Ophthalmologic apparatus, and control method of ophthalmologic apparatus and program

Abstract

To provide a fixation target for guiding the direction of a subject eye with a simple constitution.SOLUTION: An ophthalmologic apparatus includes an imaging part (14) containing an optical scanner for irradiating a subject eye with imaging light, a fixation part (29) including a fixation light scanner for projecting a fixation target onto the subject eye via the optical scanner, and a control part (16) for driving the optical scanner and the fixation light scanner so that the fixation target is continuously projected to a first position of the subject eye, and that a first area of the subject eye is scanned with imaging light.SELECTED DRAWING: Figure 2

Description

Technical Field

[0001] The present invention relates to an ophthalmic device, a control method for an ophthalmic device, and a program.

Background Art

[0002] Patent Document 1 discloses an ophthalmic imaging device that provides a fixation target to an eye to be examined by providing a plurality of light sources as fixation targets and switching the light source to any one of the plurality of light sources and directing the fixation target toward the eye to be examined. However, there are limitations on the installation location of the fixation optical system for presenting the fixation target.

Prior Art Documents

Patent Documents

[0003]

Patent Document 1

Summary of the Invention

[0004] The first aspect of the technology of the present disclosure is a scanning optical system that scans an eye to be examined with light from a light source, a fixation light source that irradiates the eye to be examined with fixation light through the scanning optical system and functions as a fixation target, a fixation light scanning unit that scans the fixation light in synchronization with the scanning of the scanning optical system so that the irradiated fixation target does not move more than a predetermined distance due to the scanning of the scanning optical system, and an ophthalmic device including the same.

[0005] The second aspect of the technology of the present disclosure is a scanning optical system that scans an eye to be examined with light from a light source, a fixation light source that irradiates the eye to be examined with fixation light through the scanning optical system, and a fixation light scanning unit that scans the fixation light in synchronization with the scanning of the scanning optical system so that the fixation target irradiated to the eye to be examined does not move more than a predetermined distance due to the scanning of the scanning optical system for an ophthalmic device including the same, Based on instruction information indicating an instruction for guiding the orientation of the eye to be examined, the fixation light source and the fixation light scanning unit are controlled so that the fixation light irradiates a fixation target at a position corresponding to the instruction. A control method for an ophthalmic apparatus including this.

[0006] A third aspect of the technology of the present disclosure is A program stored in a storage medium and causing a processor to execute fixation control, wherein the processor A scanning optical system that scans the eye to be examined with light from a light source, A fixation light source that irradiates the eye to be examined with fixation light through the scanning optical system and functions as a fixation target, and A fixation light scanning unit that scans the fixation light in synchronization with the scanning of the scanning optical system so that the fixation target irradiated on the eye to be examined does not move more than a predetermined distance due to the scanning of the scanning optical system For an ophthalmic apparatus including Based on instruction information indicating an instruction for guiding the orientation of the eye to be examined, the fixation light source and the fixation light scanning unit are controlled so that the fixation light irradiates a fixation target at a position corresponding to the instruction. A program that executes a process including this.

Brief Description of the Drawings

[0007]

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Embodiments for Carrying Out the Invention

[0008] Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings. In addition, components and processes having the same functions may be given the same reference numerals throughout the drawings, and redundant descriptions may be omitted as appropriate.

[0009] Referring to FIG. 1, the configuration of the ophthalmic system 100 will be described. As shown in FIG. 1, the ophthalmic system 100 includes an ophthalmic device 110, a server device (hereinafter referred to as "server") 140, and an image display device (hereinafter referred to as "viewer") 150. The ophthalmic device 110 acquires fundus images. The server 140 stores a plurality of fundus images obtained by photographing the fundus of a plurality of patients by the ophthalmic device 110 in correspondence with the patient IDs. The viewer 150 displays the fundus images acquired from the server 140.

[0010] The ophthalmic device is an example of the "ophthalmic device" of the technology of the present disclosure.

[0011] The ophthalmic device 110, the server 140, and the viewer 150 are interconnected via a network 130.

[0012] Next, referring to FIG. 2, the configuration of the ophthalmic device 110 will be described. For convenience of explanation, a Scanning Laser Ophthalmoscope is referred to as "SLO". Also, an Optical Coherence Tomography is referred to as "OCT".

[0013] When the ophthalmic device 110 is installed in a horizontal plane, the horizontal direction is defined as the "X direction", the vertical direction with respect to the horizontal plane is defined as the "Y direction", and the direction connecting the center of the pupil of the anterior segment of the eye to be examined 12 and the center of the eyeball is defined as the "Z direction". Therefore, the X direction, the Y direction, and the Z direction are perpendicular to each other.

[0014] The ophthalmic device 110 includes an imaging device 14 and a control device 16. The imaging device 14 includes an SLO unit 18, an OCT unit 20, and an imaging optical system 19, and acquires a fundus image of the fundus of the eye to be examined 12. Hereinafter, the two-dimensional fundus image acquired by the SLO unit 18 is referred to as an SLO image. Also, a tomographic image or an en-face image of the fundus (e.g., retina) created based on the OCT data acquired by the OCT unit 20 is referred to as an OCT image.

[0015] The imaging device 14 is an example of the "imaging unit" of the technology of the present disclosure. The control device 16 is an example of the "control unit" of the technology of the present disclosure.

[0016] The control device 16 includes a computer having a CPU (Central Processing Unit) 16A which is an example of a processor, a RAM (Random Access Memory) 16B, a ROM (Read-Only memory) 16C, and an input / output (I / O) port 16D.

[0017] The control device 16 includes an input / display device 16E connected to the CPU 16A via the I / O port 16D. The input / display device 16E has a graphic user interface for displaying an image of the eye to be examined 12 and receiving various instructions from the user. Examples of the graphic user interface include a touch panel display.

[0018] Also, the control device 16 includes an image processing device 17 connected to the I / O port 16D. The image processing device 17 generates an image of the eye to be examined 12 based on the data obtained by the imaging device 14. Note that the control device 16 also includes a communication I / F 16F connected to the I / O port 16D, and is connected to the network 130 via the communication I / F 16F.

[0019] As described above, in FIG. 2, the control device 16 of the ophthalmic device 110 includes the input / display device 16E, but the technology of the present disclosure is not limited thereto. For example, the control device 16 of the ophthalmic device 110 may not include the input / display device 16E, and may be provided with a separate input / display device physically independent of the ophthalmic device 110. In this case, the display device includes an image processing unit that operates under the control of the CPU 16A of the control device 16. The image processing unit may display an SLO image or the like based on the image signal output-instructed by the CPU 16A.

[0020] The imaging device 14 operates under the control of the CPU 16A of the control device 16. The imaging device 14 includes an SLO unit 18, an imaging optical system 19, and an OCT unit 20. The imaging optical system 19 includes a first optical scanner 22, a second optical scanner 24, a combining unit 26, an objective optical system 28, and a fixation unit 29. These first optical scanner 22, second optical scanner 24, combining unit 26, objective optical system 28, and fixation unit 29 are shown as functional blocks within the imaging optical system 19.

