JP2022048635A - Ophthalmologic device and control method thereof - Google Patents

Abstract

To provide an ophthalmologic device capable of checking a fixation state of an eye to be examined while an intraocular distance of the eye to be examined is measured, and a control method thereof.SOLUTION: An ophthalmologic device includes: an interference optical system for detecting interference light between return light of measurement light and reference light, which includes a light scanning part for scanning the measurement light and an optical path length changing part for changing an optical path length of at least one of the measurement light and the reference light; a scanning control part for executing first scanning control for scanning the posterior eye part of an eye to be examined by the measurement light and second scanning control for scanning the anterior eye part of the eye to be examined by the measurement light; a first tomographic image generation part for generating a first tomographic image of the posterior eye part under the first canning control; a second tomographic image generation part for generating a second tomographic image of the anterior eye part under the second scanning control; and a display control part for displaying the first tomographic image generated by the first tomographic image generation part during the first scanning control on a display part, and displaying the second tomographic image generated by the second tomographic image generation part during the second scanning control on the display part.SELECTED DRAWING: Figure 5

Description

The present invention relates to an ophthalmic apparatus capable of photographing a tomographic image of an eye to be inspected and a control method thereof.

An ophthalmic apparatus for taking a tomographic image of an eye to be inspected using optical coherence tomography (OCT) is known (see Patent Document 1). This ophthalmic apparatus divides the light from the light source into the measurement light and the reference light, irradiates the test eye with the measurement light, and detects the interference light between the return light of the measurement light from the test eye and the reference light. It is equipped with an interference optical system. The interference optical system is provided with an optical scanning unit that scans the measurement light and an optical path length changing unit such as a corner cube or a reflector that changes the optical path length of at least one of the measurement light and the reference light. By controlling these optical scanning unit and optical path length changing unit, a desired portion of the eye to be inspected can be scanned with measurement light to obtain a tomographic image of the desired region. Then, by using this ophthalmic apparatus, it is possible to measure the intraocular distance between the anterior and posterior eye parts of the eye to be inspected, for example, the axial length between the apex of the cornea and the fovea centralis of the fundus.

For example, the ophthalmic apparatus described in Patent Document 2 scans the cornea and the fundus of the eye to be inspected with measurement light by an interference optical system, and scans the corneal tomographic image which is a tomographic image of the cornea and the tomographic image of the fundus which is a tomographic image of the fundus. To shoot. Then, this ophthalmologic apparatus determines the eye to be inspected based on the corneal tomographic image and the fundus tomographic image and the optical path length (for example, the position of the optical path length changing portion) of the reference light at the time of photographing each of the corneal tomographic image and the fundus tomographic image. Measure the axial length.

Non-Patent Document 1 discloses an ophthalmic apparatus that simultaneously displays a measurement result of the axial length of the eye to be inspected, a corneal tomographic image, and an image of a single point on the fundus of the eye to be inspected on a monitor. Has been done.

Japanese Unexamined Patent Publication No. 2019-213752 Japanese Unexamined Patent Publication No. 2020-44027

"ZEISS IOLMaster 700", [online], [Search on September 2, 2nd year of Reiwa], Internet <https://www.zeiss.com/meditec/int/product-portfolio/optical-biometers/iolmaster-700. html>

By the way, in order to accurately measure the intraocular distance, for example, the axial length of the eye to be inspected by using the ophthalmologic apparatus described in Patent Document 1, Patent Document 2, and Non-Patent Document 1, this measurement is in progress (measurement). It is necessary that the test eye can be fixed (stable) during scanning of the cornea and the fundus of the eye with light. However, in the ophthalmic apparatus described in Patent Document 1 and Patent Document 2, it is confirmed whether or not the eye to be fixed is fixed during the measurement of the intraocular distance (axis length), that is, the state of the fixed eye of the eye to be inspected. Can not do it.

Further, in the ophthalmic apparatus described in Non-Patent Document 1, the cornea is scanned by the measurement light based on the corneal tomographic image displayed on the monitor after the measurement of the axial length of the eye to be inspected (when the corneal tomographic image is taken). Although it is possible to confirm the fixative state of the optometry, it is not possible to confirm the fixative state of the eye to be inspected when scanning the cornea with the measurement light (when taking a tomographic image of the cornea). Therefore, in the ophthalmologic apparatus described in Non-Patent Document 1, it is possible to confirm whether or not the position of the fovea centralis of the fundus is at the position where it should be (for example, the central position of the fundus tomographic image) when scanning the fundus with the measurement light. Can not. Further, in the ophthalmic apparatus described in Non-Patent Document 1, it is not possible to confirm the fixative state of the eye to be inspected in real time during the measurement of the axial length of the eye to be inspected.

The present invention has been made in view of such circumstances, and an object of the present invention is to provide an ophthalmic apparatus capable of confirming the fixative state of the eye to be inspected while measuring the intraocular distance of the eye to be inspected, and a control method thereof. ..

The ophthalmic apparatus for achieving the object of the present invention divides the light from the light source into the measurement light and the reference light, irradiates the test eye with the measurement light, and returns the measurement light from the test eye and the reference light. An interference optical system that is an interference optical system that detects interference light with and has an optical scanning unit that scans the measurement light and an optical path length changing unit that changes the optical path length of at least one of the measurement light and the reference light. The first scanning control that controls the optical scanning unit and the optical path length changing unit to scan the posterior segment of the subject eye with the measurement light, and the second scanning control that scans the anterior segment of the subject eye with the measurement light. A scanning control unit that executes Based on the detection signal detected by the interference optical system under the two-scan control, the second tomographic image generator that generates the second tomographic image of the anterior segment of the eye and the first tomographic image generator that generates the second tomographic image during the first scan control are generated. It is provided with a display control unit for displaying the generated first tomographic image on the display unit and displaying the second tomographic image generated by the second tomographic image generation unit on the display unit during the second scanning control.

According to this ophthalmic apparatus, the fixative state of the eye to be inspected during the first scanning control and the second scanning control can be confirmed in real time.

In the ophthalmic apparatus according to another aspect of the present invention, the display control unit displays a guideline indicating a position where an image of a specific portion of the rear eye portion should be displayed on the screen of the display unit during the first scanning control. To display. This makes it possible to confirm the fixative state of the eye to be inspected during the first scanning control.

In the ophthalmic apparatus according to another aspect of the present invention, the display control unit causes the display unit to display a guideline indicating the position where the image of the fovea centralis of the posterior eye portion should be displayed as a specific site. This makes it possible to confirm whether or not the eye to be fixed is fixed during the first scanning control.

The ophthalmic apparatus according to another aspect of the present invention includes a specific site detection unit that detects an image of a specific site from the first tomographic image, and a display control unit detects the specific site detection unit during the first scanning control. Based on the result, the specific part in the first tomographic image is displayed on the display unit in an identifiable manner. This makes it possible to confirm the fixative state of the eye to be inspected during the first scanning control.

In the ophthalmic apparatus according to another aspect of the present invention, the detection signal detected by the interfering optical system in the first scanning control, the detection signal detected by the interfering optical system in the second scanning control, the first scanning control and the first scan control. 2 The intraocular distance calculation unit for calculating the intraocular distance between the anterior eye portion and the posterior eye portion based on the difference in the optical path length in the scanning control is provided.

In the ophthalmic apparatus according to another aspect of the present invention, the intraocular distance calculated by the intraocular distance calculation unit, the first tomographic image generated by the first tomographic image generation unit, and the second tomographic image generation unit generated by the second tomographic image generation unit. It is provided with a simultaneous display control unit that simultaneously displays two tomographic images on the display unit. This makes it possible to confirm the fixative state of the eye to be inspected during the first scanning control and the second scanning control.

In the ophthalmic apparatus according to another aspect of the present invention, the simultaneous display control unit changes the display interval between the first tomographic image and the second tomographic image according to the magnitude of the intraocular distance. This makes it possible to visually indicate the magnitude of the intraocular distance.

In the ophthalmic apparatus according to another aspect of the present invention, when the eye to be inspected is the left and right eyes, the first scan control and the second scan control by the scan control unit and the first tomographic image generation unit are performed for each of the left and right eyes. Generation of 1 tomographic image, generation of 2nd tomographic image by 2nd tomographic image generation unit, display of 1st tomographic image and 2nd tomographic image on display unit by display control unit, and eye by intraocular distance calculation unit The calculation of the internal distance is repeatedly executed, and the simultaneous display control unit simultaneously displays the intraocular distance for each of the left and right eyes, the first tomographic image, and the second tomographic image on the display unit. This makes it possible to simultaneously confirm the fixation states of the left and right eyes during the first scanning control and the second scanning control.

