Ophthalmologic apparatus, control method of ophthalmologic apparatus, and program

Abstract

To reduce glare at the time of observation, and to acquire brightness suitable for observation.SOLUTION: An ophthalmologic apparatus for imaging an eye to be examined by illuminating the eye to be examined with illumination light includes illumination means for illuminating a first region of the eye to be examined with first illumination light having a first spectrum when taking a first image of the eye to be examined, illuminating a second region having a yellow spot different from the first region with second illumination light having a second spectrum with a second peak wavelength longer than a first peak wavelength of the first spectrum, and illuminating the eye to be examined with the first illumination light when taking a second image of the eye to be examined.SELECTED DRAWING: Figure 9

Description

[Technical Field]

[0001] The present disclosure relates to an ophthalmic apparatus, a control method for an ophthalmic apparatus, and a program. [Background technology]

[0002] Currently, in the field of ophthalmology, fundus cameras are in practical use as devices for capturing two-dimensional images of the fundus.

[0003] When observing the fundus with a fundus camera, a light source such as an LED that emits near-infrared or infrared light is used. In this case, the observed image is monochrome. When photographing the fundus, a light source such as an arc lamp for flashing or an LED that emits visible light is used. In this case, the photographed image is color. Generally, visible light is more dazzling than infrared light, so if the subject's eye is illuminated with a visible light source, there is a high possibility that the subject's eye will constrict. For this reason, fundus cameras that use infrared light for observation and visible light for photography are becoming more common. However, there is also a need to obtain color images rather than monochrome images for observation.

[0004] Here, Patent Document 1 discloses an ophthalmic apparatus that uses a visible light source both during observation and photography in order to obtain a color image during observation.

[0005] Furthermore, Patent Document 1 discloses a method for reducing glare during observation by reducing the amount of light during observation compared to the amount of light during photography. [Prior art documents] [Patent documents]

[0006] [Patent Document 1] Japanese Patent Application Laid-Open No. 2002-17682 Summary of the Invention [Problem to be solved by the invention]

[0007] Here, with a method of reducing the amount of light during observation to be less than the amount of light during photography, it is not possible to obtain brightness suitable for observation, and the fundus may become dark.

[0008] Therefore, an object of the present disclosure is to reduce glare during observation and obtain brightness suitable for observation. [Means for solving the problem]

[0009] The ophthalmic apparatus disclosed herein is an ophthalmic apparatus that photographs a test eye by illuminating the test eye with illumination light, and includes an illumination means that, when photographing a first image of the test eye, illuminates a first region of the test eye with first illumination light having a first spectrum, and illuminates a second region different from the first region, the second region including the macula, with second illumination light having a second spectrum that has a second peak wavelength longer than the first peak wavelength of the first spectrum, and illuminates the test eye with the first illumination light when photographing a second image of the test eye. [Effects of the Invention]

[0010] According to the present disclosure, it is possible to reduce glare during observation and obtain brightness suitable for observation. [Brief explanation of the drawings]

[0011] [Figure 1] 1 is a schematic diagram showing a general configuration of a fundus camera according to a first embodiment. [Figure 2] FIG. 1 is a schematic diagram showing an optical configuration according to a first embodiment. [Figure 3] 4 is a schematic diagram showing a modified example of the arrangement of light sources according to the first embodiment. FIG. [Figure 4] FIG. 4 is a schematic diagram showing a modified example of the arrangement of image pickup elements according to the first embodiment. [Figure 5] FIG. 2 is a schematic diagram illustrating an example of a control unit according to the first embodiment. [Figure 6] 3 is a schematic diagram showing an example of the relationship between illumination of an eye to be inspected and miosis according to the first embodiment. FIG. [Figure 7] FIG. 2 is a schematic diagram illustrating an example of a switchable filter according to the first embodiment. [Figure 8] 4 is a flowchart showing a series of processes for visible light observation and visible light photography according to the first embodiment. [Figure 9] 3A and 3B are schematic diagrams showing an example of a fundus observation image and an illumination state according to the first embodiment. [Figure 10] 10 is a flowchart showing a photographing process according to a third modification of the first embodiment. [Figure 11] 10 is a schematic diagram showing a captured image according to a third modification of the first embodiment. FIG. [Figure 12] FIG. 10 is a schematic diagram showing an optical configuration according to a second embodiment. [Figure 13] 10 is a flowchart showing a series of processes for visible light observation and visible light photography according to the second embodiment. [Figure 14] 10 is a schematic diagram showing an example of a light emission pattern when scanning a fundus according to the second embodiment. FIG. [Figure 15] FIG. 10 is a schematic diagram showing another example of a light emission pattern when scanning a fundus according to the second embodiment. [Figure 16] FIG. 10 is a schematic diagram showing a modified example of the arrangement of light receiving elements according to the second embodiment. [Figure 17] FIG. 2 is a diagram showing the spectrum of a light source 201. DETAILED DESCRIPTION OF THE INVENTION

[0012] The embodiments of the present disclosure will be described in detail below with reference to the drawings. However, the dimensions, materials, shapes, and relative positions of components described in the following embodiments are arbitrary and can be changed depending on the configuration of the device to which the present disclosure is applied or various conditions. In addition, the same reference numerals are used in the drawings to indicate identical or functionally similar elements.

[0013] [Embodiment 1] In this embodiment, an embodiment of a fundus camera to which the present disclosure is applied will be described with reference to FIGS. 1 to 11. FIG.

[0014] In this embodiment, a filter is used to irradiate different regions of the fundus 303 of the subject's eye E with illumination light having different characteristics. Here, the characteristics refer to, for example, spectrum. The spectrum will be described in detail later with reference to FIG. 17. The configuration described in this embodiment can suppress miosis of the subject's eye (reduce glare during observation). Furthermore, it is possible to brighten the fundus, thereby obtaining brightness suitable for observation. This embodiment will be described in detail below.

[0015] <Outline of the device> First, the general configuration of a fundus camera according to this embodiment will be described with reference to Fig. 1. Fig. 1 is a schematic diagram showing an example of the general configuration of a fundus camera. The fundus camera is provided with an imaging unit 10, a control unit 20, and a display unit 30. The imaging unit 10 is provided with an optical head unit 100, a stage unit 110, a base unit 120 including operation units such as a joystick and a shooting button (not shown), and a face support unit 130.

[0016] The optical head unit 100 includes a measurement optical system that irradiates the subject's eye with light, detects the return light from the subject's eye, and observes and captures an anterior ocular observation image and a frontal fundus image. The stage unit 110 is an example of a moving unit that can move the optical head unit 100 in the x, y, and z directions in the figure using a driving mechanism such as a motor (not shown). The face support unit 130 is a chin rest that can fix the subject's chin and forehead, thereby promoting fixation of the subject's eye (examined eye). The face support unit 130 is also an example of a moving unit that can move the face support unit 130 in the y direction in the figure using a driving mechanism such as a motor (not shown).

[0017] The control unit 20 is connected to the photographing unit 10 and the display unit 30 and can control them. The control unit 20 can align the optical head unit 100 with the subject's eye by, for example, controlling the movement of the stage unit 110. The control unit 20 can also generate an anterior eye observation image, a frontal fundus image, and the like based on data acquired by the photographing unit 10.

[0018] The control unit 20 can be configured using a general computer including a processor and memory, but may also be configured as a computer dedicated to the fundus camera. The control unit 20 may be a separate (external) computer to which the photographing unit 10 is communicatively connected, or may be a built-in (internal) computer of the photographing unit 10. The control unit 20 may also be, for example, a personal computer, such as a desktop PC, a notebook PC, or a tablet PC (portable information terminal).

[0019] The display unit 30 is configured by any monitor. The display unit 30 displays various information such as subject information and various images under the control of the control unit 20. The display unit 30 may be a touch panel display. In this case, the display unit 30 is also used as an operation unit.

[0020] In this embodiment, the photographing unit 10, the control unit 20, and the display unit 30 are configured separately, but some or all of these may be configured as an integrated unit. Also, the control unit 20 may be connected to other devices (for example, a storage device, etc.).

[0021] <Optical configuration of the device> Next, the optical system of the fundus camera according to this embodiment will be described with reference to the schematic diagram of FIG. 2. The optical system is composed of an observation optical system for observing the eye to be examined, or an imaging optical system for imaging the eye to be examined. The configuration of the optical system is divided into multiple optical axes L1 to L5 on which various optical elements are arranged, and each of these will be described in order. Note that optical axes L1 to L3 are optical paths along which illumination light emitted from a visible light source 201 illuminates the eye to be examined. Note that the configuration relating to optical axes L1 to L3 is an example of an illumination means.

[0022] A light source that emits light for observing or photographing the fundus and related components are arranged on the optical axis L1. This component is arranged along the optical path of the light emitted from the light source. A light source 201 for observation and photography, a condenser lens 202, and a mirror 203 are arranged on the optical axis L1. An LED capable of emitting both white light and near-infrared light (hereinafter sometimes simply referred to as "infrared" or "IR (InfraRed)") is used as the light source 201.

[0023] FIG. 17 shows a typical spectrum of light source 201. In FIG. 17, the horizontal axis represents wavelength, and the vertical axis represents intensity. The intensity is normalized with the maximum value set to 100%. Light source 201 shows both a white light spectrum (solid line) and a near-infrared light spectrum (dashed line). The peak wavelength of white light (the wavelength at which light intensity is maximum) is approximately 460 nm. The peak wavelength of near-infrared light is approximately 780 nm. Light having a wavelength of approximately 780 nm is generally invisible light. Although the peak wavelengths of white light and near-infrared light are different, the wavelengths of white light and near-infrared light do not need to be different (the spectrum of white light and the spectrum of near-infrared light may overlap). Note that the spectrum of white light (solid line) in FIG. 17 is an example of a first spectrum. The spectrum of near-infrared light (dashed line) is an example of a second spectrum. The white light is an example of a first illumination light. Further, near-infrared light is an example of second illumination light, and the peak wavelength of white light is an example of a first peak wavelength. Further, the peak wavelength of near-infrared light is an example of a second peak wavelength.