[0021] The first optical scanner 22 scans the incident light in one direction (e.g., the X direction), and the second optical scanner 24 scans in the other direction (e.g., the Y direction). Thereby, the first optical scanner 22 and the second optical scanner 24 two-dimensionally scan the light emitted from the SLO unit 18 and the light emitted from the OCT unit 20 in the X direction and the Y direction. The first optical scanner 22 and the second optical scanner 24 may be optical elements capable of deflecting a light beam. For example, a polygon mirror, a galvanometer mirror, or the like can be used. Also, a combination thereof may be used.

[0022] The combining unit 26 combines the light from the SLO unit 18 and the light from the OCT unit 20. The objective optical system 28 emits the light from the SLO unit 18 and the light from the OCT unit 20 to the eye to be examined 12. The fixation unit 29 functions as a fixation target for guiding the orientation (line-of-sight direction) of the eye to be examined 12.

[0023] Note that the objective optical system 28 may be a reflective optical system using a concave mirror such as an elliptical mirror, a refractive optical system using a wide-angle lens, or a refractive reflective optical system combining a concave mirror and a lens. By using a wide-angle optical system using an elliptical mirror or a wide-angle lens, it is possible to image the retina not only in the central part of the fundus but also in the peripheral part of the fundus.

[0024] When using a system including an elliptical mirror, a configuration using the system with an elliptical mirror described in International Publication WO2016 / 103484 or International Publication WO2016 / 103489 may be adopted. The disclosures of International Publication WO2016 / 103484 and International Publication WO2016 / 103489 are each incorporated herein by reference in their entirety.

[0025] The imaging optical system 19 enables observation of a wide field of view (FOV) 12A in the fundus. The FOV 12A indicates the range that can be imaged by the imaging device 14. The FOV 12A can be expressed as a field angle. In the present embodiment, the field angle can be defined by an internal irradiation angle and an external irradiation angle. The external irradiation angle is the irradiation angle of the light beam irradiated from the ophthalmic device 110 to the eye to be examined 12, defined with reference to the pupil 27. The internal irradiation angle is the irradiation angle of the light beam irradiated to the fundus, defined with reference to the center O of the eyeball. The external irradiation angle and the internal irradiation angle are in a corresponding relationship. For example, when the external irradiation angle is 120 degrees, the internal irradiation angle corresponds to approximately 160 degrees. In the present embodiment, the internal irradiation angle is 200 degrees. With the imaging optical system 30 configured with such a wide-angle optical system, the field angle (FOV) of the fundus can be set to an ultra-wide angle, and the range of the fundus with an internal irradiation angle of 200 degrees starting from the center of the eyeball can be imaged. That is, it is possible to image the region from the posterior pole to beyond the equator of the fundus of the eye to be examined 12. Of course, it goes without saying that the present invention can be applied not only to a wide-angle optical system but also to an ophthalmic device equipped with optical systems of various picture angles.

[0026] Here, an SLO fundus image obtained by imaging with an imaging angle of 160 degrees or more with the internal irradiation angle is referred to as a UWF-SLO fundus image. Note that UWF is an abbreviation for UltraWide Field (ultra-wide angle).

[0027] The SLO system is realized by the control device 16, the SLO unit 18, and the imaging optical system 19 shown in FIG. 2. The SLO system enables fundus imaging with a wide FOV 12A by the imaging optical system 19.

[0028] The SLO unit 18 includes a light source 40 for B (blue light), a light source 42 for G light (green light), a light source 44 for R light (red light), and a light source 46 for IR light (infrared light (e.g., near-infrared light)), and optical systems 48, 50, 52, 54, 56 that reflect or transmit the light from the light sources 40, 42, 44, 46 and guide it into one optical path. The optical systems 48, 50, 56 are mirrors, and the optical systems 52, 54 are beam splitters. The B light is reflected by the optical system 48, transmitted through the optical system 50, and reflected by the optical system 54. The G light is reflected by the optical systems 50 and 54. The R light is transmitted through the optical systems 52 and 54. The IR light is reflected by the optical systems 56 and 52 and is respectively guided into one optical path.

[0029] The SLO unit 18 is configured to be able to switch between a mode of emitting G light, R light, and B light and a combination of light sources that emit laser light or cause emission of laser light with different wavelengths, such as a mode of emitting infrared light. In the example shown in FIG. 2, it includes four light sources: a light source 40 for B light (blue light), a light source 42 for G light, a light source 44 for R light, and a light source 46 for IR light. However, the technology of the present disclosure is not limited thereto. For example, the SLO unit 18 may further include a light source for white light and emit light in various modes such as a mode of emitting only white light.

[0030] The light incident from the SLO unit 18 into the imaging optical system 19 is scanned in the X direction and the Y direction by the first optical scanner 22 and the second optical scanner 24. The scanned light is irradiated onto the posterior part of the eye to be examined 12 via the objective optical system 28 and the pupil 27. The reflected light reflected by the fundus is incident on the SLO unit 18 via the objective optical system 28, the first optical scanner 22, and the second optical scanner 24.

[0031] The anterior segment of the eye to be examined 12 includes, as the anterior eye segment, for example, parts including the cornea, iris, angle, lens, ciliary body, and a part of the vitreous body. The posterior segment of the eye to be examined 12 includes, as the posterior eye segment, for example, parts including the remaining part of the vitreous body, retina, choroid, and sclera. Note that the vitreous body belonging to the anterior segment is the part of the vitreous body on the cornea side with the X-Y plane passing through the point closest to the center of the eye in the lens as the boundary, and the vitreous body belonging to the posterior segment is the part of the vitreous body other than the vitreous body belonging to the anterior segment within the vitreous body.

[0032] The SLO unit 18 includes a beam splitter 64 that reflects B light and transmits light other than B light among the light from the posterior segment (for example, the fundus) of the eye to be examined 12, and a beam splitter 58 that reflects G light and transmits light other than G light among the light transmitted through the beam splitter 64. The SLO unit 18 includes a beam splitter 60 that reflects R light and transmits light other than R light among the light transmitted through the beam splitter 58. The SLO unit 18 includes a beam splitter 62 that reflects IR light among the light transmitted through the beam splitter 60. The SLO unit 18 includes a B light detection element 70 that detects the B light reflected by the beam splitter 64, a G light detection element 72 that detects the G light reflected by the beam splitter 58, an R light detection element 74 that detects the R light reflected by the beam splitter 60, and an IR light detection element 76 that detects the IR light reflected by the beam splitter 62.