In the ophthalmic apparatus according to another aspect of the present invention, the simultaneous display control unit displays the intraocular distance, the first tomographic image, and the second tomographic image side by side for each of the left and right eyes on the display unit, and each eye is displayed for each eye. The display interval between the first tomographic image and the second tomographic image is changed according to the size of the internal distance. This makes it possible to visually indicate the length of the axial length of each of the left and right eyes.

In the ophthalmic apparatus according to another aspect of the present invention, when the posterior eye portion is the fundus of the eye to be inspected and the anterior eye portion is the cornea of the eye to be inspected, the intraocular distance calculation unit determines the eye of the inspected eye as the intraocular distance. Calculate the axis length.

The control method of the ophthalmic apparatus for achieving the object of the present invention is to divide the light from the light source into the measurement light and the reference light, irradiate the test eye with the measurement light, and return the measurement light from the test eye. It is an interference optical system that detects interference light between the light and the reference light, and has an optical scanning unit that scans the measurement light and an optical path length changing unit that changes the optical path length of at least one of the measurement light and the reference light. In the control method of the ophthalmologic apparatus provided with the interference optical system, the first scanning control in which the optical scanning unit and the optical path length changing unit are controlled to scan the posterior segment of the subject eye with the measurement light, and the anterior segment of the subject to be inspected are controlled. A first tomographic image of the posterior segment is generated based on the scanning control step for executing the second scanning control of scanning with the measurement light and the detection signal of the interference light detected by the interference optical system under the first scanning control. The first tomographic image generation step to generate a second tomographic image of the anterior segment of the eye based on the detection signal detected by the interference optical system under the second scanning control, and the first scanning control. Display control that displays the first tom image generated in the first tomographic image generation step on the display unit and displays the second tomographic image generated in the second tomographic image generation step on the display unit during the second scanning control. With steps.

INDUSTRIAL APPLICABILITY According to the present invention, the fixative state of the eye to be inspected can be confirmed during the measurement of the intraocular distance of the eye to be inspected.

It is a schematic diagram of the optical system of the ophthalmic apparatus which combined the autorefkeratometer and the OCT apparatus. It is a schematic diagram of the optical system of an OCT unit. It is a functional block diagram of a processing part. It is a functional block diagram of the main control part when the axial length measurement control is executed. It is explanatory drawing for demonstrating an example of the 1st live display screen in the case of the fixative of the eye to be examined. It is an enlarged view of the fundus tomographic image display area in FIG. It is explanatory drawing for demonstrating an example of the 1st live display screen at the time of not being able to fix the eye to be examined. It is explanatory drawing for demonstrating an example of the 2nd live display screen. It is explanatory drawing for demonstrating an example of a preview screen. It is explanatory drawing which showed an example of the axial length measurement information stored in the storage part. It is a flowchart which shows the flow of the measurement process of the axial length of the eye to be examined by the ophthalmic apparatus. It is explanatory drawing for demonstrating the modification of the preview screen generated by the preview screen generation part.

[Structure of optical system of ophthalmic appliance]
FIG. 1 is a schematic diagram of an optical system of an ophthalmic appliance 1000 (multifunction device) in which an autorefkeratometer and an OCT apparatus are combined. As shown in FIG. 1, the ophthalmic apparatus 1000 includes eye refractive power measurement (refraction measurement) and corneal shape measurement (kerato measurement) of the eye E to be inspected, imaging of a tomographic image of the eye E to be inspected using OCT, and intraocular parameters. Measure and perform.

The intraocular parameters include the axial length of the eye E to be inspected, the corneal thickness, the depth of the anterior chamber, the lens thickness, the radius of curvature of the strong main meridian of the anterior surface of the cornea, the radius of curvature of the weak main meridian of the anterior surface of the cornea, and the strong main meridian of the posterior surface of the cornea. Radius of curvature, weak main meridian radius of the posterior surface of the cornea, strong main meridian radius of the anterior surface of the lens, weak main meridian radius of the anterior surface of the crystalline lens, strong meridian radius of the posterior surface of the crystalline lens, and weak main meridian radius of curvature on the posterior surface of the lens. Take as an example.

The ophthalmic apparatus 1000 includes an alignment system 1, a kerato measurement system 3, a fixative projection system 4, an anterior ocular segment observation system 5, a reflex measurement optical system (ref measurement projection system 6 and a reflex measurement light receiving system 7). Includes OCT optical system 8. Further, the ophthalmic apparatus 1000 includes a measurement head 1002 (also referred to as an apparatus main body) for accommodating each of these optical systems and the like.

(Anterior eye observation system 5)
The anterior eye portion observation system 5 acquires an observation image P1 of the anterior segment of the eye to be inspected E, and more specifically, captures a moving image. The anterior segment observation system 5 includes an anterior segment illumination light source 50, an objective lens 51, a dichroic filter 52, an aperture 53 (telesen aperture), relay lenses 55 and 56, a dichroic filter 76, an imaging lens 58, and an imaging element 59. Be prepared. Further, the anterior eye portion observation system 5 has an observation system optical path LP1 from the objective lens 51 to the image pickup element 59.

The anterior eye illumination light source 50 irradiates the anterior segment of the eye E to be invisible illumination light, for example, infrared light having a wavelength of 940 nm. The observation system return light, which is the illumination light reflected by the anterior eye portion, passes through the objective lens 51, passes through the dichroic filter 52, passes through the hole formed in the aperture 53, and passes through the relay lenses 55 and 56. Then, it passes through the dichroic filter 76.

The dichroic filter 52 is a so-called long-pass filter that transmits light having a wavelength of around 940 nm used in the anterior segment observation system 5 and reflects light having a wavelength of around 840 nm used in the reflex measurement optical system and the OCT optical system 8 described later. do. As a result, the dichroic filter 52 branches (wavelength separation) the optical paths of both the ref measurement optical system and the OCT optical system 8 from the optical path of the anterior segment observation system 5. Further, the dichroic filter 52 synthesizes the optical paths of both the reflex measurement optical system and the OCT optical system 8 into the optical paths of the anterior ocular segment observation system 5.

The surface of the dichroic filter 52 that branches and combines each optical path is arranged so as to be inclined with respect to the optical axis of the objective lens 51. Further, instead of the dichroic filter 52, various optical elements that transmit light having a wavelength of about 940 nm and reflect (block) light having a wavelength of about 840 nm may be used.

The dichroic filter 76 transmits light having a wavelength of around 940 nm used in the anterior ocular segment observation system 5 and reflects light having a wavelength of around 840 nm used in the reflex measurement optical system and the OCT optical system 8 described later. As a result, the dichroic filter 76 synthesizes the optical path of the anterior segment observation system 5 and the optical path of the reflex measurement optical system (ref measurement light receiving system 7) branched from the optical path of the anterior segment observation system 5. The observation system return light transmitted through the dichroic filter 76 is imaged on the image pickup surface of the image pickup element 59 by the image pickup lens 58.

The image pickup element 59 is a known area sensor (area image sensor), and is shared by the anterior eye observation system 5 and the reflex measurement optical system (ref measurement light receiving system 7). The image pickup surface of the image pickup element 59 is arranged at the pupil conjugate position in the optical system passing through the anterior eye portion observation system 5. The pupil conjugate position is a position optically coupled to the pupil of the eye to be inspected E in a state where the alignment of the ophthalmologic apparatus 1000 with respect to the eye to be inspected E is completed, and a position optically coupled to the pupil or its vicinity thereof. It shall mean. The image pickup device 59 takes an image of the return light of the observation system imaged on the image pickup surface by the image pickup lens 58 at a predetermined rate and outputs a signal.

The image pickup signal (video signal) output from the image pickup element 59 is input to the processing unit 9 described later. When observing the anterior eye portion of the eye E to be inspected, the processing unit 9 causes the display unit 270 to display the observation image P1 (anterior eye portion image) based on the image pickup signal output from the image pickup element 59. The observation image P1 is, for example, an infrared moving image.

For the display unit 270, for example, a touch panel type liquid crystal monitor or the like is used to display the observation image P1. Further, the display unit 270 functions as a user interface unit, or displays various information under the control of the control unit 210 (see FIG. 3) of the processing unit 9 described later.

(Alignment system 1)
The alignment system 1 includes Z alignment in the Z direction (front-back direction, working distance direction) parallel to the optical axis of the anterior segment observation system 5 (objective lens 51) with respect to the eye E to be inspected, and a direction perpendicular to the optical axis [left-right direction]. (X direction), vertical direction (Y direction)] XY alignment. The alignment system 1 includes a stereo camera 14.

