

FIG. 1 is a diagram showing a schematic configuration of an optical system of an ophthalmologic imaging apparatus according to this embodiment. An ophthalmologic photographing apparatus 1 is an apparatus for photographing the fundus of an eye to be examined E, and includes an objective lens 2, an anterior ocular illumination 2A, an anterior ocular imaging lens 2B, a perforated mirror 3, a focus lens 4, a half mirror 5, an inner A fixation light 6, a relay lens 7, a focus dot mirror 8, a focus index projection system 9, a black dot plate glass 10, a relay lens 11, a ring slit 12, a diffuser plate 13, and a photographing illumination 14 (referred to as "second illumination means" in the present application). an example), observation illumination 15 (an example of the “first illumination means” referred to in the present application), imaging lens 16, narrow-angle lens 17, wide-angle lens 18, infrared cut filter 19, image sensor 20 (which is an example of the “imaging device” referred to in the present application).

First, the positional relationship and function of each component provided in the ophthalmologic imaging apparatus 1 will be described. The objective lens 2 is a lens positioned in front of the eye E to be examined. The anterior segment illumination 2A is an infrared LED that has both a function of illuminating the anterior segment of the eye to be inspected E with infrared light and a function of projecting a distance measuring index onto the anterior segment of the eye to be inspected E. (Light Emitting Diode). On the optical axis behind the objective lens 2, an anterior segment imaging lens 2B, a perforated mirror 3, a focus lens 4, a half mirror 5, and an internal fixation lamp 6 are arranged in this order. The anterior segment imaging lens 2B is a movable lens that is inserted and removed on the optical axis behind the objective lens 2, and is moved by an actuator in conjunction with a switch button provided in the ophthalmic photographing apparatus 1 and a control signal. The perforated mirror 3 is a mirror having a through hole formed in a portion through which the optical axis of the objective lens 2 passes, and is fixed in the ophthalmologic imaging apparatus 1 at an appropriate tilt angle with respect to the optical axis of the objective lens 2. .

A relay lens 7, a focus dot mirror 8, a black dot plate glass 10, and a relay lens are arranged in this order from the perforated mirror 3 side on the axis of the illumination optical system that guides the illumination light reflected by the perforated mirror 3 and applied to the eye E to be examined. 11, a ring slit 12, a diffuser plate 13, a photographing illumination 14, and an observation illumination 15 are arranged. Therefore, the light emitted from the photographic illumination 14, which is a flash lamp that instantaneously emits visible light, and the observation illumination 15, which is an infrared LED that emits invisible infrared light, is emitted from the diffusion plate 13 and the ring slit 12. In the process of passing through the relay lens 11,
The light passes through the black dot plate glass 10, the focus dot mirror 8, and the relay lens 7, is reflected by the perforated mirror 3, passes through the objective lens 2, and illuminates the fundus of the eye E to be examined.

The black dot plate glass 10 is provided for the purpose of preventing reflected light from the objective lens 2 from appearing in a photographed image, and a small light blocking object is arranged at the center of the plate glass, that is, at the position of the optical axis. Light from the focus index projection system 9 is incident on the focus dot mirror 8 between the black dot plate glass 10 and the relay lens 7 at such an angle that the reflected light is aligned with the optical axis of the relay lens 7 . A focus index projection system 9 projects a focus index onto the fundus of the eye E to be examined. Therefore, the focus index light emitted by the focus index projection system 9 is incident on the fundus of the eye E to be inspected, in addition to the light emitted by the photographing illumination 14 and the observation illumination 15 . An infrared LED that emits infrared light is used for the focus index projection system 9 .