[0033] The light (reflected light reflected by the fundus) incident on the SLO unit 18 via the objective optical system 28, the first optical scanner 22, and the second optical scanner 24 is reflected by the beam splitter 64 and received by the B light detection element 70 in the case of B light, transmitted through the beam splitter 64, reflected by the beam splitter 58, and received by the G light detection element 72 in the case of G light. The incident light is transmitted through the beam splitters 64 and 58, reflected by the beam splitter 60, and received by the R light detection element 74 in the case of R light. The incident light is transmitted through the beam splitters 64, 58, and 60, reflected by the beam splitter 62, and received by the IR light detection element 76 in the case of IR light. The image processing device 17 operating under the control of the CPU 16A generates a UWF-SLO image using the signals detected by the B light detection element 70, the G light detection element 72, the R light detection element 74, and the IR light detection element 76.

[0034] The UWF-SLO image includes a UWF-SLO image (G-color fundus image) obtained by photographing the fundus in G color and a UWF-SLO image (R-color fundus image) obtained by photographing the fundus in R color. The UWF-SLO image includes a UWF-SLO image (B-color fundus image) obtained by photographing the fundus in B color and a UWF-SLO image (IR fundus image) obtained by photographing the fundus in IR.

[0035] Also, the control device 16 controls the light sources 40, 42, 44 to emit light simultaneously. By photographing the fundus of the eye to be examined 12 simultaneously with B light, G light, and R light, a G-color fundus image, an R-color fundus image, and a B-color fundus image in which each position corresponds to each other are obtained. An RGB color fundus image is obtained from the G-color fundus image, the R-color fundus image, and the B-color fundus image. The control device 16 controls the light sources 42, 44 to emit light simultaneously, and by photographing the fundus of the eye to be examined 12 simultaneously with G light and R light, a G-color fundus image and an R-color fundus image in which each position corresponds to each other are obtained. An RG color fundus image is obtained from the G-color fundus image and the R-color fundus image.

[0036] As UWF-SLO images, specifically, there are B-color fundus images, G-color fundus images, R-color fundus images, IR fundus images, RGB color fundus images, and RG color fundus images. Each image data of the UWF-SLO images is transmitted from the ophthalmic device 110 to the server 140 via the communication I / F 16F together with the patient information input via the input / display device 16E. Each image data of the UWF-SLO images and the patient information are stored in the storage device 254 in a corresponding manner. Note that the patient information includes, for example, patient ID, name, age, visual acuity, distinction between right eye / left eye, axial length, etc.

[0037] The OCT system is realized by the control device 16, the OCT unit 20, and the imaging optical system 19 shown in FIG. 2. The OCT system enables fundus imaging with a wide FOV 12A by the imaging optical system 19 in the same manner as the imaging of the above-described SLO fundus images. The OCT unit 20 includes a light source 20A, a sensor (detection element) 20B, a first optical coupler 20C, a reference optical system 20D, a collimating lens 20E, and a second optical coupler 20F.

[0038] The light emitted from the light source 20A is branched by the first optical coupler 20C. One of the branched lights is used as measurement light, collimated by the collimating lens 20E, and then incident on the imaging optical system 19. The measurement light is scanned in the X direction and the Y direction by the first optical scanner 22 and the second optical scanner 24. The scanned light is irradiated onto the fundus via the objective optical system 28 and the pupil 27. The measurement light reflected by the fundus is incident on the OCT unit 20 via the objective optical system 28, the first optical scanner 22, and the second optical scanner 24, and then incident on the second optical coupler 20F via the collimating lens 20E and the first optical coupler 20C.

[0039] The other light emitted from the light source 20A and branched by the first optical coupler 20C is incident on the reference optical system 20D as reference light, and then incident on the second optical coupler 20F via the reference optical system 20D.

[0040] These lights incident on the second optical coupler 20F, that is, the measurement light reflected by the fundus and the reference light, are interfered by the second optical coupler 20F to generate interference light. The interference light is received by the sensor 20B. The image processing device 17 operating under the control of the CPU 16A generates OCT images such as tomographic images and en-face images based on the OCT data detected by the sensor 20B.

[0041] Here, an OCT fundus image obtained by imaging with an imaging angle of 160 degrees or more at the internal irradiation angle is referred to as a UWF-OCT image.

[0042] The image data of the UWF-OCT image is transmitted from the ophthalmic device 110 to the server 140 via the communication I / F 16F together with the patient information. The image data of the UWF-OCT image and the patient information are correspondingly stored in the storage device 254.

[0043] In this embodiment, the light source 20A is an example of a wavelength-sweeping type SS-OCT (Swept-Source OCT), but various types of OCT systems such as SD-OCT (Spectral-Domain OCT) and TD-OCT (Time-Domain OCT) may also be used.

[0044] Next, referring to FIG. 3, the electrical configuration of the server 140 will be described. As shown in FIG. 3, the server 140 includes a computer main body 252. The computer main body 252 has a CPU 262, a RAM 266, a ROM 264, and an input / output (I / O) port 268 that are interconnected by a bus 270. A storage device 254, a display 256, a mouse 255M, a keyboard 255K, and a communication interface (I / F) 258 are connected to the input / output (I / O) port 268. The storage device 254 is composed of, for example, a non-volatile memory. The input / output (I / O) port 268 is connected to the network 130 via the communication interface (I / F) 258. Therefore, the server 140 can communicate with the ophthalmic device 110 and the viewer 150. A photographing processing program described later is stored in the storage device 254. Note that the photographing processing program may be stored in the ROM 264.

[0045] A processing unit 208 (to be described later) of the server 140 stores each data received from the ophthalmic device 110 in the storage device 254.

[0046] Since the electrical configuration of the viewer 150 is the same as that of the server 140, its description will be omitted.

[0047] Next, referring to FIG. 4, the functions realized by the CPU 262 of the server 140 executing an image processing program will be described. The image processing program has a predetermined display control function, a predetermined image processing function, and a predetermined processing function. By the CPU 262 executing the image processing program having these functions, the CPU 262 functions as a display control unit 204, an image processing unit 206, and a processing unit 208 as shown in FIG. 4.

[0048] Next, with reference to FIG. 5, the configuration of the imaging optical system 19 including the fixation unit 29 will be described. In the following, the light emitted from the SLO unit 18 and incident on the imaging optical system 19 is referred to as "SLO light", and the light emitted from the OCT unit 20 and incident on the imaging optical system 19 is referred to as "OCT light". In the present embodiment, the SLO light and the OCT light incident on the imaging optical system 19 are configured to be substantially parallel light.

[0049] FIG. 5 is a conceptual diagram showing an example of the schematic configuration of the imaging optical system 19. As shown in FIG. 5, the imaging optical system 19 includes a combining unit 26 that combines SLO light and OCT unit light, a first optical scanner 22 (denoted as an H scanner in FIG. 5), a second optical scanner 24 (denoted as a V scanner in FIG. 5), an objective optical system 28, and a fixation unit 29 that functions as a fixation target for guiding the direction (line-of-sight direction) of the eye 12 to be examined.