The stereo camera 14 is composed of a pair of cameras, and the anterior eye portion of the eye E to be inspected is photographed from different directions, and a pair of captured images of the anterior eye portion, a stereo image P2 (see FIG. 4), is described later. Is output to the processing unit 9 of. Although the details will be described later, the processing unit 9 automatically aligns the measurement head 1002 with respect to the eye E to be inspected in the XYZ direction based on the stereo image P2 input from the stereo camera 14. The number of cameras constituting the stereo camera 14 may be 3 or more.

(Kerato measurement system 3)
The kerato measurement system 3 is used for measuring the shape of the corneal Cr of the eye E to be inspected. The kerato measurement system 3 shares the objective lens 51 to the image pickup element 59 with the anterior eye observation system 5, and also projects infrared light, a pattern light (ring-shaped luminous flux) for measuring the corneal shape, onto the corneal Cr. It has a kerato plate 31 and a keratling light source 32.

The kerato plate 31 is arranged between the objective lens 51 and the eye E to be inspected. A keratling light source 32 is provided on the back surface side (objective lens 51 side) of the kerato plate 31. The kerato plate 31 is formed with a kerato pattern (transmissive portion) that transmits light from the keratling light source 32 along the circumference centered on the optical axis of the objective lens 51. The kerato pattern may be formed in an arc shape (a part of the circumference) centered on the optical axis of the objective lens 51. By illuminating the kerato plate 31 with the light from the keratling light source 32, the pattern light for measuring the shape of the cornea is projected onto the cornea Cr.

The reflected light (keratling image) from the corneal Cr is detected by the image pickup device 59 together with the observation image P1 of the anterior eye portion of the eye E to be inspected. The processing unit 9 calculates a corneal shape parameter representing the shape of the corneal Cr by performing a known calculation based on this keratling image.

(Ref measurement optical system: Ref measurement projection system 6 and Ref measurement light receiving system 7)
The reflex measurement optical system is used for reflex measurement for measuring the refractive power value of the eye E to be inspected. This reflex measurement optical system includes a reflex measurement projection system 6 and a reflex measurement light receiving system 7. The reflex measurement projection system 6 projects invisible light (infrared light) ring-shaped pattern light onto the fundus Ef of the eye E to be inspected. The reflex measurement light receiving system 7 receives the reflex system return light, which is the return light of the pattern light from the eye E to be inspected.

The reflex measurement projection system 6 is provided in an optical path branched by a perforated prism 65 provided on the optical path of the reflex measurement light receiving system 7. The hole portion formed in the hole opening prism 65 is arranged at the pupil conjugate position. The reflex measurement projection system 6 shares the objective lens 51 and the dichroic filter 52 with the anterior ocular segment observation system 5, and also has a reflex measurement light source 61, a relay lens 62, a conical prism 63, a ring aperture 64, and a perforated prism. A 65, a rotary prism 66, and a dichroic filter 67 are provided.

The reflex measurement light receiving system 7 shares the objective lens 51 to the perforated prism 65 with the reflex measurement projection system 6, and shares the dichroic filter 76 to the image pickup element 59 with the anterior eye observation system 5. Further, the reflex measurement light receiving system 7 includes a relay lens 71, a reflection mirror 72, a relay lens 73, a focusing lens 74, and a reflection mirror 75. Further, the reflex measurement light receiving system 7 has a branched optical path LP2 branched from the middle of the observation system optical path LP1 (dichroic filter 52).

As the ref measurement light source 61, for example, an SLD (Super Luminescent Diode) light source, which is a high-luminance light source, is used, and invisible light (infrared light) having a wavelength of 830 nm to 890 nm (840 nm in this embodiment) is emitted. Further, the reflex measurement light source 61 is movable in the optical axis direction and is arranged at the fundus conjugate position. The fundus conjugate position is a position optically conjugated with the fundus Ef of the eye to be inspected E in the state where the alignment is completed, and means a position optically conjugated with the fundus Ef or its vicinity. ..

The light output from the reflex measurement light source 61 passes through the relay lens 62 and is incident on the conical surface of the conical prism 63. The light incident on the conical surface is deflected and emitted from the bottom surface of the conical prism 63. The light emitted from the bottom surface of the conical prism 63 passes through the ring-shaped translucent portion formed in the ring diaphragm 64. The ring-shaped pattern light (ring-shaped luminous flux) that has passed through the translucent portion is reflected by the reflecting surface formed around the hole portion of the perforated prism 65, passes through the rotary prism 66, and is reflected by the dichroic filter 67. Will be done.

The dichroic filter 67 is replaced at the time of reflex measurement by the reflex measurement optical system and at the time of OCT measurement by the OCT optical system 8. As the dichroic filter 67, a filter that reflects light having a wavelength of around 840 nm at the time of ref measurement and transmits the visual target light from the fixative projection system 4 described later is used, and a filter that transmits light having a wavelength of around 840 nm at the time of OCT measurement is used. Used. As a result, the dichroic filter 67 branches (separates) the optical path of the OCT optical system 8 from the optical path of the reflex measurement optical system, and combines these two optical paths.

The light reflected by the dichroic filter 67 is reflected by the dichroic filter 52, passes through the objective lens 51, and is projected onto the eye E to be inspected. The rotary prism 66 is used to average the light amount distribution of the pattern light with respect to the blood vessels of the fundus Ef, the diseased part, and the like, and to reduce the speckle noise caused by the reflex measurement light source 61.

The ref-type return light, which is the return light of the ring-shaped pattern light projected on the fundus Ef, passes through the objective lens 51 and is reflected by the dichroic filter 52 and the dichroic filter 67. The ref-based return light reflected by the dichroic filter 67 passes through the rotary prism 66, passes through the hole portion of the perforated prism 65, passes through the relay lens 71, is reflected by the reflection mirror 72, and is reflected by the relay lens 73 and the combination. It passes through the focusing lens 74.

The focusing lens 74 can move along the optical axis of the reflex measurement light receiving system 7. The light that has passed through the focusing lens 74 is reflected by the reflection mirror 75, reflected by the dichroic filter 76, and imaged on the image pickup surface of the image pickup element 59 by the image pickup lens 58. The image pickup surface of the image pickup device 59 is arranged at the fundus conjugate position in the optical system via the reflex measurement light receiving system 7. The processing unit 9 calculates the refractive power value of the eye E to be inspected by performing a known calculation based on the image pickup signal output from the image pickup element 59. Refractive force values include, for example, spherical power, random vision power and random vision axis angle, or equivalent spherical power.

The reflex measurement light source 61 and the focusing lens 74 are the fundus Ef and the reflex measurement light source 61 based on the refractive power value of the eye E to be inspected obtained by using the reflex measurement optical system under the control of the processing unit 9 described later. And the image pickup element 59 are moved in the optical axis direction to positions where they are conjugated (see Patent Document 1 above).

(Fixation projection system 4)
The fixative projection system 4 is provided in an optical path branched from the optical path of the OCT optical system 8 described later by the dichroic filter 83.

The fixative projection system 4 presents the fixative to the eye E to be inspected. A fixative unit 40 is arranged in the optical path of the fixative projection system 4. The fixative unit 40 can move along the optical path of the fixative projection system 4 under the control of the processing unit 9 described later. The fixative unit 40 is movable along the optical path (optical axis) of the fixative projection system 4, and includes a liquid crystal panel 41. A relay lens 42 is arranged between the dichroic filter 83 and the fixative unit 40.

The liquid crystal panel 41 displays a pattern representing a fixative under the control of the processing unit 9, which will be described later. The liquid crystal panel 41 can arbitrarily change the display position of the pattern representing the fixative. As a result, the fixative position of the eye E to be inspected can be changed. The fixation positions of the eye E to be inspected include a position for acquiring an image centered on the macula of the fundus Ef, a position for acquiring an image centered on the optic disc, and an interval between the macula and the optic disc. There is a position for acquiring an image centered on the center of the fundus of the eye.

Further, the liquid crystal panel 41 is moved in the optical axis direction in conjunction with the movement of the reflex measurement light source 61 and the focusing lens 74 described above under the control of the processing unit 9 described later (see Patent Document 1).

The visual target light from the liquid crystal panel 41 passes through the relay lens 42, passes through the dichroic filter 83, passes through the relay lens 82, is reflected by the reflection mirror 81, is transmitted through the dichroic filter 67, and is reflected by the dichroic filter 52. Will be done. The target light reflected by the dichroic filter 52 passes through the objective lens 51 and is projected onto the fundus Ef. As a result, fixation (fixation in the line-of-sight direction) of the eye E to be inspected is executed.