Reflected light from the fundus of the subject's eye E illuminated by the light of the photographing illumination 14 and the observation illumination 15 passes through the objective lens 2 , the perforated mirror 3 and the focus lens 4 and enters the half mirror 5 . A half mirror 5 is fixed in the ophthalmic photographing apparatus 1 at an appropriate tilt angle with respect to the optical axis of the objective lens 2 . Therefore, the reflected light from the fundus of the eye to be examined E is reflected at an appropriate angle with respect to the optical axis of the objective lens 2 by the half mirror 5 . An imaging lens 16 , an infrared cut filter 19 , and an image sensor 20 are provided in this order on the optical axis of reflected light from the half mirror 5 incident from the focus lens 4 . Between the imaging lens 16 and the infrared cut filter 19, a narrow-angle lens 17 or a wide-angle lens 18, which is a zooming lens that is appropriately selected according to the magnification desired by the observer, is inserted. . Therefore, the reflected light from the fundus of the subject's eye E is reflected by the half mirror 5 , passes through the imaging lens 16 , passes through the narrow-angle lens 17 or the wide-angle lens 18 , and enters the image sensor 20 . In the image sensor 20, photoelectric conversion elements arranged in a matrix receive light energy and emit electrical signals, so that an image of the fundus of the eye E to be examined is obtained.

The image sensor 20 is an imaging element that has sensitivity to visible light and infrared light. Therefore, the image sensor 20 is configured such that the light sources for illuminating the eye to be inspected E are the anterior segment illumination 2A for illuminating the anterior segment of the eye to be inspected E, the photographing illumination 14 for illuminating the fundus of the eye to be inspected E, and the eye to be inspected. An image of the anterior segment or the fundus can be obtained with any of the observation illuminations 15 for illuminating the fundus of E. FIG. Such an image sensor 20 includes, for example, CMOS.

The infrared cut filter 19 is inserted into the optical path when imaging the fundus of the subject's eye E with visible light, and removed from the optical path when observing with infrared light. The infrared cut filter 19 has a filter function of blocking infrared light, and plays a role of preventing infrared light from being reflected in the captured image of the fundus.

In addition, in the ophthalmologic imaging apparatus 1, the main body of the imaging apparatus containing the optical system components described above is mounted on a frame. The ophthalmologic photographing apparatus 1 is provided with a moving mechanism for moving the housing mounted on the pedestal back and forth, left and right, or up and down by operating the operation lever. The positional relationship of the main body of the imaging device can be adjusted.

FIG. 2 is an example of a block diagram of an electric circuit (an example of the “control means” referred to in the present application) provided in the ophthalmologic imaging apparatus 1. As shown in FIG. The ophthalmologic imaging apparatus 1 includes, for example, a CPU board 21, an LCD panel 22 (Liquid Crystal Display), an LCD backlight 23, an operation section 24, and a main board 25. FIG. In FIG. 2, the actuators that move the focus lens 4 and the infrared cut filter 19, the high-voltage circuit that emits light from the imaging lighting 14, the LEDs provided in the focus index projection system 9, and the observation lighting 15 are all grouped together as electronic components 26. showing.

The CPU board 21 is a circuit board mainly responsible for processing images acquired by the image sensor 20, and includes a CPU (Central Processing Unit) and FPGA (Field Programmable Gate Array) that process images, and an SD card ( "SD" is a registered trademark) and various electronic parts such as a drive are mounted. The image sensor 20 operates according to a control signal from the CPU board 21 and provides the CPU board 21 with the acquired image. The CPU board 21 performs various processes on the image acquired by the image sensor 20, and outputs the processed image to the LCD panel 22 or SD card. An image output from the CPU board 21 is displayed on the LCD panel 22 .

The main board 25 is a circuit board that controls the entire ophthalmologic imaging apparatus 1, and is mounted with an FPGA and various other electronic components. The main board 25 operates the CPU board 21 and the electronic components 26 according to the contents of the operation received by the operation section 24 . The main substrate 25 implements the following processing flow.

That is, when the use of the ophthalmologic photographing apparatus 1 is started, the operation of the image sensor 20 and the energization of the observation illumination 15 are started. When the ophthalmologic photographing apparatus 1 is started to be used, the anterior segment mode in which the anterior segment of the subject's eye E is displayed on the LCD panel 22 is selected, so the anterior segment imaging lens 2B is inserted on the optical axis. The anterior segment illumination 2A for illuminating the anterior segment is also energized. Then, in the ophthalmologic photographing apparatus 1, after alignment adjustment is performed so that the anterior segment of the eye to be examined E is clearly captured, the pupil diameter is checked, and observation of the fundus is started.