[0024] Note that instead of providing an LED that can emit both white and near-infrared light, a white LED and a near-infrared LED may be provided separately. For example, as shown in Fig. 3, the mirror 203 may be configured as a dichroic mirror that transmits light in the IR band and reflects light in the visible light band, and a xenon lamp or white LED 201 may be used in combination with an IR band LED arranged on the optical path L2.

[0025] On the optical axis L2 in the reflection direction of the mirror 203, a ring slit 204 having a ring-shaped opening, a lens baffle 205, a splitter unit 206, a relay lens 207, a corneal baffle 208, and a perforated mirror 209 having a central opening are arranged in this order from the mirror 203. In correspondence with the ocular optical system of Figure 6, the ring slit 204 is arranged at a position that is approximately optically conjugate with the pupil 301 of the subject's eye E, the lens baffle 205 is arranged at a position that is approximately optically conjugate with the posterior surface 302 of the lens of the subject's eye E, and the corneal baffle 208 is arranged at a position that is approximately optically conjugate with the cornea 300 of the subject's eye E.

[0026] An objective lens 211 is disposed on an optical axis L3 in the reflection direction of the perforated mirror 209, facing a dichroic mirror 210 and the subject's eye E. A photographing diaphragm 220 is disposed in the hole of the perforated mirror 209, and further behind it are a focus lens 212 that adjusts the focus by moving its position on the optical axis L3, a photographing lens 213, and a half mirror 214. A two-dimensional image sensor 230 that can be used for both observation in visible light and still image capture is disposed beyond the half mirror 214.

[0027] In this embodiment, an RGB-IR type CMOS sensor is used as the two-dimensional image sensor 230. An RGB-IR type CMOS sensor is an image sensor that has IR (infrared) pixels in addition to the usual RGB (red, green, blue) pixels. With this configuration, the RGB-IR type CMOS sensor can capture both IR light images and visible light images. Instead of using an RGB-IR type CMOS sensor, a configuration using a CMOS sensor for visible light and a CMOS sensor for IR light may be used separately. For example, as shown in FIG. 4, a dichroic mirror 280 that transmits visible light and reflects infrared light may be used to separate the IR light and visible light. In this configuration, a visible light CMOS camera 230a and an IR light CMOS camera 230b are disposed. If a bright image cannot be obtained due to the low pixel sensitivity of the RGB-IR type CMOS sensor, a bright image can be obtained by using a visible light CMOS sensor and an IR light CMOS sensor separately.

[0028] A high-sensitivity CMOS sensor may be used as the two-dimensional image sensor 230. Because the amount of light reflected from the fundus 303 of the subject's eye E is low compared to the amount of incident light, a bright image can be obtained by using a high-sensitivity CMOS sensor. A single photon avalanche diode (SPAD) sensor may be used as the two-dimensional image sensor 230. The SPAD sensor is a highly sensitive sensor that uses avalanche multiplication and photon counting technology. The SPAD sensor has the advantages of being able to achieve resolution even with a low amount of received light and of being able to eliminate read noise during digital signal conversion, making it suitable for generating a clearer image from a small amount of reflected light from the fundus 303. Note that the reflected light of the white light from the light source 201 reflected by the fundus 303 is an example of first reflected light. The reflected light of the near-infrared light from the light source 201 reflected by the fundus 303 is an example of second reflected light.

[0029] An internal fixation target 260 that indicates the target position of the line of sight of the subject's eye is disposed at the end of the optical axis L4, which is the reflection direction of the half mirror 214. The target position of the line of sight of the subject's eye can be changed to any position by the examiner's operation, etc.

[0030] A lens 215, a diaphragm 216, a prism 217, a lens 218, and a two-dimensional image sensor 240 sensitive to infrared light are arranged on the optical axis L5 of the dichroic mirror 210. This configuration forms an anterior-segment observation optical system for observing the anterior segment. Light incident on the prism 217 is refracted in opposite left-right directions by the upper and lower halves of the prism 217 and split. Therefore, when the distance between the subject's eye E and the optical head unit 100 is longer than the appropriate working distance, the observed image of the anterior segment is formed by the lens 215 closer to the lens 215 than the prism 217, with the upper half of the observed image shifted to the right and the lower half shifted to the left. When the distance between the subject's eye E and the optical head unit 100 is shorter than the appropriate working distance, the observed image is captured upside down. The anterior segment of the subject's eye E is illuminated by an infrared light source 250 for anterior-segment observation. The above-described anterior-segment observation optical system makes it possible to detect the alignment state with the anterior segment of the subject's eye E. In this embodiment, this configuration, the stage unit 110, and the control unit 20 constitute an alignment means that controls the alignment of the photographing optical system with the subject's eye. The two-dimensional image sensor 230 and the two-dimensional image sensor 240 are examples of a light receiving unit.

[0031] Next, the configuration of the focus optical system will be described.

[0032] The split unit 206 arranged on the optical axis L2 has a focus index light source, a prism, a focus index mask, an insertion / removal mechanism, and a unit movement mechanism (not shown). The focus index light source is used to project a focus index. The prism is used to split the light source and projects split focus indexes onto the pupil of the subject's eye E. The focus index mask is also used to form the outer shape of the focus index. The focus index mask is arranged in a position that is approximately optically conjugate with the fundus 303 of the subject's eye E.

[0033] The insertion / removal mechanism has a split insertion / removal drive motor. The split insertion / removal drive motor inserts the split unit 206 into the optical axis L2. This allows a split index to be projected into the fundus image. The split insertion / removal drive motor is also used when removing the split unit 206 into the optical axis L2. This prevents the focus index from being captured in the fundus image. The split unit 206 also has the function of filtering the light emitted from the light source 201 so that the first and second regions each have different illumination characteristics. This will be described in more detail below.

[0034] The unit moving mechanism has a split shift motor, which is used to shift the split unit 206 in the optical axis direction to adjust the focus of the focus index.

[0035] The splitter unit 206 and the focus lens 212 move in conjunction with each other under control of the control unit 20. The two-dimensional image sensor 230 is optically approximately conjugate with the focus index mask. Therefore, moving the splitter unit 206 in the optical axis direction moves the split index on the fundus image captured by the two-dimensional image sensor 230. At the same time, the focus lens 212 moves in conjunction with each other in the optical axis direction. The focus indexes split and projected onto the pupil of the subject's eye E are aligned in the same straight line, bringing the fundus of the subject's eye E into focus. In manual operation, the examiner operates an operation unit (not shown) while checking the focus index projected on the fundus image. The control unit 20 moves the splitter unit 206 and the focus lens 212 in conjunction with each other in accordance with the examiner's operation. In automatic operation, the control unit 20 analyzes the fundus image to detect the position of the focus index and automatically moves the splitter unit 206 and the focus lens 212 in conjunction with each other.

[0036] <Controller configuration> Next, the configuration of the control unit of the fundus camera according to this embodiment will be described with reference to the schematic diagram of Fig. 5. Fig. 5 is a block diagram showing an example of the configuration of the control unit 20. The control unit 20 includes an acquisition unit 21, an image generation unit 22, an image analysis unit 23, a drive control unit 24, and a storage unit 25.

[0037] The acquisition unit 21 can acquire various signals output from the two-dimensional image sensor 230 and the two-dimensional image sensor 240. The acquisition unit 21 can also acquire instructions from an operator via an operation unit (not shown). Furthermore, the acquisition unit 21 can acquire various information such as subject information stored in the storage unit 25, various images such as fundus images, and various images generated by the image generation unit 22.

[0038] The image generating unit 22 can generate an anterior eye observation image based on the output signal of the two-dimensional image sensor 240 acquired by the acquiring unit 21, and can generate a fundus observation image and a fundus photograph image based on the output signal of the two-dimensional image sensor 230. Note that any known method may be used to generate images for ophthalmologists, such as fundus observation images and fundus photograph images, from ophthalmologic information, such as data related to the fundus of the subject's eye E. The image generating unit 22 can also generate a fundus motion image by continuously stitching together the generated fundus observation images in a time series. Furthermore, the image generating unit 22 can also generate a fundus panoramic image by continuously stitching together the generated fundus observation images in a positional manner.

[0039] The image analysis unit 23 can calculate information about the position and shape of the subject's eye E by analyzing the images generated by the image generation unit 22. Furthermore, the image analysis unit 23 can detect changes in the position and state of the subject's eye E by continuously analyzing the images generated by the image generation unit 22.

[0040] The drive control unit 24 controls the driving of various components within the imaging unit 10. Specifically, the drive control unit 24 can control the driving of, for example, the stage unit 110, the face support unit 130, the lens baffle 205, the split unit 206, the focus lens 212, and the like.

[0041] The storage unit 25 can store various types of generated information, various images, and videos. The storage unit 25 can also store identification information of the subject, etc. Furthermore, the storage unit 25 can store programs for imaging, etc.

[0042] Each component of the control unit 20 other than the storage unit 25 may be configured by a software module executed by a processor such as a CPU (Central Processing Unit) or an MPU (Micro Processing Unit). The processor may be, for example, a GPU (Graphical Processing Unit) or an FPGA (Field-Programmable Gate Array). Each component may also be configured by a circuit that performs a specific function, such as an ASIC. The storage unit 25 may be configured by any storage medium, such as an optical disk such as a hard disk, or a memory.

[0043] <Illumination of the subject's eye and miosis> Next, the relationship between illumination of the subject's eye and miosis will be described with reference to FIG.