(OCT optical system 8)
The OCT optical system 8 corresponds to the interference optical system of the present invention, and is an optical system for performing OCT measurement of the eye E to be inspected. The OCT optical system 8 is provided so as to be branched from the reflex measurement optical system. The OCT optical system 8 has a branched optical path LP3 branched (wavelength separation) from the optical path of the anterior segment observation system 5 by the dichroic filter 52 and branched from the optical path of the reflex measurement optical system by the dichroic filter 67. The optical path of the fixation projection system 4 described above is combined (coupled) with the branched optical path LP3 of the OCT optical system 8 by the dichroic filter 83. As a result, the optical axes of the OCT optical system 8 and the fixative projection system 4 can be coaxially coupled.

The OCT optical system 8 includes an objective lens 51, a dichroic filter 52, 67, a reflection mirror 81, a relay lens 82, a dichroic filter 83, a reflection mirror 84, a relay lens 85, a focusing lens 87, an optical scanner 88, and a collimeter lens unit 89. And has an OCT unit 100.

FIG. 2 is a schematic diagram of the optical system of the OCT unit 100. As shown in FIG. 2 and FIG. 1 described above, the OCT light source 101 of the OCT unit 100 is a wavelength sweep type capable of sweeping (scanning) the wavelength of the emitted light like the light source of a general swept source type OCT device. A (wavelength scanning type) light source, including a laser light source including a resonator. The OCT light source 101 changes the output wavelength with time in a near-infrared wavelength region that cannot be visually recognized by the human eye.

The OCT unit 100 is provided with an optical system for performing a swept source OCT. This optical system includes an interference optical system. This interference optical system has a function of dividing the light L0 from the OCT light source 101 into the measurement light LS and the reference light LR, and the OCT system return light LS1 and the reference light path which are the return light of the measurement light LS from the eye E to be inspected. It has a function of superimposing the reference light LR that has passed through to generate an interference light LC and a function of detecting the interference light LC. The detection result (detection signal) of the interference light LC obtained by the interference optical system is a signal showing the spectrum of the interference light LC and is sent to the processing unit 9.

In the OCT light source 101, for example, the wavelength of the emitted light (light L0) is in the same wavelength range as the wavelength range of the light emitted from the ref measurement light source 61 (including substantially the same, overlapping, and partially overlapping) in the vicinity of the wavelength of 860 nm (including substantially the same, overlapping, and partially overlapping). In this embodiment, it is set to 840 nm) and is changed at high speed. The light L0 output from the OCT light source 101 is guided to the polarization controller 103 by the optical fiber 102, and its polarization state is adjusted. The light L0 whose polarization state has been adjusted is guided to the fiber coupler 105 by the optical fiber 104, and is divided into the measurement light LS and the reference light LR by the fiber coupler 105.

The reference light LR is guided to the collimator 111 by the optical fiber 110, converted into a parallel light flux, passes through the optical path length correction member 112 and the dispersion compensation member 113, and is guided to the corner cube 114. The optical path length correction member 112 acts to match the optical path length of the reference light LR with the optical path length of the measured light LS. The dispersion compensating member 113 acts to match the dispersion characteristics between the reference light LR and the measurement light LS.

The corner cube 114 (retroreflector) and the corner cube moving mechanism 115 correspond to the optical path length changing portion of the present invention. The corner cube 114 is movably held along the incident direction of the reference light LR by the corner cube moving mechanism 115. The corner cube moving mechanism 115 is an actuator that moves the corner cube 114 along the incident direction of the reference light LR, thereby changing the optical path length of the reference light LR.

The reference light LR via the corner cube 114 is converted from a parallel luminous flux to a focused luminous flux by a collimator 116 via a dispersion compensating member 113 and an optical path length correction member 112, and is incident on the optical fiber 117. The reference light LR incident on the optical fiber 117 is guided by the polarization controller 118 to adjust its polarization state, is guided to the attenuator 120 by the optical fiber 119 to adjust the amount of light, and is guided to the fiber coupler 122 by the optical fiber 121.

On the other hand, the measurement light LS generated by the fiber coupler 105 is guided by the optical fiber f1 and converted into a parallel luminous flux by the collimator lens unit 89. The measurement light LS converted into the parallel light beam is reflected by the dichroic filter 83 via the focusing lens 87, the relay lens 85, and the reflection mirror 84.

The focusing lens 87 can move in the optical axis direction (the optical axis direction of the objective lens 51, the optical axis direction of the OCT optical system 8). The focusing lens 87 is moved in the optical axis direction in conjunction with the movement of the focusing lens 74 under the control of the processing unit 9 described later. Further, in the focusing lens 87, the end face of the optical fiber f1 is coupled to the measurement site (fundus Ef or the anterior eye portion) and the optical system based on the reflex measurement result of the eye E to be inspected performed before the OCT measurement. The position is adjusted to.

The optical scanner 88 corresponds to the optical scanning unit of the present invention, and is used by, for example, a MEMS (Micro Electro Mechanical Systems) scanner, a galvano mirror, a polygon mirror, a rotating mirror, a dowel prism, a double dowel prism, a rotation prism, and the like. Be done. The optical scanner 88 two-dimensionally deflects the measurement light LS, for example, scans the imaging site (corneal Cr, fundus Ef, etc.) in the horizontal and vertical directions orthogonal to the optical axis of the OCT optical system 8. The measurement light LS is deflected to. Scanning modes of such measurement light LS include, for example, horizontal scan, vertical scan, cross scan, radial scan, circular scan, concentric circular scan, and spiral scan.

The measurement light LS reflected by the dichroic filter 83 passes through the relay lens 82, is reflected by the reflection mirror 81, is transmitted through the dichroic filter 67, is reflected by the dichroic filter 52, is refracted by the objective lens 51, and is refracted by the objective lens 51. Incident to. The OCT system return light LS1 (corresponding to the return light of the present invention), which is the return light of the measurement light LS from the eye E to be inspected, travels in the same path as the outward path in the opposite direction and is guided to the fiber coupler 105, and further, the optical fiber 128. Reach the fiber coupler 122 via.

The fiber coupler 122 generates an interference light LC between the OCT system return light LS1 incident via the optical fiber 128 and the reference light LR incident via the optical fiber 121. Further, the fiber coupler 122 generates a pair of interference light LCs by branching the interference light LC at a predetermined branching ratio (for example, 1: 1). The pair of interference light LCs are guided to the detector 125 through the optical fibers 123 and 124, respectively.

The detector 125 is, for example, a balanced photodiode. The balanced photodiode includes a pair of photodetectors that detect each pair of interference light LCs, and outputs the difference between the pair of detection results obtained by these photodetectors. The detector 125 sends this output (detection signal) to the DAQ 130 which is a data acquisition device (Data Acquisition System).

A clock KC is supplied to the DAQ 130 from the OCT light source 101. The OCT light source 101 generates a clock KC in synchronization with the output timing of each wavelength of the light L0 swept within a predetermined wavelength range. The OCT light source 101 optically delays one of the two branched lights obtained by branching the light L0 of each output wavelength, and then sets the clock KC based on the result of detecting these combined lights. Generate. The DAQ 130 samples the detection signal input from the detector 125 based on the clock KC.

Further, the DAQ 130 sends the sampling result of the detection signal from the detector 125 to the arithmetic processing unit 220 (see FIG. 3) of the processing unit 9. The arithmetic processing unit 220 forms a reflection intensity profile in each A line by, for example, performing a Fourier transform or the like on the spectral distribution based on the sampling data for each series of wavelength scans (for each A line). Further, the arithmetic processing unit 220 forms image data (B scan image) by imaging the reflection intensity profile of each A line.

[Structure of processing unit 9]
FIG. 3 is a functional block diagram of the processing unit 9.

As shown in FIG. 3, the processing unit 9 includes an arithmetic circuit composed of various processors (Processor), a memory, and the like. Various processors include CPU (Central Processing Unit), GPU (Graphics Processing Unit), ASIC (Application Specific Integrated Circuit), and programmable logic devices [for example, SPLD (Simple Programmable Logic Devices), CPLD (Complex Programmable Logic Device), And FPGA (Field Programmable Gate Arrays)] and the like. The various functions of the processing unit 9 may be realized by one processor, or may be realized by a plurality of processors of the same type or different types. The processing unit 9 functions as a control unit 210 and an arithmetic processing unit 220 by reading and executing a program stored in a storage circuit or a storage device (not shown).

Further, in addition to the respective parts of the ophthalmic apparatus 1000 described above, the processing unit 9 includes a moving mechanism 200, moving mechanisms 40D and 80D, moving mechanisms 61D and 74D, an operation unit 280, and a communication unit 290. It is connected.