FIG. 3 is a diagram showing a timing chart of each process before and after photographing the fundus. When observation of the fundus is started, the observation illumination 15 repeats turning on and off at an arbitrary light emission intensity (hereinafter referred to as "arbitrary light intensity") every 1/60th of a second. Images are acquired by the image sensor 20 alternately every 1/60th of a second. The arbitrary amount of light is the amount of illumination light that enables an image of the fundus to be obtained by reflected infrared light, and is the amount of light that is constantly increased or decreased under the control of the main board 25 . An observation image is an image of the fundus illuminated with infrared light by lighting of the observation illumination 15 and is an image displayed on the LCD panel 22 . The determination image is an image of the fundus projected by the focus index projection system 9 and including the working dots and the focus dots.

FIG. 4 is a diagram showing a processing flow realized by the ophthalmologic imaging apparatus 1. As shown in FIG. When the shutter button of the operation unit 24 is pressed in a state where observation images are acquired every 1/60th of a second and displayed as a moving image on the LCD panel 22 (symbol F1 in FIG. 3), the ophthalmologic photographing apparatus 1: According to a predetermined sequence, the following processing is realized along predetermined timings indicated by symbols T1 to T7 in FIG.

That is, the ophthalmologic imaging apparatus 1 accepts the operation of the shutter button as an imaging request, stops the synchronous light emission of the observation illumination 15, and starts continuously lighting the observation illumination 15 with the reference light amount (S101). Also, in the ophthalmologic photographing apparatus 1, the display on the LCD panel 22 is temporarily stopped at this timing. Here, the reference amount of light is the amount of infrared light with which the observation illumination 15 irradiates the fundus when determining the light emission amount of the photographing illumination 14, and is, for example, a predetermined amount of light larger than the arbitrary amount of light. . Then, in the ophthalmologic photographing apparatus 1, the image sensor 20 acquires three frames of judgment images in a state in which the observation illumination 15 is continuously lit with the reference light amount (S102). Then, in the ophthalmologic photographing apparatus 1, the light emission amount at the time of photographing is determined based on the luminance value of the acquired image (S103, reference numeral F2 in FIG. 3).

FIG. 5 is a diagram showing an example of a region in which luminance values are referred to when determining the amount of light emitted during shooting. 5A shows an observation image displayed on the LCD panel 22 as a moving image, FIG. 5B shows a judgment image acquired when the observation illumination 15 is off, FIG. 5(C) shows a determination image acquired in a state in which the lighting 15 is continuously lit at the reference light amount.

As shown in FIG. 5A, the observation image displayed as a moving image includes working dots WDL and WDR on both left and right sides of the center spot CS, and focus dots above the center spot CS so as to overlap the fundus image. Dot FD is displayed. Further, as shown in FIGS. 5B and 5C, the determination image hardly shows the fundus image, but shows the working dots WDL and WDR and the focus dot FD. Then, the area in which the luminance value is referred to when determining the light emission amount at the time of photographing is an area slightly below the center spot CS, that is, the determination area HE shown in FIG. (which is an example of "area").

The central spot CS is an area in which stray light reflected from the fundus is reflected, so it is an inappropriate area for referring to luminance in determining the amount of light emitted during imaging. Therefore, in the ophthalmologic photographing apparatus 1 of the present embodiment, by setting the determination area HE in a region slightly away from the center spot CS, the brightness of the part where the stray light is reflected is referred to in determining the light emission amount. This prevents determination of an appropriate amount of light emission.

The ophthalmologic photographing apparatus 1 determines the amount of light emitted during photographing based on the average value obtained by averaging the brightness values of the judgment area HE in three frames (three judgment images indicated by symbols G1 to G3 in FIG. 3). Specifically, the ophthalmologic imaging apparatus 1 increases or decreases the amount of light emitted during imaging according to the difference between the average value and the prescribed standard value.