[0050] In the present embodiment, as the combining unit 26, a dichroic mirror having wavelength dependence can be used, and the combining unit 26 has a function of combining the optical path of the SLO light traveling toward the eye to be examined and the optical path of the OCT traveling toward the eye to be examined. Further, for the light irradiated on the eye 12 to be examined and reflected by the eye 12 to be examined, the combining unit 26 separates the optical path of the reflected light based on the SLO light and the optical path of the reflected light based on the OCT light, guides the reflected light based on the SLO light to the SLO unit 18, and also has a function of guiding the reflected light based on the OCT light to the OCT unit 20.

[0051] The light (SLO light or OCT light) emitted from the combining unit 26 is incident on the objective optical system 28 via the first optical scanner 22 and the second optical scanner 24, and is emitted to the eye 12 to be examined by the objective optical system 28. On the optical path between the first optical scanner 22 and the second optical scanner 24, a first lens group 295 on the first optical scanner 22 side and a second lens group 296 on the second optical scanner 24 side are arranged.

[0052] The optical system composed of the first lens group 295 and the second lens group 296 is an afocal optical system, and is configured to establish a conjugate relationship between the position of the first optical scanner 22 (the position of the scanning center of the first optical scanner 22) and the position of the second optical scanner 24 (the position of the scanning center of the second optical scanner 24). In this specification, the "conjugate relationship" is not limited to a complete conjugate relationship, but means a conjugate relationship including errors allowed in advance as manufacturing errors and errors associated with changes over time. Also, in this specification, the "afocal optical system" is not limited to a complete afocal optical system, but means an afocal optical system including errors allowed in advance as manufacturing errors and errors associated with changes over time.

[0053] The general operation of the imaging optical system 19 having the above configuration will be described. The SLO light or OCT light of parallel light incident on the imaging optical system 19 is angularly scanned by a second optical scanner 24 such as a polygon mirror via a combining unit. The angularly scanned SLO light or OCT light of parallel light passes through the second lens group 296 and the first lens group 295 in sequence, is angularly scanned by the first optical scanner 22, and is projected onto the pupil plane of the eye to be examined 12 as parallel light at a predetermined magnification via the objective optical system 28, and angular scanning is performed with the pupil of the eye to be examined 12 as the scanning center. This parallel light is condensed by the eye to be examined 12, and at the fundus of the eye to be examined 12, a condensing spot of SLO light or OCT light scans the fundus as irradiation light. The reflected light obtained by reflection of this irradiation light at the fundus passes through the pupil of the eye to be examined 12, and sequentially passes through the objective optical system 28, the first optical scanner 22, the first lens group 295, the second lens group 296, the second optical scanner 24, and the combining unit 26, and enters the SLO unit 18 or the OCT unit 20. The operation after each reflected light enters the SLO unit 18 or the OCT unit 20 is as described above.

[0054] Between the first optical scanner 22 and the second optical scanner 24, a fixation unit 29, which is an optical system for presenting a fixation target, is disposed between the first lens group 295 and the second lens group 296. The fixation unit 29 includes a fixation light source 291 that functions as a fixation lamp, a fixation lamp scanner 292, a third lens group 293, and a reflection element 294 such as a half mirror. It is configured to guide light from the fixation light source 291 (hereinafter referred to as fixation light) on the principal optical axis AX of the imaging optical system 19. Further, the third lens group 293 in the fixation unit 29 is disposed at a common position with the optical path lengths of the first lens group 295 and the second lens group 296. Also, the third lens group 293 is configured to have a conjugate relationship between the position of the first optical scanner 22 (the position of the scanning center of the first optical scanner 22) and the position of the fixation lamp scanner 292 (the position of the scanning center of the fixation lamp scanner 292), and to form an afocal optical system.

[0055] The first optical scanner 22 is an example of the "scanning optical system" and the "second scanning optical system" of the technology of the present disclosure. The second optical scanner 24 is an example of the "first scanning optical system" of the technology of the present disclosure. Also, the second optical scanner 24 is an example of the "optical scanner" of the technology of the present disclosure. The reflection element 294 is an example of the "optical member" of the technology of the present disclosure. The fixation light source 291 is an example of the "fixation light source" of the technology of the present disclosure, and the fixation lamp scanner 292 is an example of the "fixation light scanning unit" of the technology of the present disclosure. Also, the fixation lamp scanner 24 is an example of the "fixation lamp scanner" of the technology of the present disclosure.

[0056] The fixation lamp scanner 292 of the fixation unit 29 is controlled to be driven in synchronization with the first optical scanner 22. The drive control of the fixation lamp scanner 292 is performed by the control device 16 (details will be described later).

[0057] As shown in Fig. 5, when the fixation light is guided to the optical axis by the fixation unit 29, the irradiation angle to the eye to be examined 12 is changed by the scanning of the first optical scanner 22, and the fixation target moves in the horizontal direction. Therefore, in the present embodiment, the fixation lamp scanner 292 is arranged, and the fixation lamp scanner 292 is driven in synchronization with the first optical scanner 22 (so as to cancel the horizontal movement amount by the H scanner 22) so that the fixation target stays still. Thereby, even when the SLO light or the OCT light is scanned by the optical scanner 22 (the H scanner in the horizontal direction), the fixation target continues to be lit at the same position with respect to the eye to be examined 12. That is, the fixation light from the fixation light source 291 is scanned by the fixation lamp scanner 292 in synchronization with the scanning of the first optical scanner 22 so that the fixation target by the fixation light source 291 does not move more than a predetermined distance from the position with respect to the eye to be examined 12 due to the scanning of the first optical scanner 22.

[0058] Specifically, the fixation lamp scanner 292 is driven at a scanning angle equivalent to the scanning angle of the first optical scanner 22 and in the opposite scanning direction. As shown in Fig. 5, when the first optical scanner 22 rotates (scans light) in the direction of arrow Ra, the fixation lamp scanner 292 rotates in the direction of arrow Rb. Due to the rotation of the fixation lamp scanner 292 in the direction of arrow Rb, the fixation light moves in the direction of arrow Rc on the reflection element 294. In this case, the first optical scanner 22 and the fixation lamp scanner 292 are driven in synchronization with a common phase. That is, as shown in Fig. 6, the control device 16 makes the drive signal 297 of the first optical scanner 22 and the drive signal 298 of the fixation lamp scanner 292 coincide in signal period and phase, and drives the first optical scanner 22 and the fixation lamp scanner 292 respectively. Thereby, the variation in the rotation angle of the first optical scanner 22 and the variation in the rotation angle of the fixation lamp scanner 292 are common variations and are synchronized, and the first optical scanner 22 and the fixation lamp scanner 292 are each driven.