(Movement mechanism 200)
The movement mechanism 200 corresponds to the relative movement mechanism of the present invention, and moves the measurement head 1002 relative to the eye E to be inspected in the XYZ directions (front-back, left-right, up-down directions). The moving mechanism 200 is provided with an actuator that generates a driving force for moving the measurement head 1002 and a transmission mechanism that transmits the driving force. The actuator is composed of, for example, a pulse motor. The transmission mechanism is composed of, for example, a combination of gears or a rack and pinion. The moving mechanism 200 moves the measuring head 1002 under the control of the control unit 210 (main control unit 211).

(Movement mechanism 40D, 80D, 61D, 74D)
The moving mechanism 40D moves the fixation unit 40 (liquid crystal panel 41) in the optical axis direction of the fixation projection system 4 (the optical axis direction of the objective lens 51). The moving mechanism 80D moves the focusing lens 87 of the OCT optical system 8 in the optical axis direction of the OCT optical system 8 (the optical axis direction of the objective lens 51). The moving mechanism 61D moves the reflex measuring light source 61 of the reflex measuring projection system 6 in the optical axis direction thereof. The moving mechanism 74D moves the focusing lens 74 of the reflex measurement light receiving system 7 in the optical axis direction thereof.

Each of the moving mechanisms 40D, 80D, 61D, and 74D includes an actuator that generates a driving force and a transmission mechanism that transmits the driving force, similarly to the moving mechanism 200. Although specific description of each moving mechanism 40D, 80D, 61D, 74D is omitted, the fixation unit 40, the focusing lens 87, the reflex measurement light source 61, and the control unit 210 (main control unit 211) control the fixation unit 40, the focusing lens 87, and the reflex measuring light source 61. And the focusing lens 74 is moved (see Patent Document 1 above).

(Operation unit 280)
The operation unit 280 receives inputs for various operations of the ophthalmic apparatus 1000. The operation unit 280 includes various hardware keys (operation levers, buttons, switches, etc.) provided in the ophthalmologic device 1000. Further, the operation unit 280 also includes various software keys (buttons, icons, menus, etc.) displayed on the display screen of the touch panel type display unit 270.

(Communication unit 290)
The communication unit 290 has a function for communicating with an external device (not shown). The communication unit 290 includes a communication interface according to the connection form with the external device. An example of an external device is a spectacle lens measuring device that measures the optical characteristics of a lens. Further, the external device may be an arbitrary ophthalmic device, a device (reader) for reading information from a recording medium, a device (writer) for writing information on a recording medium, or the like. Further, the external device may be a hospital information system (HIS) server, a DICOM (Digital Imaging and Communications in Medicine) server, a doctor terminal, a mobile terminal, a personal terminal, a cloud server, or the like. Furthermore, the external device may be a remote control device that remotely controls the ophthalmic device 1000. The communication unit 290 may be provided in, for example, the processing unit 9.

(Control unit 210)
The control unit 210 includes the above-mentioned processor and controls each unit of the ophthalmic apparatus 1000. The control unit 210 includes a main control unit 211 and a storage unit 212. The storage unit 212 stores a computer program for controlling the ophthalmic apparatus 1000 and various data.

The computer programs stored in the storage unit 212 include a control program for controlling the operation of each part of the ophthalmic apparatus 1000, a control program for causing the ophthalmic apparatus 1000 to perform various measurements and measurements, and arithmetic processing by the arithmetic processing unit 220. A control program for, and is included. When the main control unit 211 operates according to such a computer program, the control unit 210 executes the control process.

The data stored in the storage unit 212 includes, for example, measurement results of objective measurement (refractive power value, corneal shape), tomographic image data, fundus image image data, and eye information to be inspected. The eye test information includes information about the subject such as a patient ID (identification) and a name, and information about the test eye E such as left and right eye information indicating whether the test eye E is the left or right eye.

Further, the storage unit 212 of the present embodiment stores the axial length measurement information 320 (see FIG. 10), which will be described later, showing the measurement result of the axial length of the eye to be inspected E.

The main control unit 211 performs various controls of the ophthalmic apparatus 1000. These various controls include alignment control related to the alignment of the measurement head 1002 with respect to the eye to be inspected E, kerato measurement control related to the measurement of the corneal shape of the eye to be inspected E (kerato measurement), and measurement of the optical refractive power of the eye to be inspected E (ref measurement). ), And a plurality of known controls such as OCT measurement control related to OCT measurement (tomographic image imaging and intraocular parameter calculation) of the eye E to be inspected are included. Since the kerato measurement control and the reflex measurement control are known techniques (see, for example, Patent Document 1), specific description thereof will be omitted here.

(Alignment control)
The main control unit 211 controls the alignment system 1 and the movement mechanism 200 before the OCT measurement to perform alignment control. For example, the main control unit 211 causes the stereo camera 14 of the alignment system 1 to take an image of the anterior eye portion of the eye to be inspected E, and makes known the three-dimensional position of the eye to be inspected E based on the stereo image P2 taken by the stereo camera 14. (For example, see Japanese Patent Application Laid-Open No. 2013-248376) for alignment detection. Then, the main control unit 211 drives the movement mechanism 200 based on the alignment detection result to move the measurement head 1002 back and forth, left and right, up and down, thereby executing the auto-alignment of the measurement head 1002 with respect to the eye E to be inspected.

(OCT measurement control)
After the auto alignment is completed, the main control unit 211 controls the OCT optical system 8 and the arithmetic processing unit 220 to perform OCT measurement control for performing OCT measurement of the eye E to be inspected. Before starting the OCT measurement control, the main control unit 211 controls the liquid crystal panel 41 of the fixative projection system 4 to present the fixative target to the eye E to be inspected. Further, the main control unit 211 changes the optical path length of the reference light LR to, for example, an optical path length corresponding to the imaging of a tomographic image of the fundus Ef by driving the corner cube moving mechanism 115 to move the corner cube 114. Or, change the optical path length to correspond to the imaging of the tomographic image of the corneal Cr.

The main control unit 211 controls the OCT optical system 8 to turn on the OCT light source 101 of the OCT unit 100 and start the operation of the optical scanner 88 to start the operation of the optical scanner 88 to determine a predetermined portion (anterior eye portion, front eye portion) of the eye to be inspected E. The fundus Ef, or both) is scanned with the measurement light LS. Further, the main control unit 211 controls the OCT optical system 8 to detect the pair of interference light LCs by the detector 125, output the detection signal, and sample the detection signal by the DAQ 130, and then perform this detection. The signal sampling result is input to the arithmetic processing unit 220. Further, the main control unit 211 causes the arithmetic processing unit 220 to form a tomographic image based on the sampling result of the detection signal and to calculate the intraocular parameter.

(Arithmetic processing unit 220)
The arithmetic processing unit 220 includes an optical power calculation unit 221A, a corneal shape calculation unit 221B, an image formation unit 222, a data processing unit 223, and an intraocular distance calculation unit 224.

Under the control of the main control unit 211, the optical power calculation unit 221A analyzes the captured image (ring image) of the fundus Ef captured by the image pickup element 59 during the reflex measurement of the eye to be inspected E by a known method, and receives the subject. The refractive power value (spherical power, astigmatic power, and astigmatic axis angle) of the optometry E is calculated. Further, the corneal shape calculation unit 221B analyzes the observation image P1 imaged by the image pickup element 59 at the time of measuring the kerato of the eye to be inspected E by a known method under the control of the main control unit 211, and the corneal shape of the eye to be inspected E. (Corneal refractive power, corneal astigmatism, and corneal astigmatism axis angle) are calculated.

Under the control of the main control unit 211, the image forming unit 222 performs the same filter processing and high speed as the conventional spectral domain type OCT based on the sampling result of the detection signal input through the detector 125 and the DAQ 130 at the time of OCT measurement. The image data (B scan image) of the tomographic image of the eye E to be inspected is formed by executing the Fourier transform process or the like.

The data processing unit 223 performs various data processing (image processing) and analysis processing on the tomographic image formed by the image forming unit 222 under the control of the main control unit 211. For example, the data processing unit 223 executes correction processing such as luminance correction and dispersion correction for each tomographic image. Further, the data processing unit 223 also performs various image processing and analysis processing on the observation image P1 of the anterior eye portion of the eye E to be inspected obtained by using the anterior eye portion observation system 5.

The intraocular distance calculation unit 224, under the control of the main control unit 211, has an intraocular distance between an arbitrary region (site) of the anterior eye portion (cornea Cr) of the eye E to be inspected and an arbitrary region of the posterior eye portion (fundus Ef). Perform the calculation of. This intraocular distance includes the axial length, which is the distance between the apex of the cornea of the cornea Cr and the fovea Fc (see FIG. 5) of the fundus Ef. Therefore, the OCT measurement control by the main control unit 211 described above includes the axial length measurement control for measuring the axial length of the eye to be inspected E as an intraocular parameter of the eye to be inspected E.