[0044] A corneal baffle image 300, which is an image of the corneal baffle 208, is formed near the cornea Ec in the anterior part of the subject's eye E, a ring slit image 301, which is an image of the ring slit 204, is formed near the anterior surface (pupil) of the lens E1, and a lens baffle image 302, which is an image of the lens baffle 205, is formed near the posterior surface of the lens E1. The iris Ei is also located near the entire surface of the lens E1. These corneal baffle image 300, ring slit image 301, and lens baffle image 302 prevent reflection of illumination light on the optical surfaces of the subject's eye E (the cornea Ec or lens E1), and illumination light 310, shown by the shaded area in Figure 6(a) that passes through between the corneal baffle image 300, ring slit image 301, and lens baffle image 302, illuminates the fundus 303.

[0045] In such an illumination method, if the subject feels glare, the iris Ei of the subject's eye E constricts, reducing the pupil diameter. When the pupil diameter reduces, illumination light blocking portions 311, which are the mesh portions of illumination light 310 shown in FIG. 6(b), occur, reducing the amount of light (amount of incident light) that reaches the fundus 303. When the amount of incident light decreases, the amount of light reflected from the fundus 303 also decreases, resulting in a dark fundus image generated from the reflected light. Furthermore, the illumination unevenness caused by the illumination light blocking portions 311 results in uneven brightness in the generated fundus image.

[0046] Visible light is more likely to be perceived as dazzling than infrared light, and the subject's eye is more likely to contract, resulting in the state shown in Figure 6(b). Therefore, measures are necessary to ensure good visible light observation.

[0047] Switchable filter control Next, the configuration and control of the split unit 206 according to this embodiment will be described with reference to Fig. 7(a). The split unit 206 has a plurality of masks, each of which is switchable. The split unit 206 is an example of a change unit.

[0048] The split unit 206 comprises a focus index mask 206a and a turret 206b. The focus index mask 206a and the turret 206b can both rotate independently in the directions of the arrows around a fulcrum 206c. The focus index mask 206a forms the outer shape of the focus index. The turret 206b is equipped with filters 206e to 206k for applying illumination light with different characteristics to each region of the fundus. As the focus index mask 206a rotates, the focus index mask 206a is inserted into or removed from the optical axis L2. As the turret 206b rotates, the filter inserted into the optical axis L2 is switched. Note that the shape of the turret 206b is not circular, but rather a notched circle. Since there is no filter in the notched portion, it is also possible to guide the illumination light from the light source 201 directly to the fundus. When the focus index mask 206a is inserted into the optical axis L2, a focus index is projected onto the pupil of the subject's eye E. When the focus index mask 206a is removed from the optical axis L2, the focus index on the pupil is not projected. The colorless portions of the filters 206e to 206k mounted on the turret 206b indicate that they have the property of transmitting light in the visible wavelength band and blocking light in the near-infrared wavelength band. The black portions indicate that they have the property of blocking light in the visible wavelength band and transmitting light in the near-infrared wavelength band. Since the split unit 206 is positioned at a position conjugate with the fundus, it is possible to irradiate two regions of the fundus with illumination light of different properties. In addition, by switching the filter inserted into the optical axis L2 through rotation control of the turret, it is possible to switch the illuminated region and the properties of the illumination light.

[0049] The visible light wavelength band is, for example, 400 nm to 750 nm, and the near-infrared wavelength band is, for example, 750 nm to 1000 nm.

[0050] The transmittance (or light attenuation rate) of the colorless portion of the filter in the visible light wavelength band and the transmittance (or light attenuation rate) of the black portion of the filter in the near-infrared wavelength band may be selected according to the sensitivity of the pixels of the two-dimensional image sensor 230. For example, if the sensitivity of the pixels of the two-dimensional image sensor 230 is high, a bright image can be obtained even with a small amount of light, so a filter with low transmittance (filter with high light attenuation rate) can be selected. For example, if a SPAD sensor is used as the two-dimensional image sensor 230, the transmittance (or light attenuation rate) should be selected according to the sensitivity of the SPAD sensor (the minimum number of photons that can be counted).

[0051] <Visible light observation and visible light photography flow> Next, a flow of visible light observation and visible light photography according to this embodiment will be described with reference to Fig. 8. Fig. 8 is a flowchart showing a series of processes for visible light observation and visible light photography according to this embodiment.

[0052] First, in step S401, the examiner uses the input unit to input the subject information to the control unit 20. Here, it is assumed that the examination starts with this operation.

[0053] Next, in step S402, the image generating unit 22 generates an image for anterior eye observation. More specifically, the control unit 20 turns on the light source 250 for anterior eye observation, the acquisition unit 21 acquires a signal output from the two-dimensional image sensor 240, and the image generating unit 22 generates an image for anterior eye observation based on the acquired signal. The generated image for anterior eye observation is displayed on the display unit 30 and stored in the storage unit 25.

[0054] Next, in step S403, the examiner moves the face support unit 130 and the optical head unit 100 to predetermined positions using the input unit and the operation unit while viewing the anterior eye observation image displayed on the display unit 30. Alternatively, the drive control unit 24 may automatically move the face support unit 130 and the optical head unit 100 to predetermined positions. Furthermore, the examiner may then fine-tune the positions using the input unit and the operation unit.

[0055] Next, in step S404, the examiner determines whether to start visible light observation. The examiner checks the position of the eye to be examined from the anterior eye observation image displayed on the display unit 30, and if the examiner determines that visible light observation is possible, the examiner starts visible light observation using the input unit or operation unit. The control unit 20 detects that an operation to start visible light observation has been performed, and the process proceeds to step S405. If the examiner determines that further position adjustment is necessary, the examiner does not perform an operation to start visible light observation, but performs the operation to adjust the position again. The process returns to step S402.

[0056] Next, in step S405, in order to perform visible light observation, the drive control unit 24 switches the turret 206b of the split unit 206 to a position for visible light observation of the fundus.

[0057] The switching of the turret 206b will be explained using the schematic diagrams of Figure 7(b) and Figure 9. Figure 7(b) shows an example of the arrangement of the split unit 206 for visible light observation, showing a state in which the focus target mask 206b is removed from the optical path L2 and the turret 206b inserts the filter 206e into the optical path L2.

[0058] When observing the fundus 303 of the left eye, focusing on the posterior pole (the deepest part when viewed from the front), the fundus as shown in Figure 9(a) can be seen. The optic disc 700 is located to the left (nasal side) of the center, and the fovea centralis 701 is located opposite the optic disc 700. The optic disc, fovea centralis, and macula can be seen in the right eye, symmetrically to the left eye. The optic disc 700 is a bundle of retinal optic nerve fibers and does not perceive brightness because it does not contain photoreceptors that distinguish color or brightness. In contrast, the macula near the fovea centralis 701 is highly sensitive to brightness because it contains many photoreceptors that distinguish color and light. Therefore, when strong light hits the macula, the subject perceives it as dazzling and contracts their pupils. Therefore, when performing visible light observation, a filter 206e is inserted into the optical path L2. The first region 702 corresponds to the colorless portion of the filter 206e, and therefore visible light is irradiated onto the first region 702. Since the second region 703 including the macula corresponds to the black portion of the filter 206e, the second region 703 is irradiated with infrared light. Since the splitter unit 206 is located conjugate with the fundus, illumination light according to the filter's transmission and absorption characteristics for visible light and infrared light is irradiated onto the fundus. Because the macula is not sensitive to infrared light, glare experienced by the subject is reduced when visible light is not irradiated onto the macula. As a result, miosis of the subject's eye can be suppressed. Furthermore, when the subject's eye is the right eye, by inserting the filter 206k into the optical path L2, infrared light can be irradiated onto the second region including the macula, and visible light can be irradiated onto the other first regions, as in the case of the right eye.

[0059] Note that multiple filter patterns are available. For example, when filter 206f is inserted into optical path L2, the illumination pattern on the fundus is as shown in FIG. 9(b). At this time, visible light is irradiated onto the first region (near the optic disc). Infrared light is irradiated onto the second region (the region including the macula other than near the optic disc). The region near the optic disc is not sensitive to visible light. Therefore, no glare is felt when visible light is irradiated onto this region. Filter 206f is an effective filter when observing the region near the optic disc with visible light. When filter 206(g) is applied, the illumination pattern on the fundus is as shown in FIG. 9(c). Visible light is irradiated onto the nasal side including the optic disc, and infrared light is irradiated onto the temporal side including the macula. When filter 206(g) is applied, the subject's glare is also reduced. Note that the filter pattern (illumination pattern on the fundus) is not limited to the pattern shown in FIG. 9, and any other pattern may be applied.

[0060] Next, in step S406, the control unit 20 turns on the visible light source 201 to perform visible light observation. At this time, the control unit 20 also reduces the light intensity of the visible light source 201 to a light intensity for visible light observation. Because visible light is more likely to cause glare than infrared light, the control unit 20 adjusts the light intensity of the visible light to minimize miosis. Specifically, when the filter applied in step S405 is applied, the control unit 20 adjusts the light intensity of the visible light so that the brightness is such that visible light observation of the fundus is possible.

[0061] Next, in step S407, the image generating unit 22 generates a fundus observation image. More specifically, the acquiring unit 21 acquires a signal output from the two-dimensional image sensor 230, and the image generating unit 22 generates a fundus observation image based on the acquired signal. At this time, a first region of the fundus 303 is illuminated with visible light and a second region of the fundus 303 is illuminated with infrared light according to the filter applied by the split unit 206. The light reflected by the fundus 303 enters the two-dimensional image sensor 230 and is imaged by the two-dimensional image sensor 230. The second region of the image illuminated with infrared light becomes a monochrome image. The first region of the image illuminated with visible light becomes a color image. By combining the first region (color image) and the second region (monochrome image), an image without defects (regions that are dark and therefore invisible) can be obtained as a fundus observation image. The generated fundus observation image is displayed on the display unit 30 and stored in the storage unit 25. The image generating unit 22 generates a fundus moving image based on the continuously generated fundus observation images. The generated fundus moving image is an example of a first image.