[0059] In this way, by synchronously driving the first optical scanner 22 and the fixation lamp scanner 292 with a common signal period and a common phase, even if the scanning angle varies during the scanning by the first optical scanner 22, the fixation light is incident on the first optical scanner 22 at an angle that cancels out the variation. As a result, the fixation target is fixed, and the eye under test 12 is irradiated with the fixation light at an arbitrary angle (for example, the angle in the line-of-sight direction on the principal optical axis AX), and it becomes possible to guide the orientation (line-of-sight direction) of the eye under test 12 in an arbitrary direction in the irradiation direction of the fixation light.

[0060] Also, when the drive signal of the first optical scanner 22 is defined as the first drive signal and the drive signal of the fixation lamp scanner 292 is defined as the second drive signal, the first drive signal and the second drive signal may have the same waveform, a similar waveform, or the second drive signal may have a waveform proportional to the first drive signal. By generating the first drive signal and the second drive signal in this way, the total amount at the optical conjugate position of the deflection vector of the light beam by the first scanner and the deflection vector of the light beam by the second scanner becomes constant. Therefore, while the SLO light or OCT light, which is the imaging light, is scanning the eye under test by the first optical scanner 22, the fixation target continues to light up at a fixed position. While the SLO light or OCT light, which is the imaging light, is scanning the eye under test 12, the orientation of the eye under test 12 can be fixed.

[0061] The fixation unit 29 can be configured to be able to change the position where the fixation target is presented. The control for changing the position where the fixation target is presented is performed by the control device 16. FIGS. 7 and 8 show a configuration example in which the position where the fixation target is presented can be changed.

[0062] In the example shown in FIG. 7, the fixation unit 29 includes a light source array 2910 that emits fixation light having a plurality of fixation lights 2912. The light source array 2910 is controlled to turn on by the control device 16. The light emitting surface of the light source array 2910 is conjugate with the retina of the eye to be examined 12. By turning on any one of the fixation lights 2912 of the light source array 2910 by the control device 16, the position where the fixation light is emitted at the fixation light source 291 can be changed two-dimensionally. That is, control is performed to change the position where the fixation light is turned on from the first position to a second position different from the first position. Thereby, the orientation of the eye to be examined with respect to the optical axis can be changed. Therefore, when the fixation light is turned on at the first position, the SLO light or OCT light, which is imaging light, is scanned with respect to the first region of the eye to be examined 12, and for example, the central part of the fundus (the posterior pole of the fundus including the macula and the optic disc) can be imaged. When the position where the fixation light is turned on is set to the second position, the eye to be examined 12 will face the second position, and a second region different from the first region of the eye to be examined 12 (a region including a part of the central part and the peripheral part around the central part) can be scanned with the imaging light.

[0063] Also, in the example shown in FIG. 8, the fixation unit 29 has a fixation light 2916 and includes a light source 2914 configured to be movable in the Xa direction along the X direction and movable in the Ya direction along the Y direction. The position of the light source 2914 is controlled by the control device 16. By changing the position of the light source 2914 by the control device 16, the position (the position of the fixation light 2916) where the fixation light is emitted at the fixation light source 291 can be changed two-dimensionally. In this way, by changing the position where the fixation target is presented, the orientation (line-of-sight direction) of the eye to be examined 12 can be guided in an arbitrary direction. In the present embodiment, the case where the light source array 2910 shown in FIG. 7 is used as the fixation light source 291 will be described as an example.

[0064] Next, with reference to FIG. 9, the imaging function realized by the CPU 16A in the control device 16 of the ophthalmic device 110 by executing an imaging processing program will be described. The imaging processing program includes an imaging mode setting processing function, an imaging processing function (fixation target processing function, actual processing function), and an image processing control function. By executing the imaging processing program having each of these functions, the CPU 16A functions as an imaging mode setting processing unit 162, an imaging processing unit 164 (fixation target processing unit 164A, actual processing unit 164B), and an image processing control unit 166, as shown in FIG. 9. The imaging processing program is an example of the "program" of the technology of the present disclosure.

[0065] Next, with reference to FIG. 10, the imaging processing by the ophthalmic device 110 will be described in detail. By the CPU 16A of the control device 16 in the ophthalmic device 110 executing the imaging processing program, the imaging processing shown in the flowchart of FIG. 10 is realized. The imaging processing program starts when the operator instructs the start of the imaging processing of the test eye 12 by operating the input / display device 16E of the ophthalmic device 110. The imaging processing shown in the flowchart of FIG. 10 is an example of the processing for realizing the "control method of an ophthalmic device" of the technology of the present disclosure.

[0066] When the imaging processing program starts, in step S102, the imaging mode setting processing unit 162 sets the imaging mode obtained by detecting the operation of the input / display device 16E. The imaging mode indicates the imaging site and imaging method of the test eye 12. For example, there are an SLO imaging mode in which the posterior part of the test eye 12 (for example, the fundus) is imaged by the SLO unit 18, and an OCT imaging mode in which the posterior part of the test eye 12 is imaged by the OCT unit 20. Note that the imaging mode is not limited to the imaging mode for imaging the posterior part of the test eye 12, and includes an imaging mode for imaging the anterior part of the eye and an imaging mode for performing imaging related to the test eye 12. By the processing of step S102, the imaging mode is set.

[0067] In step S104, the fixation mark processing unit 164A of the imaging processing unit 164 executes a fixation mark position acquisition process by acquiring, from a table, the position of a fixation mark predetermined for a set imaging mode. The table is information associating the imaging mode with the position of the fixation mark and is stored in advance in the ROM 16C. Note that the table may be acquired from an external device.

[0068] In step S106, the fixation mark processing unit 164A sets the first optical scanner 22 (H scanner) and the fixation lamp scanner 292 (third scanner) at predetermined initial positions (for example, positions where each light propagates in a direction along the main optical axis AX). In step S108, the fixation mark processing unit 164A controls the fixation lamp 2912 at a predetermined position in the light source array 2910 to turn on in order to present the fixation mark at the predetermined position acquired in step S104. Thereby, the fixation mark is presented at a predetermined position corresponding to the imaging mode, and preparations are made to guide the orientation (line-of-sight direction) of the eye to be examined 12.

[0069] In step S110, the actual processing unit 164B executes (starts) an imaging process according to the imaging mode set in step S102.

[0070] In step S112, the fixation mark processing unit 164A controls the first optical scanner 22 (H scanner) and the fixation lamp scanner 292 (third scanner) to be driven synchronously. That is, the drive signal 297 of the first optical scanner 22 and the drive signal 298 of the fixation lamp scanner 292 are made to match in signal period and phase, and control is performed to drive each of the first optical scanner 22 and the fixation lamp scanner 292 (FIG. 6). In step S114, the actual processing unit 164B determines whether or not the imaging process has been completed, and repeats the process of step S112 until the process is completed (a positive determination in step S114). In step 116, at least the first optical scanner 22 (H scanner) and the fixation lamp scanner 292 (third scanner) are stopped and returned to their initial positions.