FIG. 4 is a functional block diagram of the main control unit 211 when the axial length measurement control is executed. In FIG. 4, the configuration of the ophthalmic apparatus 1000 and the functions of the main control unit 211 and the arithmetic processing unit 220, which are not directly related to the axial length measurement control, are not shown.

As shown in FIG. 4, when the main control unit 211 executes the axial length measurement control, that is, when the operation unit 280 or the like performs the measurement start operation of the axial length of the eye E to be inspected, the image acquisition unit 300 , Alignment control unit 302, scanning control unit 304, tomographic image generation control unit 306, specific site detection unit 308, display control unit 310, and preview screen generation unit 312. The measurement start operation also includes an operation of inputting eye test information (patient ID, left and right eye identification information).

The image acquisition unit 300 acquires the observation image P1 of the anterior eye portion of the eye subject E from the anterior eye portion observation system 5 in response to the operation of starting the measurement of the axial length of the eye subject E, and outputs the observation image P1 to the display control unit 310. Hereinafter, the image acquisition unit 300 acquires the observation image P1 from the anterior eye portion observation system 5 and outputs the observation image P1 to the display control unit 310 until the measurement of the axial length of the eye to be inspected E is completed. And execute.

The alignment control unit 302 acquires the stereo image P2 from the stereo camera 14, performs alignment detection, and auto-alignment, as described in the above-mentioned alignment control, according to the operation of starting the measurement of the axial length of the eye to be inspected E. To execute. Further, the alignment control unit 302 acquires the stereo image P2 from the stereo camera 14 and outputs the stereo image P2 to the display control unit 310 until the measurement of the axial length of the eye to be inspected E is completed. do.

The scanning control unit 304 controls the OCT optical system 8, that is, the scanning of the eye E to be inspected by the measurement light LS. After the auto-alignment of the measurement head 1002 is completed, the scanning control unit 304 controls the corner cube moving mechanism 115 and the optical scanner 88 to scan the fundus Ef (B scan) with the measurement light LS, and the measurement light. The second scanning control of scanning the corneal Cr (B scan) by the LS is executed in order. In the first scanning control, the OCT optical system 8 scans the measured light LS (B scan) on the fundus Ef and detects the interference light LC a plurality of times. Further, in the second scanning control, the OCT optical system 8 scans the measurement light LS (B scan) on the corneal Cr and detects the interference light LC a plurality of times.

Since the first scanning control and the second scanning control (including changing the optical path length of the reference light LR by moving the corner cube 114) are known techniques, specific description thereof will be omitted here (for example, Patent Document 2). Etc.). Further, instead of executing the second scanning control after the first scanning control, the first scanning control may be executed after the second scanning control.

The tomographic image generation control unit 306 functions as the first tomographic image generation unit and the second tomographic image generation unit of the present invention together with the image formation unit 222 described above.

Specifically, when the first scanning control is started, the tomographic image generation control unit 306 controls the image forming unit 222 based on the sampling result of the detection signal input via the detector 125 and the DAQ 130. The fundus tomographic image P3 (corresponding to the first tomographic image of the present invention), which is a tomographic image of the fundus Ef, is generated. As a result, every time the fundus Ef is scanned (B scan) by the measurement light LS in the first scanning control, a new fundus tomographic image P3 is generated by the image forming unit 222. The fundus tomographic image P3 is sequentially output from the image forming unit 222 to the display control unit 310.

Further, when the second scanning control is started, the tomographic image generation control unit 306 controls the image forming unit 222 based on the sampling result of the detection signal input via the detector 125 and the DAQ 130, and controls the corneal Cr. The corneal tomographic image P4 (corresponding to the second tomographic image of the present invention), which is a tomographic image of the above, is generated. As a result, each time the scanning of the cornea Cr by the measurement light LS (B scan) is executed in the second scanning control, the image forming unit 222 generates a new corneal tomographic image P4. The corneal tomographic image P4 is sequentially output from the image forming unit 222 to the display control unit 310.

The specific site detection unit 308 uses a known image analysis method every time the fundus tomographic image P3 is generated by the image forming unit 222 during the first scanning control, and the inspected eye E (fundus) from within the fundus tomographic image P3. The image of the fovea Fc (see FIG. 5), which is an image of a specific site of Ef), is detected. Since the fovea Fc has a recessed shape smaller than that of the optic nerve head, the image of the fovea Fc can be easily detected by detecting the small recessed shape from the fundus tomographic image P3. Then, each time the specific site detection unit 308 detects the image of the fovea Fc from the fundus tomographic image P3, the specific site detection unit 308 displays the foveal detection information indicating the position and range of the image of the fovea Fovea in the fundus tomographic image P3. Output to the control unit 310.

[1st live display screen 400A]
When the first scanning control is started, the display control unit 310 generates a first live display screen 400A showing the state of the eye to be inspected E during the first scanning control and displays it on the display unit 270. Specifically, the display control unit 310 includes eye information to be inspected input from the operation unit 280, an observation image P1 sequentially input from the image acquisition unit 300, and a stereo image P2 sequentially input from the alignment control unit 302. The first live display screen 400A is generated based on the fundus tomographic image P3 sequentially input from the tomographic image generation control unit 306 and the foveal detection information input for each fundus tomographic image P3 from the specific site detection unit 308. Is displayed on the display unit 270.

FIG. 5 is an explanatory diagram for explaining an example of the first live display screen 400A in the case where the eye E to be inspected is fixed (when the alignment is appropriate). FIG. 6 is an enlarged view of the fundus tomographic image display area 408 in FIG. FIG. 7 is an explanatory diagram for explaining an example of the first live display screen 400A when the eye to be inspected E cannot be fixed. As shown in FIGS. 5 to 7 and FIG. 4 described above, the first live display screen 400A has a left and right eye information area 402, an observation image display area 404, a stereo image display area 406, and a fundus tomographic image. Includes a display area 408.

The left and right eye information area 402 is an area for displaying which of the left and right eyes is the eye E to be inspected. The display control unit 310 controls the display of the left and right eye information areas 402 based on the eye-tested information input from the operation unit 280. Here, the left and right eye information regions 402 in FIGS. 5 and 7 indicate that the eye to be inspected E is the right eye. The display mode of the left and right eye information region 402 is not particularly limited as long as it is possible to determine whether the eye to be inspected E is the left or right eye.

The observation image display area 404 is an area for displaying the observation image P1. The display control unit 310 causes the observation image P1 to be lively displayed in the observation image display area 404 based on the observation image P1 sequentially input from the image acquisition unit 300. This makes it possible to confirm the observation image P1 (anterior eye portion) during the first scanning control in real time.

The stereo image display area 406 is an area for displaying the stereo image P2. The display control unit 310 causes the stereo image P2 to be live-displayed in the stereo image display area 406 based on the stereo image P2 sequentially input from the alignment control unit 302. As a result, the stereo image P2 (anterior eye portion) under the first scanning control can be confirmed in real time.

The fundus tomographic image display area 408 is an area for displaying the fundus tomographic image P3. The display control unit 310 causes the fundus tomographic image P3 to be lively displayed in the fundus tomographic image display area 408 based on the fundus tomographic image P3 sequentially input from the tomographic image generation control unit 306. This makes it possible to confirm the fundus tomographic image P3 during the first scanning control in real time.

At this time, the display control unit 310 sets an index 410 indicating the position of the fovea Fc in the fundus tomographic image P3 based on the foveal detection information input from the specific site detection unit 308 for each fundus tomographic image P3. It is superimposed and displayed on the fundus tomographic image P3 in the image display area 408. Thereby, the image of the fovea Fc in the fundus tomographic image P3 displayed in the fundus tomographic image display area 408 can be easily identified.

In addition, instead of superimposing the index 410 on the fundus tomographic image P3 in the fundus tomographic image display area 408, the display control unit 310 in the fundus tomographic image display area 408 in various display modes capable of identifying the fovea Fc. The fundus tomographic image P3 may be displayed.

Further, the display control unit 310 displays two types of the first guideline 412 and the second guideline 414 in the fundus tomographic image display area 408.

The first guideline 412 corresponds to the guideline of the present invention, and is a position where the image of the fovea Fc is to be displayed in the fundus tomographic image display area 408 (in the screen of the display unit 270), for example, the fundus tomographic image display. The central part of the region 408 is shown. As a result, is the position of the image of the fovea Fc in the fundus tomographic image P3 within the position range defined by the first guideline 412 (see FIGS. 5 and 6) or outside this position range (FIG. 6). 7), it is possible to easily confirm whether or not the eye E to be inspected has been fixed in the first scan control, that is, the state of fixation.