[0062] The generated fundus motion image is stored in the storage unit 25. Note that the fundus motion image may be generated using all of the generated fundus observation images, or may be generated by selecting (thinning out) some of the generated fundus observation images. The generated fundus observation images may be processed in some way, such as resizing, smoothing, or alignment, before being generated. For example, a process may be used in which a second monochrome region in the generated fundus observation image is converted into a color image using AI (artificial intelligence), thereby converting the entire image into a color image. The trained model may be generated by machine learning using training data prepared from multiple sets of monochrome fundus images obtained with infrared light and color fundus images obtained with visible light. Alternatively, other general-purpose methods may be used.

[0063] Although the position adjustment of the face rest 130 and the optical head unit 100 is described in step S403, the positions of the face rest 130 and the optical head unit 100 can be adjusted even during visible light observation. This allows the examiner to check the anterior eye observation image and the visible light observation image displayed on the display unit 30, and adjust the positions of the face rest 130 and the optical head unit 100 so that the fundus position to be observed and photographed is displayed on the display unit 30.

[0064] Next, in step S408, the examiner determines whether to end the examination. The examiner performs visible light observation and visible light photography, and if the examiner determines to end the examination, ends the examination using the input unit or operation unit. The examination ends in step S413. If the examiner determines not to end the examination, the examiner does not perform any operation to end the examination. The process proceeds to step S409.

[0065] Next, in step S409, the examiner determines whether to start visible light imaging. The examiner checks the visible light observation image displayed on the display unit 30, and if he or she determines to perform visible light imaging, he or she starts visible light imaging using the input unit or operation unit. The control unit 20 detects that an operation to start visible light imaging has been performed, and the process proceeds to step S410. If the examiner determines that he or she does not yet want to perform visible light imaging, he or she does not perform an operation to start visible light imaging, and the process returns to step S407.

[0066] Next, in step S410, to perform visible light imaging, the drive control unit 24 switches the turret 206b to a position for visible light imaging. More specifically, the drive control unit 24 rotates the turret 206b to the position shown in FIG. 7(a) so that the notch of the turret is positioned in the optical path L2, allowing light to pass through the optical path L2 without passing through a filter. At the same time, the drive control unit 24 also removes the focus index mask 206a from the optical path L2. This allows the illumination light in the optical path L2 to pass through as is without being changed by the split unit 206. As a result, the entire fundus, including the macula, is illuminated with the same illumination light, making it more suitable for visible light imaging.

[0067] Next, in step S411, in order to perform visible light photography, the control unit 20 causes the light source 201 to emit a flash of only visible light. At this time, the control unit 20 also increases the light intensity of the light source 201 for visible light photography. If the subject's eye is miotic, it is difficult for light to reach the fundus 303, so the control unit 20 adjusts the light intensity of the visible light so that it is bright enough to photograph the fundus with visible light.

[0068] Next, in step S412, the image generating unit 22 generates a fundus photographed image. More specifically, the acquiring unit 21 acquires a signal output from the two-dimensional image sensor 230, and the image generating unit 22 generates a fundus photographed image based on the acquired signal. The generated fundus photographed image is a still image and is an example of a second image.

[0069] The generated fundus image is displayed on the display unit 30 and stored in the storage unit 25. When visible light photography is completed, the process returns to step S405.

[0070] Although the examination flow for only one eye has been described here, a flow in which both eyes are photographed consecutively may also be used. In that case, the above flow can be executed for each of the right and left eyes. However, in step S405, different filters must be selected from the turret 206b for the right and left eyes. This is because the macula and optic disc are roughly opposite in the right and left eyes. In FIG. 7(a), 206e, 206f, and 206g are filters for the left eye, and 206k, 206j, and 206i are filters for the right eye. The filters for the left eye and the right eye are symmetrical.

[0071] In this embodiment, the first region is irradiated with visible light and the second region with infrared light. However, if an RGB-IR type two-dimensional image sensor 230 is used, the first region may be irradiated with both visible light and infrared light. The RGB-IR type two-dimensional image sensor 230 can separate and image a mixture of visible and infrared light. In this case, the filter disposed on the turret 206b only needs to block visible light in the region corresponding to the second region, eliminating the need for a wavelength band-selective light-blocking characteristic for the first region, allowing for the use of a less expensive filter. Alternatively, any combination of illumination light types that can reduce glare can be used for irradiating the first and second regions. For example, the first region may be irradiated with white light and the second region with light having a red wavelength. The red wavelength may be, for example, 600 nm to 750 nm. The light irradiated to the second region is not limited to infrared or red light. As long as the light does not include blue light, which is particularly dazzling among visible light, it can reduce glare and suppress miosis more effectively than white light.

[0072] In addition, in this embodiment, a method of changing the illumination light by switching the filter placed in the split unit 206 has been described, but this is not limited to this, and the filter may be placed at any position in the optical system that is approximately conjugate with the fundus 303.

[0073] In this embodiment, the input of the subject information in step S401 also serves to indicate the start of the examination. However, the method for starting the examination is not limited to this, and for example, the start of the examination may be determined by turning on the power of the device. Alternatively, the start of the examination may be determined by providing a dedicated input, different from the subject information, from the input unit to indicate the start of the examination. Furthermore, the end of the previous examination may be determined to be the start of the next examination.

[0074] As described above, the ophthalmologic apparatus according to this embodiment illuminates the fundus of the subject's eye with illumination light having different characteristics (e.g., spectrum) for visible light observation and captures the fundus. For example, visible light is irradiated onto a first region not including the macula, and infrared light is irradiated onto a second region including the macula. This prevents miosis (reducing glare) in the subject's eye. Furthermore, brightness suitable for observation can be obtained, enabling better visible light observation. Furthermore, during fundus examinations, mydriatics are sometimes used to prevent miosis even when dazzling light is applied. However, according to the present disclosure, mydriatics can be suppressed to prevent miosis in the subject's eye or brighten the fundus even if miosis occurs, enabling better visible light observation. This can reduce the amount of mydriatics used or even eliminate the need for mydriatics. Risks associated with the use of mydriatics include headaches, drug allergies, and acute glaucoma attacks, which can be a significant burden on the subject. Therefore, reducing the amount of mydriatics used or eliminating them is a significant benefit.

[0075] [Variation 1] In the method of the first embodiment, for example, a change in the line of sight due to fixational eye movement of the subject's eye may result in visible light being irradiated onto the macular region. When visible light is irradiated onto the macular region, miosis may occur. In the first modification, a method is described in which fundus movement is detected to cause the fundus irradiating light to track the fundus. The following mechanism and control flow are added to the first embodiment.

[0076] <Mechanism> 2 is driven by a motor (not shown) so as to be movable in two-dimensional directions in a plane perpendicular to the optical path L2. The split unit 206 moves in two-dimensional directions relative to the optical path at a fundus conjugate position, thereby enabling free translational movement of the first and second regions on the fundus of the subject's eye.

[0077] <Control flow> After step S407 in FIG. 8, the following steps S451 and S452 are executed in order.

[0078] In step S451, the image analysis unit 23 analyzes and identifies characteristic parts (for example, fundus characteristics and the positions of the optic disc and macula) from the fundus observation image. More specifically, the image analysis unit 23 analyzes the fundus observation image generated in step S407 to analyze and identify fundus characteristics and the positions of the optic disc and macula. The image analysis unit 23 is an example of an identification unit.

[0079] Next, in step S452, based on the analyzed positions of the optic disc and macula, the drive control unit 24 drives the splitter unit 206 in a plane perpendicular to the optical axis L2. More specifically, the drive control unit 24 moves the position of the splitter unit 206 so that the first and second regions on the fundus of the subject's eye move to offset the positional change of the fundus. This operation keeps the macula 702 within the second region even if the position or line of sight of the subject's eye changes, thereby preventing visible light from being irradiated onto the macula. As a result, miosis can be prevented.

[0080] In this embodiment, the method of analyzing the fundus observation image and moving each area of ​​illumination light has been described, but it may also be moved according to the position of the fixation target, for example. Since the line of sight can be roughly determined from the presented position of the fixation target, the positions of the optic disc and macula can be roughly determined from the line of sight.

[0081] [Variation 2] In the first embodiment, the second region including the macula is photographed by irradiating it with infrared light or red light, and therefore the second region including the macula is not a color image. To obtain a color image, for example, a technology that uses AI to colorize the image is known, but this technology has the drawback of requiring extensive learning. In the second modification, a function for obtaining a color image of the second region including the macula using a simpler method will be described.

[0082] The difference between the first embodiment and the second modification is the characteristics of the filter provided on the turret 206b in Figures 7(a) and 7(b). In the first embodiment, the black portion corresponding to the second region is described as having the characteristic of blocking visible light, but in the second modification, a filter having the characteristic of slightly transmitting visible light is used. For example, in the second modification, a filter with a visible light transmittance of 3% is used.