[0071] In step S118, the actual processing unit 164B determines whether or not the process of presenting the fixation target and taking a photograph for each of all the positions acquired in step S104 has been completed. If all the processes are not completed (negative determination in step S118), the actual processing unit 164B returns the process to step S106. If all the processes are completed (positive determination in step S118), the process proceeds to step S120.

[0072] In step S120, the fixation target processing unit 164A turns off the fixation light source 291. In the processing routine shown in FIG. 10, the fixation light source 291 is turned on before photographing and turned off after photographing is completed. The technology of the present disclosure is not limited to the fixation light source 291 being turned on during photographing. For example, when the fixation light from the fixation light source affects the photographing, the fixation light source may be turned off immediately before photographing. Further, the lighting of the fixation light source 291 is not limited to being always on, and includes a state of lighting for a predetermined time and a blinking state of repeating a state of lighting for a predetermined time.

[0073] In step S122, the image processing control unit 166 outputs image data. Specifically, the image data of the fundus image (for example, UWF-SLO image) obtained by photographing the fundus of the eye 12 to be examined by the ophthalmic apparatus 110 is transmitted from the ophthalmic apparatus 110 to the server 140. That is, the image processing control unit 166 controls the image processing apparatus 17 to perform noise removal processing and the like on the image obtained by photographing, perform image processing on a UWF-SLO image or a UWF-OCT image, and then transmit the processed image to the server 140.

[0074] On the other hand, in the server 140, when the image data of the fundus image (for example, UWF-SLO image) obtained by photographing the fundus of the eye 12 to be examined by the ophthalmic apparatus 110 is received from the ophthalmic apparatus 110, the CPU 262 executes an image processing program, and thus image processing is executed.

[0075] Specifically, the server 140 uses the image processing unit 206 to obtain a fundus image from the image data, performs predetermined image processing using the obtained fundus image, and generates a processed image after the image processing. An example of the predetermined image processing includes image processing for generating a composite image (see FIGS. 11 and 12) obtained by synthesizing a plurality of UWF-SLO images taken at fixation marks presented at different positions.

[0076] For example, a composite image synthesized using at least two of the fundus images IG1, IG2, and IG3 is generated. The fundus image IG1 is a UWF-SLO image taken by presenting a fixation mark at the fundus conjugate position Fcj on the principal optical axis AX. The fundus images IG2 and IG3 are UWF-SLO images taken by presenting a fixation mark at the fundus conjugate position Fcj and at a position separated from the principal optical axis AX. Specifically, a UWF-SLO image taken by presenting a fixation mark above the principal optical axis AX is used as the fundus image IG2, and a UWF-SLO image taken by presenting a fixation mark below the principal optical axis AX is used as the fundus image IG3.

[0077] The server 140 performs image processing such as pattern matching to match the blood vessel portions, for example, on the fundus images IG2 and IG3 with respect to the fundus image IG1 as a reference, and performs image processing to synthesize the fundus images IG2 and IG3 to generate a processed image.

[0078] The processing unit 208 stores the processed image (composite image) together with each of the fundus images in the storage device 254 (see FIG. 3) together with the information of the patient (patient ID, name, age, visual acuity, right eye / left eye distinction, axial length, etc.).

[0079] The display control unit 204 may display the processed image on the display 256.

[0080] When an ophthalmologist diagnoses the patient's eye to be examined 12, the viewer 150 inputs the patient ID. The viewer 150 with the patient ID input instructs the server 140 to transmit the image data of each image (IG1, IG4, etc.) together with the patient information corresponding to the patient ID. The viewer 150 that has received the image data of each image (IG1, IG4) together with the patient information generates a diagnostic screen 400 for the patient's eye to be examined 12 shown in FIG. 11 and displays it on the display of the viewer 150.

[0081] FIG. 11 shows the diagnostic screen 400 of the viewer 150. As shown in FIG. 11, the diagnostic screen 400 has an information display area 402 and an image display area 404.

[0082] Information regarding the patient, such as the patient ID, patient name, and patient gender, is displayed in the information display area 402. Although not shown in the figure, various information such as the patient's age, visual acuity, information indicating whether the displayed image is of the right eye or the left eye, and axial length of the eye can also be displayed in the information display area 402. The viewer 150 displays the information regarding the corresponding patient in the information display area 402 based on the received patient information.

[0083] The image display area 404 has a main image display area 404A and a composite image display area 404B. The viewer 150 displays the images (fundus image IG1 as the main image and fundus image IG4 as the composite image) corresponding to each image display area (404A, 404B) based on the received image data. Although not shown in the figure, the date of year, month, and day when the displayed image was acquired can be displayed in each of the image display areas 404A and 404B.

[0084] As shown in FIG. 12, the fundus image IG4, which is a composite image, is an image obtained by synthesizing the fundus image IG2 when fixating upward and the fundus image IG3 when fixating downward by pattern matching or the like that aligns the blood vessel portions with reference to the fundus image IG1.

[0085] Note that the image display area 404 can include a text display area for displaying text information related to the image. Examples of the text information include, for example, text information such as "In the left area, a fundus image when a fixation target is presented on the principal optical axis AX is displayed. In the right area, an image synthesized from respective fundus images when the fixation target is presented vertically and horizontally is displayed."

[0086] In addition, various information useful for diagnosis can be displayed on the diagnostic screen 400, but it is omitted in the example shown in FIG. 11.

[0087] In this way, by synchronously driving the first optical scanner 22 and the fixation lamp scanner 292 with a common signal period and a common phase, even if the scanning angle varies in the scanning of the first optical scanner 22, the fixation light is incident on the first optical scanner 22 at an angle that cancels out the variation. As a result, the fixation target is fixed, and the examined eye 12 is irradiated with the fixation light at an arbitrary position (for example, a position in the line-of-sight direction on the principal optical axis AX), and the direction (line-of-sight direction) of the examined eye 12 can be guided in an arbitrary direction.

[0088] The above-described fixation unit 29 has been described for the case where the lighting position of the fixation lamp source is controlled using the light source array 2910 (FIG. 7) as the fixation lamp source 291, but the technology of the present disclosure is not limited thereto. For example, instead of changing the lighting position of the fixation lamp source, an offset may be added to the drive signal of the scanner that is synchronously driven. The case of offsetting this drive signal will be described as a first modification example.

[0089] As shown in FIG. 13, in the above, the drive signal 297 of the first optical scanner 22 and the drive signal 298 of the fixation light scanner 292 are made to have the same signal period and phase, and each of the first optical scanner 22 and the fixation light scanner 292 is driven. On the other hand, the fixation light scanner 292 is configured to be driven by a drive signal 299 offset by a predetermined offset time tofs. The offset time tofs may be determined by the scanning time with respect to the scanning angle of the first optical scanner 22 corresponding to the position where the fixation target is presented when commonly driven at the offset time “0”. Thereby, the common variation between the variation in the rotation angle of the first optical scanner 22 and the variation in the rotation angle of the fixation light scanner 292 is offset by the offset time tofs and synchronized, and each of the first optical scanner 22 and the fixation light scanner 292 is driven. As a result, the fixation target is stationary at the offset position, the fixation light is irradiated to an arbitrary offset position on the eye to be examined 12, and it becomes possible to guide the direction (line-of-sight direction) of the eye to be examined 12 to the offset direction.