The second guideline 414 is a line obtained by dividing the fundus tomographic image display area 408 into two in the vertical direction. By photographing the fundus tomographic image P3 so that the fundus tomographic image P3 (the region showing the cross section of the fundus Ef) is located above the second guideline 414 in the fundus tomographic image display area 408, the fundus tomographic image P3 can be obtained. The image quality is good. Therefore, the second guideline 414 indicates the position where the fundus tomographic image P3 should be displayed in the fundus tomographic image display area 408.

[Second live display screen 400B]
FIG. 8 is an explanatory diagram for explaining an example of the second live display screen 400B. As shown in FIG. 8 and FIG. 4 described above, the display control unit 310 displays the second live display screen 400B showing the state of the eye to be inspected E during the second scanning control when the second scanning control is started. Is generated and displayed on the display unit 270. Specifically, the display control unit 310 includes eye information to be inspected input from the operation unit 280, an observation image P1 sequentially input from the image acquisition unit 300, and a stereo image P2 sequentially input from the alignment control unit 302. Based on the corneal tomographic image P4 sequentially input from the tomographic image generation control unit 306, the second live display screen 400B is generated and displayed on the display unit 270.

The second live display screen 400B includes a left and right eye information area 402, an observation image display area 404, and a stereo image display area 406 similar to the first live display screen 400A, as well as a corneal tomographic image display area 420.

The corneal tomographic image display area 420 is an area for displaying the corneal tomographic image P4. The display control unit 310 causes the corneal tomographic image P4 to be lively displayed in the corneal tomographic image display area 420 based on the corneal tomographic image P4 sequentially input from the tomographic image generation control unit 306. As a result, the corneal tomographic image P4 under the second scanning control can be confirmed in real time. As a result, based on the observation image P1 and the corneal tomographic image P4, it is possible to easily confirm whether or not the eye E to be inspected has been fixed in the second scanning control, that is, the fixation state.

Although not shown, when the corneal tomographic image P4 is displayed live in the corneal tomographic image display area 420, the image of a specific part in the corneal tomographic image P4, for example, the image of the corneal apex may be displayed in an identifiable manner. good. In this case, every time the image forming unit 222 generates the corneal tomographic image P4, the specific site detecting unit 308 detects the image of the corneal apex from within the corneal tomographic image P4.

Although not shown, the first guideline 412 indicating the position where the image of the corneal apex should be displayed is displayed in the corneal tomographic image display area 420, and the corneal tomographic image P4 is displayed in the corneal tomographic image display area 420. The second guideline 414, which indicates the position to be performed, may be displayed.

[Intraocular distance calculation unit 224]
Returning to FIG. 4, the intraocular distance calculation unit 224 calculates the axial length of the eye to be inspected E after the completion of the first scanning control and the second scanning control. The intraocular distance calculation unit 224 includes a detection signal (funeral tomographic image P3) for each B scan detected by the OCT optical system 8 in the first scanning control and a B scan detected by the OCT optical system 8 in the second scanning control. The detection signal (corner tomographic image P4) for each, and the optical path length difference (movement amount of the corner cube 114) of the optical path length of the reference light LR in the first scanning control and the optical path length of the reference light LR in the second scanning control. get. Then, the intraocular distance calculation unit 224 calculates the axial length of the eye to be inspected E based on these acquisition results. Since the specific calculation method of the axial length is a known technique (see, for example, Patent Document 2 above), the description thereof will be omitted here.

When the eye to be inspected E is the left and right eyes (both eyes), each part of the main control unit 211 (from the image acquisition unit 300 to the display control unit 310) and the intraocular distance calculation unit 224 operate repeatedly for each of the left and right eyes. .. As a result, for each of the left and right eyes, the above-mentioned auto-alignment, the first scanning control and the second scanning control, the generation of the fundus tomographic image P3 and the corneal tomographic image P4, the detection of the image of the foveal Fc, and the first. The display of the live display screen 400A and the second live display screen 400B and the calculation of the axial length are repeatedly executed.

[Preview screen generator 312 and preview screen 500]
The preview screen generation unit 312 functions as the simultaneous display control unit of the present invention together with the display control unit 310. The preview screen generation unit 312 operates after the calculation of the axial length of the eye to be inspected E (left and right eyes) is completed by the intraocular distance calculation unit 224, and the calculation result of the axial lengths of the left and right eyes by the intraocular distance calculation unit 224. And, the preview screen 500 is generated based on the fundus tomographic image P3 and the corneal tomographic image P4 for each of the left and right eyes formed by the image forming unit 222. Then, the preview screen generation unit 312 causes the display unit 270 to display the preview screen 500 via the display control unit 310.

FIG. 9 is an explanatory diagram for explaining an example of the preview screen 500. As shown in FIG. 9, the preview screen 500 is a screen in which the axial length, the fundus tomographic image P3, and the corneal tomographic image P4 are simultaneously displayed for each of the left and right eyes, which are the eyes to be inspected E. The preview screen 500 includes a right eye display area 500R and a left eye display area 500L.

The right eye display area 500R includes a left and right eye information area 502R, an axial length display area 504R, a right eye corneal tomographic image P4, and a right eye fundus tomographic image P3 from the upper part of the screen to the lower part of the screen. Are displayed side by side. Further, in the display area 500L for the left eye, from the upper part of the screen to the lower part of the screen, the left and right eye information area 502L, the axial length display area 504L, the corneal tomographic image P4 of the left eye, and the fundus tomographic image of the left eye are included. P3 and P3 are displayed side by side.

In the left and right eye information region 502R, a display (for example, "R") indicating that the eye to be inspected E is the "right eye" is made. Further, in the left and right eye information area 502L, a display (for example, "L") indicating that the eye to be inspected E is the "left eye" is made.

In the axial length display area 504R, the calculation result of the axial length of the eye to be inspected E (right eye) is displayed. Further, in the axial length display area 504L, the calculation result of the axial length of the eye to be inspected E (left eye) is displayed.

In this way, by displaying the calculation result of the axial length, the corneal tomographic image P4, and the fundus tomographic image P3 side by side for each eye E (left and right eye) to be examined on the preview screen 500, the first scanning control is performed for each left and right eye. And the fixative state of the eye E to be inspected at the time of the second scanning control can be confirmed. As a result, it is possible to confirm whether or not the axial length of each of the left and right eyes is accurately measured.

FIG. 10 is an explanatory diagram showing an example of the axial length measurement information 320 stored in the storage unit 212. As shown in FIG. 10 and FIG. 4 described above, the main control unit 211 stores the measurement result of the axial length of the eye to be inspected E (left and right eyes) in the operation unit 280 after the preview screen 500 is displayed by the display unit 270. When the operation is performed, the axial length of each of the left and right eyes, the fundus tomographic image P3, and the corneal tomographic image P4 are stored in the axial length measurement information 320 in the storage unit 212. Specifically, the main control unit 211 correlates the above-mentioned eye test information (patient ID and left and right eye information) with the axial length of each left and right eye, the fundus tomographic image P3, and the corneal tomographic image P4. It is stored in the shaft length measurement information 320. As a result, the fundus tomographic image P3 and the corneal tomographic image P4 at the time of measuring the axial length of the eye E to be inspected can be confirmed later.

[Action of ophthalmic appliances]
FIG. 11 is a flowchart showing the flow of the measurement process of the axial length of the eye to be inspected E by the ophthalmic appliance 1000 having the above configuration (corresponding to the control method of the ophthalmic appliance of the present invention).

After the subject's face is supported by a face support portion (not shown), when the examiner inputs an operation to start measuring the axial length of the eye to be inspected E (one of the left and right eyes) to the operation unit 280, the main control is performed. Unit 211 functions as an image acquisition unit 300, an alignment control unit 302, a scanning control unit 304, a tomographic image generation control unit 306, a specific site detection unit 308, a display control unit 310, and a preview screen generation unit 312 (step S1). .. As a result, the image acquisition unit 300 repeatedly executes the acquisition of the observation image P1 from the front eye portion observation system 5 and the output of the observation image P1 to the display control unit 310.

Further, in response to the measurement start operation, the alignment control unit 302 executes acquisition of the stereo image P2 from the stereo camera 14, alignment detection, and auto-alignment of the measurement head 1002 by the moving mechanism 200 (step S2). .. The alignment control unit 302 repeatedly executes the acquisition of the stereo image P2 from the stereo camera 14 and the output of the stereo image P2 to the display control unit 310 even after the completion of the auto alignment.