[0083] By using a filter that transmits only a small amount of visible light, the two-dimensional image sensor 230 receives both reflected infrared light and reflected visible light from the second region of the subject's eye. When an RGB-IR type two-dimensional image sensor 230 is used, a monochrome image using infrared light and a color image using weak visible light are obtained as images of the second region. Since the visible light reaching the subject's eye is weak, at approximately 3%, glare and the effects of miosis can be reduced. Obtaining color information using weak visible light is highly effective in obtaining color images. Obtaining color information using weak visible light makes it easy to obtain a color image of the second region, including the macula. The visible light transmittance of 3% is an example and may be appropriately set depending on the intensity of the observation light and the presence or absence of mydriasis. Furthermore, if the color image using weak visible light contains a large amount of noise, it is effective to improve image quality by correcting (reducing noise) the image using an infrared image acquired simultaneously. For example, information obtained from infrared light may be used in any manner, such as extracting contour information from a monochrome image obtained from infrared light and correcting a color image, or extracting color balance from a visible light image and extracting brightness from an infrared image and combining the results. Also, techniques such as binning may be used effectively for color images captured under weak light conditions. Binning is a technique for reducing resolution by averaging the pixel values ​​of multiple pixels. Averaging multiple pixel values ​​can reduce noise. Another effective technique is to combine a noise-reduced image with contour information from an infrared image to improve image quality. Note that the binning process does not necessarily have to be performed by the image generation unit 22. For example, if the two-dimensional image sensor 230 has a binning function, the binning process may be performed using this function. In this embodiment, the image processing described above is performed by the image generation unit 22, for example, in step S407.

[0084] The method described in Modification 2 makes it possible to obtain a color image of the entire observation area, including the second area including the macula, while suppressing the effects on glare and miosis. Note that the method described in Modification 2 (a method for obtaining a color image of the second area including the macula) may be applied not only to fundus observation images (moving images) but also to fundus photographed images (still images).

[0085] [Variation 3] In the first embodiment, when performing visible light photography after fundus observation, the entire fundus, including the macula, is irradiated with visible light in steps S410 and S411. During photography, visible light is irradiated for a short period of time, which can cause miosis. In the third modification, a function for reducing miosis during visible light photography will be described.

[0086] The configuration of the device in the third modification is the same as that in the first embodiment.

[0087] The control flow in the third modification executes steps S470 to S472 shown in Fig. 10 instead of steps S410 to S412 in Fig. 8. These control flows will be described below.

[0088] In step S470, to perform visible light imaging, the drive control unit 24 switches the turret 206b to the position shown in FIG. 7(a) and applies the filter 206g to the light path L2. As described in the first embodiment, the colorless portion of the filter transmits visible light and blocks infrared light. The black portion transmits infrared light and blocks visible light.

[0089] Next, in step S471, in order to perform visible light photography, the control unit 20 causes the light source 201 to simultaneously emit a flash of visible light and infrared light. At this time, the control unit 20 also increases the light intensity of the light source 201 for visible light photography. If the subject's eye is miotic, it is difficult for light to reach the fundus 303, so the amount of visible light is adjusted so that the brightness is sufficient to photograph the fundus with visible light.

[0090] Next, in step S472, the image generation unit 22 generates a fundus photographed image. More specifically, the acquisition unit 21 acquires a signal output from the two-dimensional image sensor 230, and the image generation unit 22 generates a fundus photographed image based on the acquired signal. At this time, a first region of the fundus 303 is irradiated with visible light and a second region is irradiated with infrared light by the filter applied by the split unit 206. The reflected light from the fundus 303 is incident on the two-dimensional image sensor 230 and imaged. An image captured using the filter 206g is shown in FIG. 11(a). A color image is obtained from a region 706 irradiated with visible light, which corresponds to the colorless portion of the filter 206g. A monochrome image is obtained from a region 707 irradiated with infrared light, which corresponds to the black portion of the filter 206g. Here, compared to the first embodiment in which visible light photography is performed by irradiating the entire fundus with visible light, the filter 206g limits the area irradiated with visible light to the first area, and also reduces the absolute amount of visible light irradiated onto the fundus, thereby achieving the effects of reducing glare and miosis. The image photographed using the filter 206g is stored in the storage unit 25.

[0091] Next, in step S473, the drive control unit 24 determines whether a filter corresponding to color photography of the entire fundus has been used. This determination is made as follows. The colorless areas corresponding to the first regions of 206g, 206h, and 206i in FIG. 7(a) are divided into regions so that the three filters, when combined, form the entire fundus. FIGS. 11(a) to 11(c) show fundus images photographed using the filters 206g to 206i, respectively. The light-colored region 706 represents the first region photographed with visible light, and the dark-colored region 707 represents the second region photographed with infrared light. Based on the division of the three filters described above, the regions 706 in (a) to (c) together form the entire fundus. That is, in step S473, it is determined whether fundus photography using each of the filters 206g, 206h, and 206i has been completed. Therefore, for example, when only image capture using 206g has been completed, image capture using filter 206h and image capture using 206i have not been completed, so the flow returns to step S470, switches to a filter that has not been used for image capture, and executes steps S470 to S472 again. If it is determined that image capture using all filters has been completed, the flow proceeds to step S474.

[0092] In step S474, the image analysis unit reads out the images captured with each filter from the memory unit 25 and combines them to generate a full-color fundus image. At this time, the image of the second region captured with infrared light is used to align the images. If only the first region is used, there is no overlapping area between the images, making alignment difficult. However, by using the second region, an overlapping area between the images can be obtained, making alignment easier. The generated fundus image is displayed on the display unit 30 and saved in the memory unit 25. When visible light imaging is complete, the process returns to step S405.

[0093] As shown in (a) to (c) of Figure 11, by capturing images of separate regions, the amount of visible light irradiated per capture and the area can be reduced, thereby reducing glare. Furthermore, alignment can be easily performed by using an image of the second region captured with infrared light. If similar imaging and alignment were performed using only visible light, the overlapping region for alignment would need to be captured with visible light, which would increase the amount of visible light irradiated and the area irradiated by the overlapping region. Therefore, Variation 3, in which illumination light with different characteristics is irradiated on the first and second regions, has the effect of reducing glare.

[0094] The number of divisions and the division shape of the region are not limited to those shown in Modification 3, and any number of divisions and any division shape can be applied.

[0095] [Embodiment 2] In the first embodiment, an embodiment of a fundus camera to which the present disclosure is applied has been described. In the present embodiment, an example in which the present disclosure is applied to a scanning laser ophthalmoscope (SLO; hereinafter referred to as an SLO device) will be described in detail.

[0096] <Outline of the device> The schematic configuration of the SLO device according to this embodiment is the same as that of the first embodiment shown in FIG. 1, and a detailed description thereof will be omitted.

[0097] <Optical configuration of the device> Next, the optical configuration of the SLO device according to this embodiment will be described with reference to the schematic diagram of Fig. 12. Fig. 12 is a schematic diagram showing an example of the optical configuration of the optical head unit 100.

[0098] An SLO optical system is arranged in the optical head unit 100. A dichroic mirror 512 and a beam splitter 510 are arranged on the optical axis of an objective lens 511 arranged to face the subject's eye E. These optical components cause the optical axis of the objective lens 511 to branch into an SLO optical path L12, an anterior-segment observation optical path L13, and a fixation lamp optical path L14. The SLO optical path L12 is an optical path for capturing a frontal image of the fundus, the anterior-segment observation optical path L13 is an optical path for observing the anterior segment, and the fixation lamp optical path L14 is an optical path for presenting a fixation lamp to encourage the subject's eye E to fixate.

[0099] The dichroic mirror 512 branches an anterior-eye-segment observation optical path L13 in the reflection direction from the optical axis of the objective lens 511 according to the wavelength band of each light ray. The beam splitter 510 branches a fixation lamp optical path L14 in the reflection direction from the optical axis of the objective lens 511 according to the wavelength band, and branches an SLO optical path L12 in the transmission direction. Note that the optical paths provided in the transmission direction and reflection direction of each dichroic mirror etc. may be reversed.

[0100] The SLO optical path L12 includes an SLO scanning means 514, a focus lens 515, and a lens 516, which are shared by an SLO scanning optical system for scanning the interior of the subject's eye while irradiating it with SLO measurement light, and a light receiving optical system for receiving return light from the subject's eye E. A partial reflection mirror 517 is provided at a position conjugate with the subject's eye pupil behind the lens 516 (in the opposite direction on the optical path to the objective lens 511 with respect to the lens 516). The partial reflection mirror 517 reflects the SLO measurement light emitted from the SLO measurement light source 521 at the center of the optical axis and transmits return light from the subject's eye E in other regions. The partial reflection mirror 517 separates the SLO measurement light and the return light in the form of a beam splitter.

[0101] The system extending from the SLO measurement light source 521 provided in the reflected light path of the partial reflection mirror 517 to the objective lens 511 as described above is the SLO scanning optical system. The SLO measurement light is scanned over the fundus of the subject's eye by the SLO scanning optical system. On the other hand, the system extending from the objective lens 511 to the SLO photodiode 520 provided in the transmitted light path of the partial reflection mirror 517 is the SLO light receiving optical system. The returned light from the subject's eye E guided to the SLO photodiode 520 by the SLO light receiving optical system is transmitted to the control unit 20 as an SLO light receiving signal.

[0102] The SLO scanning means 514, which is shared by the SLO scanning optical system and the light receiving optical system, two-dimensionally scans the fundus of the subject's eye with SLO measurement light emitted from an SLO measurement light source 521. The SLO scanning means 514 is also used to guide return light from each scanning position to the SLO photodiode 520. The SLO scanning means 514 is composed of an X scanner that scans the SLO measurement light in the X direction and a Y scanner that scans in the Y direction. In this embodiment, the X scanner uses a polygon mirror because high-speed scanning is required, and the Y scanner uses a galvanometer mirror because low-speed scanning is sufficient.

[0103] The focus lens 515 is driven by a motor (not shown) in the direction indicated by the arrow in the figure for focus adjustment. The SLO measurement light source 521 is a light source that combines and emits lasers of four different wavelengths, for example, blue, green, red, and infrared, and the output laser wavelength can be selected from among the four and is controlled by the control unit 20. The center wavelength of the laser light emitted from the infrared light source is set to be around 780 nm.