[0090] Also, when irradiating the fixation light with an offset with respect to the drive signal 297 of the first optical scanner 22, it is also possible to present the fixation target with a two-dimensional position change.

[0091] FIG. 14 is a conceptual diagram showing a configuration example when presenting the fixation target with a two-dimensional position change. As shown in FIG. 14, the fixation unit 29 includes a first fixation lamp scanner 292V that scans fixation light in one direction, and a second fixation lamp scanner 292H that scans in a direction intersecting (for example, orthogonal to) the first fixation lamp scanner 292V. The second fixation lamp scanner 292H is synchronously driven (or offset-driven) with the first optical scanner 22 (H scanner) in the same manner as the fixation lamp scanner 292. The first fixation lamp scanner 292V is configured to be driven by a drive signal having a predetermined scanning angle that offsets from an initial position to a predetermined position in a direction intersecting the scanning axis of the second fixation lamp scanner 292H. The predetermined scanning angle offset by the second fixation lamp scanner 292H may be determined by a scanning time determined from the position on the first optical scanner 22 corresponding to the position where the fixation target is presented when commonly driven with an initial value. In this way, the presentation position of the fixation target can be changed two-dimensionally by the scanning by the first fixation lamp scanner 292V and the second fixation lamp scanner 292H.

[0092] The configuration of offsetting the scanning by the above-described fixation lamp scanner 292 by a predetermined offset time tofs, and the first fixation lamp scanner 292V and the second fixation lamp scanner 292H are an example of the "modifying portion" of the technology of the present disclosure.

[0093] Incidentally, it is preferable that the attenuation of light is suppressed in the irradiation of the fundus with SLO light or OCT light and the reflected light reflected by the fundus. For this reason, it is more preferable to reduce the light attenuation at the reflection element 294 of the fixation unit 29 as much as possible. Therefore, with reference to FIG. 15, a configuration for reducing the light attenuation at the reflection element 294 of the fixation unit 29 as much as possible will be described as a second modification example.

[0094] FIG. 15 is a conceptual configuration diagram of a second modification. As shown in FIG. 15, the imaging optical system 19 of the second modification includes a specific reflection element 294M instead of the reflection element 294 shown in FIG. 5. The specific reflection element 294M is composed of a reflection region 294A that reflects the fixation light and a transmission region 294B that at least includes the scanning range of the SLO light or the OCT light by the scanning of the second optical scanner 24 (scanning in the direction indicated by the arrow Ro). In this way, since the specific reflection element 294M includes the transmission region 294B, it is possible to reduce the light attenuation of the SLO light or the OCT light when passing through the specific reflection element 294M.

[0095] Note that the fixation light is scanned by the fixation lamp scanner 292 (scanning in the direction indicated by the arrow Rc) across the reflection region 294A and the transmission region 294B. Therefore, when the fixation light passes through the transmission region 294B, it is not irradiated to the eye to be examined and is in a state of instantaneously turning off, and the fixation target is presented in a blinking state. Since the state where the fixation light instantaneously turns off is the time for passing through a part of the scanning range by the fixation lamp scanner 292, considering the afterimage phenomenon in the eye to be examined 12, it is assumed that the extinguishing time of the fixation light confirmed in the eye to be examined 12 is shorter than the time for the fixation light to pass through the transmission region 294B.

[0096] Also, when performing imaging processing by the SLO unit 18, since the visible light SLO light passes through the transmission region 294B in the state where the fixation light instantaneously turns off, the fixation target is presented in a state close to the state where the fixation light is continuously lit. On the other hand, when performing imaging processing by the OCT unit 18, it is possible to present the fixation target in a state close to the state where the fixation light is continuously lit by irradiating the visible light SLO light while the fixation light passes through the transmission region 294B.

[0097] Next, application examples of the technology of the present disclosure will be exemplified. The application example uses, in another device of the ophthalmic apparatus, a function of localizing the optical axis with respect to the eye to be examined 12 even when irradiating light through the first optical scanner 22 by including a scanner that is synchronously driven with the first optical scanner 22. Since the following application example has the same configuration as the above-described embodiment, the same parts are denoted by the same reference numerals and detailed description thereof is omitted.

[0098] Generally, when observing the eye to be examined, it is effective to photograph and observe the anterior segment of the eye to be examined 12. However, for photographing the anterior segment of the eye to be examined 12, in order to exclude the scanning by the first optical scanner 22, a complicated optical system for arranging the observation device at a position closer to the eye to be examined 12 than the first optical scanner 22 is required. On the other hand, as described above, by providing a specific scanner (fixation lamp scanner 292) that is synchronously driven with the first optical scanner 22, even for a specific optical system via the first optical scanner 22, it is possible to adopt a configuration that localizes the optical axis with respect to the eye to be examined 12. Therefore, by applying the function of the above-described fixation unit 29 to the observation device for observing the eye to be examined 12, the eye to be examined 12 can be easily observed. In addition, it becomes possible to arrange the observation device in the optical path via the first optical scanner 22, and the degree of freedom in device design increases.

[0099] The first application example is an example in which, by providing a scanner that is synchronously driven with the first optical scanner 22, the function of localizing the optical axis of the fixation lamp that irradiates the eye to be examined 12 even when irradiating the fixation light via the first optical scanner 22 is used in the anterior segment imaging device as an example of the observation device.

[0100] FIG. 16 schematically shows the configuration of the first application example. As shown in FIG. 16, the first application example is an application example in which an anterior segment observation optical system 500 including an anterior segment observation camera 502 and a lens group 504 for anterior segment observation is arranged instead of the fixation light source 291 (FIG. 5) of the fixation unit 29. The imaging surface of the anterior segment observation camera 502 of the anterior segment observation optical system 500 is arranged in a conjugate relationship with the pupil (pupil 27) of the eye to be examined 12.

[0101] As shown in FIG. 16, by arranging the anterior segment observation optical system 500 instead of the fixation light source 291 (FIG. 5), the position for observing the anterior segment of the eye to be examined 12 can be localized, and it becomes possible to stably observe the anterior segment of the eye to be examined 12.

[0102] In the first application example, the following disclosed technology is proposed. A scanning optical system that scans the eye with light from a light source, An observation unit that observes the eye through the scanning optical system, wherein the optical axis for observing the eye is changed in synchronization with the scanning of the scanning optical system so that a predetermined part of the eye does not move more than a predetermined distance from the predetermined part of the eye by the scanning of the scanning optical system. An ophthalmic apparatus comprising the same.