After determining the amount of light emitted during imaging, the ophthalmologic imaging apparatus 1 switches the operation mode of the image sensor 20 to the visible imaging mode (S104). By switching the operation mode of the image sensor 20 from the observation mode to the visible imaging mode, reading of pixels that have been omitted for obtaining moving images is performed, and reading of all the pixels provided in the image sensor 20 is possible. state. Then, the ophthalmologic photographing apparatus 1 turns off the observation illumination 15 (S105), and inserts the infrared cut filter 19 removed from the optical path into the optical path (S106, reference numeral F3 in FIG. 3). Then, the ophthalmologic photographing apparatus 1 causes the photographing illumination 14 to momentarily emit light with the amount of light emission determined in the process of step S103, and the image sensor 20 photographs the fundus at the same time that the photographing illumination 14 emits light (S107, FIG. 3 sign F4). As a result, the image sensor 20 acquires a still image of the fundus illuminated by the imaging illumination 14 emitting visible light.

After acquiring a still image of the fundus by the image sensor 20, the ophthalmologic imaging apparatus 1 removes the infrared cut filter 19 inserted in the optical path from the optical path (S108). Then, the ophthalmologic photographing apparatus 1 restarts the synchronous light emission of the observation illumination 15 stopped in the process of step S105 (S109), and observes the operation mode of the image sensor 20, which was changed to the photographing mode in the process of step S104. mode (S110, symbol F5 in FIG. 3). Also, in the ophthalmologic photographing apparatus 1, the display on the LCD panel 22 is resumed at this timing. By switching the operation mode of the image sensor 20 from the visible photography mode to the observation mode, reading of all pixels that has been performed to acquire a clear still image is stopped, and one of all the pixels provided in the image sensor 20 is stopped. In other words, the readout of the pixels for moving images is performed. As a result, the state before the photographing operation is started, that is, the observation image is acquired every 1/60th of a second and displayed as a moving image on the LCD panel 22 (reference numeral F6 in FIG. 3).

FIG. 6 is a diagram showing an example of changes in the amount of light emitted by the observation illumination 15. As shown in FIG. In the ophthalmologic photographing apparatus 1 of the present embodiment, the fundus is illuminated by the observation illumination 15 emitting infrared light, and when the shutter button is pressed while the fundus is imaged by the light reflected from the fundus, the observation illumination 15 is illuminated. is changed from the arbitrary light amount to the reference light amount. Since the arbitrary amount of light is the amount of light that is illuminated during observation of the fundus, the appropriate amount of light for the fundus as shown in FIG. It is the amount of light that is constantly adjusted to achieve brightness. On the other hand, the reference light amount is a predetermined light amount, as described above, and is not a light amount that constantly increases and decreases like the arbitrary light amount. Therefore, the amount of reflected light from the fundus illuminated with the reference amount of infrared light reflects the condition of the subject's eye, such as the size of the pupil, and the amount of light emitted to obtain a moving image of the fundus. becomes a stable one that does not include changes in the illumination light that constantly increases and decreases. Therefore, according to the ophthalmologic imaging apparatus 1 of the present embodiment, since the light amount of the imaging illumination is determined using such stable reflected light, the determined light amount of the imaging illumination becomes excessive or insufficient. The possibility can be suppressed as much as possible.

Further, since the display on the LCD panel 22 is stopped while the above series of processing is being performed, the fundus image is not displayed when the light emission amount of the observation illumination 15 changes to the reference light amount. Therefore, the observer of the fundus does not perceive any change in the amount of light.

Note that the ophthalmologic imaging apparatus 1 described above may be modified, for example, as follows.

In the ophthalmologic photographing apparatus 1 of the above-described embodiment, the determination area HE is set in a region slightly below the center spot CS, but the determination area HE is set in a region further away from the center spot CS, for example. may be set, may be set in a plurality of regions away from the center spot CS, or may be set in a plurality of regions so as to surround the center spot CS from a plurality of locations. good too. When the determination area HE is set in a plurality of areas, the determination of the light emission amount at the time of photographing is performed using a value obtained by averaging the luminance values of the pixels in the plurality of areas.

Further, in the ophthalmologic photographing apparatus 1 of the above embodiment, when the shutter button is pressed, the above series of processes are executed according to a predetermined sequence regardless of the brightness value in the determination area HE. For example, the electric circuit provided in the ophthalmologic photographing apparatus 1 may be executed at the timing when it automatically detects that the pupil diameter has reached a predetermined size.