[0104] The dichroic mirror 512 has the property of reflecting light in a wavelength band around 970 nm and transmitting light with wavelengths shorter than that. A lens 522, a split prism 523, a lens 524, and an anterior-segment observation CCD 525 are arranged on an anterior-segment observation optical path L13 formed by the dichroic mirror 512. The CCD 525 captures an image of the anterior segment of the subject's eye illuminated by an anterior-segment observation light source (wavelength 970 nm), not shown. The split prism 523 is arranged on the anterior-segment observation optical path L13 so as to be conjugate with the pupil of the subject's eye E when the distance between the subject's eye E and the optical head unit 100 in the Z direction (front-back direction) is appropriate. This allows the CCD 525 to capture an unsplit image of the subject's eye's pupil when the distance between the optical head unit 100 in the Z direction (front-back direction) is appropriate. Furthermore, when the distance in the Z direction is inappropriate, the CCD 525 can capture an image of the pupil of the subject's eye E split in the deflection direction of the split prism. The output signal of the CCD 525 is sent to the control unit 20, and the control unit 20 detects the relative position between the subject's eye E and the optical head unit 100 based on the signal received from the CCD 525.

[0105] A lens 518 and a fixation lamp panel 519 are provided on a fixation lamp optical path L14 formed in the reflection direction of a beam splitter 510 made of, for example, plain glass. The fixation lamp panel 519 is, for example, a high-brightness organic EL panel, and is controlled by the control unit 20 to display various patterns selected by the examiner at desired positions. A visible image of this pattern is presented to the subject's eye E, and acts as a fixation lamp to encourage the subject to fixate.

[0106] The optical head unit 100 is provided with an alignment mechanism that moves the entire optical head unit 100 in three dimensions (X, Y, Z) to align it with the subject's eye E. The control unit 20 drives this alignment mechanism using three motors (not shown) based on relative position information between the subject's eye E and the optical head unit 100 obtained from the video signal from the CCD 525, to perform the alignment operation.

[0107] <Control device description> Next, a description will be given of the control unit 20. The block diagram showing the control configuration of the control unit 20 is the same as that of the first embodiment. That is, the block diagram showing the control configuration of the control unit 20 is shown in FIG.

[0108] In this embodiment, for example, the image generation unit 22 functions as an image generation means that generates an image using a light reception signal, etc., which will be described later. In this embodiment, for example, the memory unit 25 functions as a memory means that stores scanning information, light reception signals, images generated by the image generation unit 22, etc. In this embodiment, for example, the drive control unit 24 functions as a control means that controls the optical head unit 100, the image generation unit 22, and the memory unit 25. In this embodiment, for example, the processing unit 23 analyzes control information from the drive control unit 24 and images (data) generated by the image generation unit 22 to generate necessary information. In this embodiment, for example, the acquisition unit 21 functions as an acquisition means that acquires necessary information from the processing unit 23, the optical head unit 100, and the display unit 30.

[0109] Next, the actual basic operation of each component will be described using the generation of an SLO image as an example. In a method for generating a frontal fundus (SLO) moving image, the drive control unit 24 turns on the SLO measurement light source 521 and then sends a scanning control signal, which is scanning information, to the SLO scanning means 514 to start scanning with the SLO measurement light. The returned light from the fundus of the subject's eye is converted into a light-receiving signal by the SLO photodiode 520. The acquisition unit 21 samples this light-receiving signal and sequentially stores it in the memory unit 25 as pixel values ​​of pixels corresponding to each scanning position, which is scanning information, to generate a single piece of frontal fundus image data. A still image can be displayed by reading this image data and displaying it on the display unit 30. Furthermore, by repeatedly performing this series of controls and continuously displaying the sequentially obtained still images in chronological order, a frontal fundus moving image can be displayed. Furthermore, while this frontal fundus moving image is being generated, the processing unit 23 can detect the focus state by analyzing image data at different positions of the focus lens 515. The drive control unit 24 controls the position of the focus lens 515 based on the result of detecting the focus state, thereby realizing adjustment control of the device such as SLO autofocus adjustment.

[0110] Also, by switching the wavelength range of the SLO measurement light emitted from the SLO measurement light source 521, it becomes possible to generate and save monochrome still images, monochrome moving images, color still images, and color moving images, and these images can be appropriately selected according to the use of the images. For example, in the preview state before this imaging, it is desirable to select a monochrome moving image using only the infrared wavelength. Also, for fundus diagnosis, it is desirable to exclusively and sequentially output each wavelength range of blue, green, and red to acquire image data of each color, synthesize these to generate a color still image, and display this. Note that the selection of the image to be generated may be performed by the apparatus or may be made possible for the operator to perform.

[0111] In the ophthalmic imaging apparatus described above, a series of processes from the observation of the subject eye E to imaging and the saving of the captured image will be described using the flowcharts of FIGS. 13(a) and (b). FIG. 13(a) shows the main processes executed during the examination. FIG. 13(b) shows the detailed processes of preview and apparatus adjustment executed in step S303 in FIG. 13(a) in color SLO imaging.

[0112] <S301 Patient Selection> First, in step S301, the examiner inputs subject information to the control unit 20 through the input unit. Here, it is assumed that the examination is started by this input.

[0113] <S302 Mode Selection> Next, in step S302, the control unit 20 initializes the optical head unit 100. That is, the control unit 20 sets the center of the fixation lamp panel 519 to be lit so that the line-of-sight direction of the subject eye E is parallel to the optical axis of the objective lens 511 of the optical head unit 100 with respect to the fixation lamp panel 519. Also, the control unit 20 sets the focus lens 515 and the focus lens 527 to the position for emmetropia, that is, the focus lens position (OD position) corresponding to a subject eye of 0 diopter. Here, the diopter is a value indicating the refractive power abnormality of the subject eye corresponding to myopia or hyperopia, and 0 diopter is the standard refractive power without refractive power abnormality.

[0114] <S303 Preview and Device Adjustment> Next, the examiner makes various adjustments to the device while achieving the preview state. The details of the adjustments performed during color SLO imaging will be described with reference to the flowchart shown in Fig. 13(b).

[0115] <S311 Manual Alignment> While looking at the pre-eye observation image displayed on the display unit 30, the examiner moves the face receiving unit 130 and the optical head unit 100 to predetermined positions using the input unit and the operation unit. This adjustment may be made by separately providing an operation button on the screen, or by taking a method of designating a point on the screen where the examiner wants to position it at the center of the window using a mouse or the like. Furthermore, the adjustment in the optical axis (Z) direction between the optical head unit 100 and the examined eye E can be performed, for example, by operating the mouse wheel. When a part of the pupil comes to a position where it is imaged, the examiner instructs the control unit 20 to start auto-alignment using the input unit and the operation unit.

[0116] <S312 Rough Auto-Alignment> When auto-alignment is started, the image generation unit 22, the drive control unit 24, the image analysis unit 23, and the acquisition unit 21 in the control unit 20 start auto-alignment in cooperation. First, the image analysis unit 23 analyzes the pre-eye moving image acquired by the acquisition unit 21 to obtain the pupil center of the examined eye E. The stage is driven so that this pupil center approaches the center of the pre-eye moving image that coincides with the optical axis of the optical head unit 100, and the position adjustment in the XY direction of the optical head unit 100 is performed. Then, based on, for example, the interval between the corneal reflection images of a plurality of pre-eye illumination light sources (not shown), the position adjustment in the optical axis (Z) direction between the optical head unit 100 and the examined eye E is performed. The adjustments of the two may be performed alternately and continuously, or may be performed in parallel. When the position of the optical head unit 100 falls within a predetermined allowable range, the control unit 20 shifts the flow to step S313.

[0117] <S313 Fine Auto-Alignment> In step S313, the drive control unit 24 instructs the SLO measurement light source 521 to emit only infrared light, drives the SLO scanning means 514, and starts shooting (previewing) an SLO moving image. When rough auto-alignment adjustment is performed, the edge of the test eye pupil in the anterior eye image becomes sharp. Also, as described above, the split pupil split by the split prism 523 provided on the anterior eye observation optical path L13 can be clearly observed. The drive control unit 24 drives the stage to adjust the position of the optical head unit 100 in the XY direction closer to the center of the anterior eye moving image, and adjusts the position of the optical head unit 100 in the Z direction so that the split amount of the split pupil becomes zero. When it is confirmed as a result of fine auto-alignment that the misalignment is within a predetermined range, the control unit 20 shifts the flow to step S314.

[0118] <S314 Auto Focus> In step S314, when it is confirmed that an appropriate SLO moving image is acquired, auto focus adjustment is started. In the present embodiment, the characteristics of confocal SLO in which the output of the SLO photodiode 520, that is, the light reception signal, becomes maximum when the fundus is correctly focused on the retina are utilized. Then, by monitoring the light reception signal while driving the focus lens 515, so-called hill-climbing AF type auto focus for determining the focus position is performed. Of course, for this adjustment, sharpness as an image may be used instead of the magnitude of the light reception signal. With the above, the adjustment of the apparatus in the preview state in S303 is completed, and the control unit 20 shifts the flow to step S304 in FIG. 13(a).

[0119] <S304 Visible Light Fundus Observation> When the adjustment of the apparatus in the preview state is completed, the drive control unit 24 instructs the SLO measurement light source 521 to emit a light emission pattern for visible light observation with reduced glare instead of infrared light. The light emission pattern will be described using FIG. 14. <I

[0120] In Figure 14, 701 and 702 represent the optic disc and macular region, respectively, as in Figure 9 and elsewhere. Three types of arrows 711, 712, and 713, each spaced apart by dashed lines, represent the red, green, and blue laser scanning trajectories, respectively, and solid arrow 714 represents the infrared laser scanning trajectory. A dashed circle 710 represents the area around the macular region. The area outside the circle is the first region, illuminated with red, green, and blue visible light, and the area inside the circle is the second region, illuminated with infrared light. To achieve this illumination, the drive controller 24 controls the SLO measurement light source 521 to sequentially switch between red, green, blue, and infrared light emissions in synchronization with the scanning of the SLO scanning means 514. Because the human eye is not sensitive to infrared light, the macular region is not illuminated with visible light, reducing glare to the subject and preventing miosis.