[0103] A second application example is an application example in which an anterior eye imaging device is further provided in the imaging optical system 19 (FIG. 5) according to the above-described embodiment. The second application example functions effectively when observing the test eye 12 while presenting a fixation target.

[0104] FIG. 17 schematically shows the configuration of the second application example. As shown in FIG. 17, in the second application example, an anterior eye observation optical system 510 is further arranged in the imaging optical system 19 including the above-described fixation unit 29 (FIG. 5). Note that the anterior eye observation optical system 510 shown in FIG. 17 has the same configuration as the anterior eye observation optical system 500 shown in FIG. 16, and thus the description thereof is omitted.

[0105] As shown in FIG. 17, the imaging optical system 19 according to the second application example can image and observe the anterior eye of the test eye 12 while presenting a fixation target by the fixation unit 29. That is, by arranging the anterior eye observation optical system 510 in addition to the fixation unit 29 (FIG. 5), even when the optical path by the anterior eye observation optical system 510 passes through the first optical scanner 22, the position for observing the anterior eye of the test eye 12 can be localized, and the anterior eye of the test eye 12 can be stably observed.

[0106] In the second application example, the following disclosed technology is proposed. A scanning optical system that scans the eye with light from a light source, A fixation light source that functions as a fixation target for irradiating fixation light to the eye through the scanning optical system, A fixation light scanning unit that scans the fixation light in synchronization with the scanning of the scanning optical system so that the fixation light irradiated from the fixation light source to a predetermined part of the eye does not move more than a predetermined distance from the predetermined part of the eye by the scanning of the scanning optical system. An observation unit that observes the eye through the scanning optical system, wherein the light axis for observing the eye is changed in synchronization with the scanning of the scanning optical system using the fixation light scanning unit so that a predetermined part of the eye does not move more than a predetermined distance from the predetermined part of the eye by the scanning of the scanning optical system. An ophthalmic apparatus comprising the same.

[0107] A third application example is an application of a function of localizing the optical axis of a fixation lamp irradiated to the eye to be examined 12 to a perimeter which is an example of spot illumination.

[0108] Fig. 18 schematically shows the configuration of the third application example. In the third application example, a perimeter optical system 600 is further arranged in the imaging optical system 19 including the above-described fixation unit 29 (Fig. 5). As shown in Fig. 18, the perimeter optical system 600 includes a perimeter light source 602, a two-dimensional changing unit 604, a mirror 606, and a mirror 608 provided on the optical path of the fixation unit 29.

[0109] The perimeter light source 602 is a light source having the same configuration as the fixation light source 291. The two-dimensional changing unit 604 is configured to be able to two-dimensionally change the light from the perimeter light source 602 so that the light spot Ls by the perimeter light source 602 can move within a predetermined measurement range on the fundus (retina) Fu of the eye to be examined 12. A mirror 606 and a mirror 608 are sequentially arranged on the light emission side of the two-dimensional changing unit 604. By configuring the perimeter optical system 600 in this way, it becomes possible to two-dimensionally illuminate the fundus of the eye to be examined 12 with light for perimeter measurement. For example, as shown in Fig. 18, it becomes possible to illuminate a light spot Lc by the irradiation of fixation light and a light spot Ls by the perimeter light source 602 at a position different from the light spot Lc on the fundus Fu of the eye to be examined 12.

[0110] Thus, in the third application example, while presenting a fixation target at a fixed point position by the irradiation of fixation light by the fixation unit 29, it is possible to illuminate the fundus of the eye to be examined 12 with light for perimeter measurement while two-dimensionally changing the light by the perimeter optical system 600, and it becomes possible to measure the visual field range of the eye to be examined 12.

[0111] In the third application example, the following disclosed technology is proposed. A scanning optical system that scans the eye with light from a light source, A fixation light source that functions as a fixation target that irradiates fixation light to the eye through the scanning optical system, A fixation light scanning unit that scans the fixation light in synchronization with the scanning of the scanning optical system so that the fixation light irradiated from the fixation light source to a predetermined part of the eye does not move more than a predetermined distance from the predetermined part of the eye by the scanning of the scanning optical system, A measurement unit that measures the visual field of the eye through the scanning optical system, and a changing unit that changes the optical axis for measuring the visual field of the eye in synchronization with the scanning of the scanning optical system using the fixation light scanning unit so that a predetermined part of the eye does not move more than a predetermined distance from the predetermined part of the eye by the scanning of the scanning optical system, An ophthalmic apparatus comprising:

[0112] Note that in the above, the ophthalmic apparatus 110 has a function of photographing, for example, a region with an internal irradiation angle of 200 degrees (an external irradiation angle of 167 degrees based on the pupil of the eyeball of the eye to be examined) with the center O of the eyeball of the eye to be examined 12 as a reference position, but is not limited to this angle of view. The internal irradiation angle may be 200 degrees or more (the external irradiation angle may be 167 degrees or more and 180 degrees or less).

[0113] Also, the specification may have an internal irradiation angle of less than 200 degrees (an external irradiation angle of less than 167 degrees). For example, the angle of view may be an internal irradiation angle of about 180 degrees (an external irradiation angle of about 140 degrees), an internal irradiation angle of about 156 degrees (an external irradiation angle of about 120 degrees), an internal irradiation angle of about 144 degrees (an external irradiation angle of about 110 degrees), etc. The numerical values are just examples.

[0114] In each of the examples described above, the case where the processing is realized by software using a computer is exemplified, but the technology of the present disclosure is not limited to this. For example, instead of software using a computer, an FPGA (Field-Programmable Gate Array) or an ASIC (Application Specific All kinds of processing may be executed only by hardware such as an Integrated Circuit. Some of the various processes may be executed by software, and the remaining processes may be executed by hardware.

[0115] Also, in each of the examples described above, the processor refers to a processor in a broad sense, including a general-purpose processor (e.g., CPU: Central Processing Unit, etc.) and a dedicated processor (e.g., GPU: Graphics Processing Unit, ASIC: Application Specific Integrated Circuit, FPGA: Field Programmable Gate Array, programmable logic device, etc.).

[0116] Also, the operation of the processor in the above embodiment may be achieved not only by one processor but also by a plurality of physically separated processors cooperating. Also, the order of each operation of the processor is not limited to the order described in each of the above examples and may be changed as appropriate.

Explanation of Signs

[0117] 12 Eye to be examined 14 Imaging device 16 Control device 28 Objective optical system 29 Fixation unit 30 Wide-angle optical system 100 Ophthalmic system 110 Ophthalmic device 130 Network 140 Server 150 Viewer

Claims

[Claim 1] an imaging unit including an optical scanner for irradiating the subject's eye with imaging light; a fixation unit including a fixation lamp scanner for irradiating a fixation target onto the subject's eye via the optical scanner; a control unit that drives the optical scanner and the fixation lamp scanner so as to continue projecting the fixation target at a first position of the subject's eye and to scan a first region of the subject's eye with the imaging light; An ophthalmic apparatus comprising:

Images