Further, in the ophthalmologic imaging apparatus 1 of the above embodiment, the amount of light emission at the time of imaging is determined based on the average value obtained by averaging the brightness values of the images for three frames acquired in the process of step S102. For example, the light emission amount at the time may be determined based on the luminance value selected by majority from among the luminance values of images for a plurality of frames, or may be determined based on the luminance value of a specific one frame image among the images for a plurality of frames. It may be determined based on the luminance value, or may be determined based only on the luminance value of the acquired image for one frame.

Further, in the ophthalmologic photographing apparatus 1 of the above-described embodiment, the amount of light emitted during photographing is determined based on the luminance value of the image acquired by the image sensor 20. However, the amount of light emitted during photographing is 20 may be determined based on the amount of reflected light observed using a separately prepared light receiving element. In this case, the separately prepared light-receiving element must have at least sensitivity to the infrared light emitted by the observation illumination 15. It may have sensitivity to both external light and visible light.

1 Ophthalmology photographing device 2 Objective lens 2A Anterior illumination: 2B Anterior imaging lens 3 Perforated mirror 4 Focus lens 5 Half mirror 6 Internal fixation light: 7 Relay lens: 8 Focus dot mirror: 9 Focus index projection system: 10 Black dot plate glass: 11 Relay lens: 12 Ring slit: 13 Diffusion plate: 14 Photographing illumination: 15 Observation illumination: 16 Imaging lens: 17 Narrow-angle lens: 18 Wide-angle lens: 19 Infrared cut filter: 20 Image sensor: 21 CPU board: 22 LCD panel: 23 LCD backlight: 24 Operation unit: 25 Main board: 26 Electronic parts: FD Focus dot: WDL, WDR Working dot: HE Determination area: CS Central spot

Claims (4)

an imaging device sensitive to visible light and invisible light;
a first illumination means for observation that illuminates the fundus of the subject's eye with invisible light;
a second illumination means for photographing that illuminates the fundus with visible light;
When an imaging request is received while the fundus illuminated by the first illumination means is being imaged by the imaging element, the light emission amount of the first illumination means is changed to a predetermined reference light amount, a control means for causing the second illuminating means to emit light with a light emission amount determined based on reflected light from the fundus illuminated with invisible light, and photographing the fundus with the imaging device ;
When the control means receives the photographing request while the fundus illuminated by the first illumination means is being imaged by the imaging device, the control means changes the light emission amount of the first illumination means to the reference light amount. illuminating the second illuminating means with a light emission amount determined based on an average value of luminance of a plurality of images of the fundus projected on the imaging device by reflected light from the fundus illuminated with the invisible light of the reference light amount; and photographing the fundus with the imaging device,
Ophthalmic imaging equipment. When the control means receives the photographing request while the imaging device is imaging the fundus illuminated by the first illumination means, the control means stops displaying the image of the fundus on the display means. increasing the light emission amount of the first illumination means to the reference light amount, and causing the second illumination means to emit light with the light emission amount determined based on the reflected light of the fundus illuminated with the invisible light of the reference light amount; is photographed with the image sensor,
The ophthalmic imaging apparatus according to claim 1. When the control means receives the photographing request while the fundus illuminated by the first illumination means is being imaged by the imaging device, the control means changes the light emission amount of the first illumination means to the reference light amount. and illuminating the fundus by causing the second illuminating means to emit light with a light emission amount determined based on the brightness of the image of the fundus projected on the imaging element by the reflected light from the fundus illuminated with the invisible light of the reference light amount. Take a picture with an image sensor,
The ophthalmologic imaging apparatus according to claim 1 or 2. When the control means receives the photographing request while the fundus illuminated by the first illumination means is being imaged by the imaging device, the control means changes the light emission amount of the first illumination means to the reference light amount. and causing the second illuminating means to emit light with an amount of light emission determined based on the brightness of a predetermined region of the image of the fundus projected on the imaging element by the reflected light of the fundus illuminated with the invisible light of the reference light amount. photographing the fundus with the imaging element;
The ophthalmologic imaging apparatus according to any one of claims 1 to 3 .

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