[0121] When acquiring a signal, the acquisition unit 21 synchronizes the output signal of the SLO photodiode 520 with the type of laser light emitted by the SLO measurement light source 521, thereby distinguishing and acquiring image data for each of the red, green, blue, and infrared colors. The image generation unit 22 combines these to generate a color image. Although the second region, the periphery of the macula, which is irradiated only with infrared light, becomes a monochrome image, by combining this with the first region, which becomes a color image, an image without any defects can be obtained across the entire effective angle of view of the SLO device. The generated fundus observation image is displayed on the display unit 30. The image generation unit 22 also generates successive fundus observation images and displays them sequentially on the display unit 30 to generate a fundus motion image. The generated fundus motion image can also be stored in the memory unit 25 by the examiner's operation.

[0122] Note that the combination of the characteristics of the illumination light irradiated to each of the first region and the second region is not limited to this, and any combination such as the entire visible light range and only red light, or a combination of three pseudo-color lights of infrared, green, and blue and infrared light can be applied. Similarly, the shapes of the first region and the second region are not limited to this, and any other arbitrary shape can be set. Also, it is effective to switch the regions according to the left and right eyes, move each region according to the visual target pattern displayed on the fixation lamp panel 519, or detect the movement of the fundus such as fixation micro-movement and track the position of each region to the fundus position. A UI (User Interface) that can set a combination of characteristics of these plurality of illumination lights, region shapes, linkage with the fixation lamp, and switching between enabling and disabling the tracking function may be displayed on the display unit 30, or a switch or button for switching may be implemented in the imaging unit 10.

[0123] <S305 Imaging & Confirmation> When visible light fundus observation is completed and the examiner instructs imaging using the input unit or the operation unit, the drive control unit 24 instructs the SLO measurement light source 521 to sequentially output light in each wavelength region of blue, green, and red exclusively instead of infrared light. The output of each laser at this time is set to a higher light intensity than during visible light observation. The acquisition unit 21 acquires image data of each color from the output of the SLO photodiode 520, and the image generation unit 22 synthesizes this to generate a color image. The generated color image is displayed on the display unit 30 by the drive control unit 24 for the examiner to confirm. When the examiner instructs to save the displayed image, it is saved in the storage unit 25 by using the input unit or the operation unit to give the save instruction. Also, when re-imaging is required, by giving a re-imaging instruction in the same way, the flow returns to step S303 and is executed again from alignment.

[0124] As described above, in the ophthalmic device according to this embodiment, when performing visible light observation, illumination light (laser light) with different characteristics is irradiated to the first region and the second region. As a result, it is possible to reduce the glare felt by the subject while acquiring an image of the entire effective picture angle of the device, and suppress the miosis of the examined eye (reduce the glare). Also, since an appropriate brightness for observation can be obtained, better visible light observation can be performed.

[0125] In this embodiment, the second region including the macula is irradiated with infrared light. However, a method of irradiating the second region with a weaker visible light laser is also effective. In this case, the output of the SLO measurement light source 521 itself may be reduced. Alternatively, as shown in FIG. 15(a), a method of partially turning off the laser in the second region around the macula to reduce the number of scans and reduce the amount of light per unit area is also effective. In this case, an infrared image can be acquired by scanning the thinned scan lines using infrared light instead, as shown in FIG. 15(b). When the image generator 22 generates an image of the second region, a method can be applied, such as contour correction of an image generated from a thinned visible light scan using an image obtained by an infrared light scan. Since a fundus image can be generated based on more information, image quality can be improved. In addition to thinning the number of scans, the scan speed of only the second region can also be increased. In this embodiment, a polygon mirror is used as the X-scanner, which makes it impossible to change the speed. However, if a MEMS mirror or a galvanometer scanner is used, the speed can be changed.

[0126] Although the present embodiment does not specifically describe light intensity control of the fixation light panel 519, additional control suitable for visible light observation may be performed. For example, even when a second region including the macula is irradiated with weakened visible light, the observation light is too bright during visible light observation, making the fixation light difficult to see. To address this issue, control may be performed to increase the light intensity of the fixation light panel 519 during visible light observation. Conversely, the light intensity of the fixation light panel 519 may be reduced or turned off during visible light observation. For example, in the visible light and infrared light irradiation pattern shown in FIG. 14 , the region 701 irradiated with infrared light appears as a black region to the subject. To encourage the subject to align the macula, which is the center of the visual field, with this region, the indicator displayed on the fixation light panel 519 is displayed so that it overlaps with the region 701. If the indicator is too bright, this can cause miosis in the subject's eye. Therefore, reducing the light intensity of the fixation light panel 519 is effective. Alternatively, since the subject sees area 701 as a black area, it may be used in place of a fixation light, and fixation light panel 519 may be turned off. As a result, it is possible to reduce the glare of the fixation light itself, and also to reduce the phenomenon in which the image of the fixation light reflected by the fundus is captured in the captured image.

[0127] Furthermore, although the present embodiment is configured to receive light using a single SLO photodiode 520, a configuration may also be adopted in which a dichroic mirror 530 is disposed to receive infrared light and visible light separately, as shown in Fig. 16. In Fig. 16, dichroic mirror 530 has the property of reflecting infrared light and transmitting visible light, and of the returned light, the infrared light reflected by dichroic mirror 530 is received by SLO photodiode 520a, and the visible light is received by SLO photodiode 520b. This light receiving method allows infrared light and visible light to be acquired simultaneously, so that while scanning the second region with the same infrared light as in Fig. 14 to acquire an infrared image, it is also possible to acquire a visible light image with the aforementioned visible light laser weakened.

[0128] As described above, the function described in Modification 2 of Embodiment 1 can also be realized in an SLO device. Furthermore, in Embodiment 2, the intensity balance for each wavelength in the first and second regions can be easily changed simply by adjusting the laser output power. For example, an irradiation method may be used in which visible light is irradiated to both the first and second regions, while the blue light, which is perceived as dazzling, is attenuated in the second region. Alternatively, an irradiation method may be used in which the amount of red light in the second region is the same as the amount of red light in the first region, while wavelength components other than red light are attenuated in the second region. Alternatively, both infrared light and visible light may be irradiated to both the first and second regions, while the illumination light in the visible light wavelength band is attenuated only in the second region. In Embodiment 1, when attenuating a specific wavelength component (when adjusting the intensity balance for each wavelength), it is desirable to use a filter whose transmission characteristics can be dynamically changed, such as a liquid crystal filter, rather than a fixed filter.

[0129] (Other embodiments) The disclosed technology can also be realized by executing the following process. That is, the disclosed technology can also be realized by supplying software (programs) that realize one or more functions of the various embodiments described above to a system or device via a network or a storage medium, and having a computer (or a CPU, MPU, or the like) of the system or device read and execute the programs. The computer has one or more processors or circuits, and may include multiple separate computers or a network of multiple separate processors or circuits to read and execute computer-executable instructions. In this case, the processor or circuit may include a central processing unit (CPU), a microprocessing unit (MPU), a graphics processing unit (GPU), an application-specific integrated circuit (ASIC), or a field-programmable gateway (FPGA). The processor or circuit may also include a digital signal processor (DSP), a data flow processor (DFP), or a neural processing unit (NPU).

[0130] (Configuration 1) An ophthalmic apparatus for photographing an eye to be examined by illuminating the eye with illumination light, When capturing a first image of the subject's eye, a first region of the subject's eye is illuminated with first illumination light having a first spectrum, and a second region different from the first region, the second region including the macula, is illuminated with second illumination light having a second spectrum having a second peak wavelength longer than the first peak wavelength of the first spectrum; an ophthalmologic apparatus comprising an illumination unit that illuminates the subject's eye with the first illumination light when capturing a second image of the subject's eye;

[0131] (Configuration 2) 2. The ophthalmologic apparatus according to claim 1, wherein the first image is a moving image used to observe a fundus, and the second image is a still image used to photograph the fundus.

[0132] (Configuration 3) 3. The ophthalmologic apparatus according to claim 1, wherein the second peak wavelength is in a red wavelength band or an infrared wavelength band.

[0133] (Configuration 4) the first illumination light is visible light; 4. The ophthalmologic apparatus according to any one of configurations 1 to 3, wherein the second illumination light is infrared light.

[0134] (Configuration 5) a light receiving unit that receives light reflected from the subject's eye; an image generating unit that generates an image according to the reflected light received by the light receiving unit; Further provided with An ophthalmic device according to any one of configurations 1 to 4, wherein the image generating unit generates the first image or the second image as a color image using an image corresponding to first reflected light corresponding to the first illumination light and an image corresponding to second reflected light corresponding to the second illumination light.

[0135] (Configuration 6) The ophthalmic apparatus of configuration 5, wherein the image generating unit generates a color image having reduced noise from a color image corresponding to visible light contained in the second reflected light and a monochrome image corresponding to infrared light contained in the second reflected light.

[0136] (Configuration 7) The ophthalmic device of either of configurations 5 or 6, wherein the image generation unit generates a color image with reduced noise compared to the color image corresponding to the visible light contained in the second reflected light, using an image with reduced resolution of the color image corresponding to the visible light contained in the second reflected light and a contour extracted from a monochrome image corresponding to the infrared light contained in the second reflected light.

[0137] (Configuration 8) An ophthalmic device according to any one of configurations 5 to 7, wherein the image generation unit generates the first image or the second image as a color image by inputting an image corresponding to first reflected light corresponding to the first illumination light and an image corresponding to second reflected light corresponding to the second illumination light into a trained model.

[0138] (Configuration 9) An ophthalmic device according to any one of configurations 5 to 8, wherein the image generation unit acquires a plurality of images in which the positions of the first region and the second region are different, aligns each of the plurality of images using the second region of each of the plurality of images, and generates an image in which the first region of each of the aligned images is synthesized.

[0139] (Configuration 10) the illumination light is laser light, The lighting means When capturing a first image of the subject's eye, a first region of the subject's eye is scanned with a first laser light having a first spectrum, and a second region different from the first region, the second region including a macula, is scanned with a second laser light having a second spectrum having a second peak wavelength longer than the first peak wavelength of the first spectrum; 10. The ophthalmologic apparatus according to any one of configurations 1 to 9, wherein the eye to be examined is scanned with the first laser light when a second image of the eye to be examined is captured.

[0140] (Configuration 11) the illumination means has a change means for changing the position or shape of the first area and the position or shape of the second area; An ophthalmologic apparatus according to any one of configurations 1 to 10, wherein the change means changes at least one of the position or shape of the first area and the position or shape of the second area depending on whether the subject eye is a left eye or a right eye.

[0141] (Configuration 12) further comprising an identifying unit that identifies a characteristic portion of the subject's eye from the first image, 12. The ophthalmologic apparatus according to any one of configurations 1 to 11, wherein the illumination means changes the position or shape of the first region and the position or shape of the second region based on the position of the identified characteristic portion.

[0142] (Configuration 13) 13. The ophthalmologic apparatus according to any one of configurations 1 to 12, wherein the illumination means changes at least one of the position or shape of the first area and the position or shape of the second area in response to an operation by an operator.

[0143] (Configuration 14) a fixation target indicating a target position of the line of sight of the subject's eye; An ophthalmic device according to any one of configurations 1 to 13, wherein the illumination means changes at least one of the position or shape of the first area and the position or shape of the second area based on the target position displayed by the fixation target.

[0144] (Configuration 15) 15. The ophthalmologic apparatus according to configuration 14, wherein the illumination means changes the position or shape of the second area so that the position of the fixation target and the second area overlap.

[0145] (Method 1) 1. A control method for an ophthalmic apparatus that photographs an eye to be examined by illuminating the eye with illumination light, comprising: When capturing a first image of the subject's eye, a first region of the subject's eye is illuminated with first illumination light having a first spectrum, and a second region different from the first region, the second region including the macula, is illuminated with second illumination light having a second spectrum having a second peak wavelength longer than the first peak wavelength of the first spectrum; A control method for an ophthalmologic apparatus, comprising an illumination step of illuminating the subject's eye with the first illumination light when capturing a second image of the subject's eye.

[0146] (Program 1) A program that causes a computer to execute the method for controlling an ophthalmologic apparatus according to Method 1.

[0147] (Configuration 16) An ophthalmic apparatus for photographing an eye to be examined by illuminating the eye with illumination light, an imaging element that outputs an image according to the number of photons of incident light; an illumination means having a filter selected based on the sensitivity of the image sensor, the filter attenuating the illumination light; An ophthalmic device having

[0148] (Configuration 17) An ophthalmic apparatus for photographing an eye to be examined by illuminating the eye with illumination light, An ophthalmic apparatus comprising: an illumination means for irradiating a region including the macula with first illumination light of a first spectrum having a first peak wavelength when capturing a still image of the test eye; and for irradiating a region including the macula with second illumination light of a second spectrum having a second peak wavelength longer than the first peak wavelength when capturing a moving image of the test eye.

[0149] (Configuration 18) An ophthalmic apparatus for photographing an eye to be examined by illuminating the eye with illumination light, An ophthalmic apparatus comprising: an illumination means for illuminating a first region of the subject's eye with first illumination light having a first spectrum, and illuminating a second region different from the first region, the second region including the macula, with second illumination light having a second spectrum having a second peak wavelength longer than the first peak wavelength of the first spectrum, when capturing a first image of the subject's eye. [Explanation of symbols]

[0150] 10. Photography Department 20 Control Unit 30 Display section 100 Optical head unit 110 Stage Section 120 base 130 Face support

Claims

1. An ophthalmic apparatus for photographing an eye to be examined by illuminating the eye with illumination light, When capturing a first image of the subject's eye, a first region of the subject's eye is illuminated with first illumination light having a first spectrum, and a second region different from the first region, the second region including a macula, is illuminated with second illumination light having a second spectrum having a second peak wavelength longer than the first peak wavelength of the first spectrum; an ophthalmologic apparatus including an illumination unit that illuminates the subject's eye with the first illumination light when capturing a second image of the subject's eye;

2. 2. The ophthalmologic apparatus according to claim 1, wherein the first image is a moving image used for observing the fundus, and the second image is a still image used for photographing the fundus.

3. The ophthalmic apparatus according to claim 1 , wherein the second peak wavelength is in a red wavelength band or an infrared wavelength band.

4. the first illumination light is visible light; The ophthalmic apparatus according to claim 1 , wherein the second illumination light is infrared light.

5. a light receiving unit that receives light reflected from the subject's eye; an image generating unit that generates an image according to the reflected light received by the light receiving unit; Further provided with 2. The ophthalmologic apparatus according to claim 1, wherein the image generating unit generates the first image or the second image as a color image using an image corresponding to first reflected light corresponding to the first illumination light and an image corresponding to second reflected light corresponding to the second illumination light.

6. 6. The ophthalmic apparatus according to claim 5, wherein the image generating unit generates a color image having reduced noise compared to the color image using a color image corresponding to visible light contained in the second reflected light and a monochrome image corresponding to infrared light contained in the second reflected light.

7. 6. The ophthalmologic apparatus according to claim 5, wherein the image generating unit generates a color image having reduced noise compared to the color image corresponding to the visible light contained in the second reflected light, using an image with reduced resolution of the color image corresponding to the visible light contained in the second reflected light and a contour extracted from a monochrome image corresponding to the infrared light contained in the second reflected light.

8. The ophthalmologic apparatus of claim 5, wherein the image generation unit generates the first image or the second image as a color image by inputting an image corresponding to first reflected light corresponding to the first illumination light and an image corresponding to second reflected light corresponding to the second illumination light into a trained model.

9. The ophthalmologic apparatus of claim 5, wherein the image generation unit acquires a plurality of images in which the positions of the first region and the second region are different, aligns each of the plurality of images using the second region of each of the plurality of images, and generates an image in which the first region of each of the aligned images is combined.

10. the illumination light is laser light, The lighting means When capturing a first image of the subject's eye, a first region of the subject's eye is scanned with a first laser light having a first spectrum, and a second region different from the first region, the second region including a macula, is scanned with a second laser light having a second spectrum having a second peak wavelength longer than the first peak wavelength of the first spectrum; 2. The ophthalmologic apparatus according to claim 1, wherein the eye is scanned with the first laser light when the second image of the eye is captured.

11. the illumination means has a change means for changing the position or shape of the first area and the position or shape of the second area; 2. The ophthalmologic apparatus according to claim 1, wherein the change unit changes at least one of the position or shape of the first region and the position or shape of the second region depending on whether the subject's eye is a left eye or a right eye.

12. an identifying unit that identifies a characteristic portion of the subject's eye from the first image; The ophthalmologic apparatus according to claim 1 , wherein the illumination means changes the position or shape of the first region and the position or shape of the second region based on the position of the identified characteristic portion.

13. 2. The ophthalmologic apparatus according to claim 1, wherein the illumination means changes at least one of the position or shape of the first area and the position or shape of the second area in response to an operation by an operator.

14. a fixation target indicating a target position of the line of sight of the subject's eye; 2. The ophthalmologic apparatus according to claim 1, wherein the illumination means changes at least one of the position or shape of the first area and the position or shape of the second area based on the target position displayed by the fixation target.

15. The ophthalmologic apparatus according to claim 14 , wherein the illumination means changes the position or shape of the second region so that the position of the fixation target and the second region overlap.

16. 1. A control method for an ophthalmic apparatus that photographs an eye to be examined by illuminating the eye with illumination light, comprising: When capturing a first image of the subject's eye, a first region of the subject's eye is illuminated with first illumination light having a first spectrum, and a second region different from the first region, the second region including a macula, is illuminated with second illumination light having a second spectrum having a second peak wavelength longer than the first peak wavelength of the first spectrum; A control method for an ophthalmologic apparatus, comprising: an illumination step of illuminating the subject's eye with the first illumination light when capturing a second image of the subject's eye.

17. A program that causes a computer to execute the method for controlling an ophthalmologic apparatus according to claim 16.

18. An ophthalmic apparatus for photographing an eye to be examined by illuminating the eye with illumination light, an imaging element that outputs an image according to the number of photons of incident light; an illumination means having a filter selected based on the sensitivity of the image sensor, the filter attenuating the illumination light; An ophthalmic device having

19. An ophthalmic apparatus for photographing an eye to be examined by illuminating the eye with illumination light, an ophthalmic apparatus comprising: an illumination means for irradiating a region including the macula with first illumination light of a first spectrum having a first peak wavelength when capturing a still image of the test eye; and for irradiating a region including the macula with second illumination light of a second spectrum having a second peak wavelength longer than the first peak wavelength when capturing a moving image of the test eye.

20. An ophthalmic apparatus for photographing an eye to be examined by illuminating the eye with illumination light, An ophthalmic apparatus comprising: an illumination means for illuminating a first region of the subject's eye with first illumination light having a first spectrum, and illuminating a second region, different from the first region and including the macula, with second illumination light having a second spectrum having a second peak wavelength longer than the first peak wavelength of the first spectrum, when capturing a first image of the subject's eye.

Images