When the auto-alignment is completed, the scanning control unit 304 controls each part of the OCT optical system 8 to perform known auto-optimization (fundus autofocus and optimization of OCT imaging position) (step S3), and then the measurement light. The first scanning control for scanning the fundus Ef (B scan) by LS is started (step S4, corresponding to the scanning control step of the present invention). As a result, the detection of the interference light LC by the detector 125 and the output of the detection signal and the sampling of the detection signal by the DAQ 130 are executed (step S5).

Then, the tomographic image generation control unit 306 controls the image forming unit 222 based on the sampling result of the detection signal input via the detector 125 and the DAQ 130 to generate the fundus tomographic image P3, and the fundus tomographic image P3. Is output to the display control unit 310 (step S6, corresponding to the first tomographic image generation step of the present invention). At this time, the specific site detection unit 308 detects the image of the fovea Fc from the tomographic image P3 of the fundus and outputs the fovea detection information which is the detection result to the display control unit 310.

Next, as shown in FIGS. 5 to 7 described above, the display control unit 310 displays the eye-tested information, the observation image P1, the stereo image P2, the fundus tomographic image P3, and the foveal detection information. Based on this, the first live display screen 400A is generated and displayed on the display unit 270 (step S7, corresponding to the display control step of the present invention). At this time, the display control unit 310 superimposes the index 410 indicating the position of the fovea Fovea on the fundus tomographic image P3 in the fundus tomographic image display area 408, and displays the index 410 in the fundus tomographic image display area 408. The guideline 412 and the second guideline 414 are displayed. Thereby, based on the first live display screen 400A (particularly, the fundus tomographic image display area 408), the fixative state (alignment state) of the eye E to be inspected during the first scanning control can be easily confirmed.

Hereinafter, until the first scanning control is completed, the processes of steps S5 to S7 described above are repeatedly executed (NO in step S8).

When the first scanning control is completed (YES in step S8), the scanning control unit 304 drives the corner cube moving mechanism 115 to move the corner cube 114 from the position corresponding to the OCT imaging of the fundus tomographic image P3 to the corneal tomographic image P4. The optical path length of the reference light LR is changed by moving to a position corresponding to OCT imaging (step S9).

After the movement of the corner cube 114 is completed, the scanning control unit 304 controls each unit of the OCT optical system 8 and starts the second scanning control of scanning the corneal Cr (B scan) with the measurement light LS (step S10, main). Corresponds to the scanning control step of the invention). As a result, the detection of the interference light LC by the detector 125 and the output of the detection signal and the sampling of the detection signal by the DAQ 130 are executed (step S11).

Then, the tomographic image generation control unit 306 controls the image forming unit 222 based on the sampling result of the detection signal input via the detector 125 and the DAQ 130 to generate the corneal tomographic image P4, and the corneal tomographic image P4. Is output to the display control unit 310 (step S12, corresponding to the second tomographic image generation step of the present invention).

Next, as shown in FIG. 8, the display control unit 310 displays the second live display screen 400B based on the eye-tested information, the observation image P1, the stereo image P2, and the corneal tomographic image P4. It is generated and displayed on the display unit 270 (step S13, corresponding to the display control step of the present invention). Thereby, based on the second live display screen 400B (particularly the observation image P1 and the corneal tomographic image P4), the fixative state (alignment state) of the eye E to be inspected during the second scanning control can be easily confirmed.

Hereinafter, until the second scanning control is completed, the processes of steps S11 to S13 described above are repeatedly executed (NO in step S14).

When the second scanning control is completed, the intraocular distance calculation unit 224 uses the detection signal (funeral tomographic image P3) for each B scan detected by the OCT optical system 8 in the first scanning control and the OCT optics in the second scanning control. The axial length of the eye to be inspected E is calculated based on the detection signal (corneal tomographic image P4) detected by the system 8 for each B scan and the above-mentioned optical coherence tomography difference (step S15). This completes the measurement of the axial length of one of the left and right eyes.

Next, the axial length of the other of the left and right eyes is also measured through the processes of steps S1 to S15 described above (NO in step S16).

When the measurement of the axial lengths of the left and right eyes is completed, the preview screen generation unit 312 displays the calculation result of the axial length of the eye to be inspected E (left and right eyes) and the fundus of the left and right eyes as shown in FIG. A preview screen 500 is generated based on the tomographic image P3 and the corneal tomographic image P4. Then, the preview screen generation unit 312 causes the display unit 270 to display the preview screen 500 via the display control unit 310 (step S17). As a result, even before the measurement result (calculation result) of the axial length of the left and right eyes is stored in the axial length measurement information 320, the fixation state of the eye E to be inspected during the first scanning control and the second scanning control can be obtained. It can be confirmed for each of the left and right eyes. As a result, it is possible to urge the examiner to remeasure the axial length of the eye to be inspected E (left and right eyes) as needed.

Then, when the operation unit 280 performs a memory operation of the measurement result of the axial length of the eye to be inspected E (left and right eyes), as shown in FIG. 10 described above, the main control unit 211 is used for each of the left and right eyes. The calculation result of the axial length, the corneal tomographic image P4, and the fundus tomographic image P3 are stored in the axial length measurement information 320 in the storage unit 212 (step S18).

As described above, in the present embodiment, when the first scanning control and the second scanning control are performed for the measurement of the axial length of the eye E to be inspected, the first scanning control includes the tomographic image P3 of the fundus. 1 The live display screen 400A can be displayed on the display unit 270, and the second live display screen 400B including the corneal tomographic image P4 can be displayed on the display unit 270 during the second scanning control. As a result, the fixative state (alignment state) of the eye to be inspected E can be easily confirmed during the measurement of the axial length of the eye to be inspected E (during the first scanning control and the second scanning control).

Further, in the present embodiment, when the measurement of the axial length of the eye to be inspected E (left and right eyes) is completed, the preview screen 500 including the axial length of each of the left and right eyes, the fundus tomographic image P3, and the corneal tomographic image P4 is displayed. By displaying on the display unit 270, the fixative state at the time of measuring the axial length of the eye E to be inspected can be easily confirmed. As a result, it is possible to determine whether to store the measurement result of the axial length for each of the left and right eyes in the storage unit 212 or to redo the measurement of the axial length.

[Modification example of preview screen 500]
FIG. 12 is an explanatory diagram for explaining a modification of the preview screen 500 generated by the preview screen generation unit 312. As shown in FIG. 9 described above, on the preview screen 500 of the above embodiment, the display intervals of the corneal tomographic image P4 and the fundus tomographic image P3 corresponding to the inspected eye E (left eye) and the inspected eye E (right eye). The display intervals of the corneal tomographic image P4 and the fundus tomographic image P3 corresponding to the above are equal intervals.

On the other hand, as shown in FIG. 12, when the preview screen generation unit 312 generates the preview screen 500, the corneal tomographic image P4 and the fundus tomographic image for each of the left and right eyes are obtained according to the axial length of each of the left and right eyes. The display interval with P3 may be changed. As a result, the display interval of the corneal tomographic image P4 and the fundus tomographic image P3 corresponding to the right eye increases or decreases according to the length of the axial length of the eye to be inspected E (right eye). In addition, the display interval of the corneal tomographic image P4 and the fundus tomographic image P3 corresponding to the left eye increases or decreases depending on the length of the axial length of the eye to be inspected E (left eye). As a result, the preview screen 500 can visually indicate the length of the axial length of each of the left and right eyes.

[others]
In the above embodiment, the first scanning control and the second scanning control are switched by moving the corner cube 114 to change the optical path length of the reference light LR, but the measurement light is measured by using various optical path length changing units. The first scan control and the second scan control may be switched by changing the optical path length of the LS or changing the optical path lengths of both the measurement light LS and the reference light LR.

In the above embodiment, the observation image P1 and the stereo image P2 are lively displayed in addition to the fundus tomographic image P3 on the first live display screen 400A, but at least the live display of the fundus tomographic image P3 is possible. The aspect is not particularly limited. Further, the display mode of the second live display screen 400B is not particularly limited as long as at least the live display of the corneal tomographic image P4 is possible.

In the above embodiment, the preview screen 500 is generated and displayed after the measurement of the axial length of the eye to be inspected E (left and right eyes) is completed, but after the measurement of the axial length of the left eye is completed and the axial length of the right eye is completed. The preview screen 500 may be generated and displayed when the measurement is completed. In this case, the preview screen generation unit 312 generates and controls the display of the left eye display area 500L described above as the preview screen 500 corresponding to the left eye, and describes the preview screen 500 corresponding to the right eye, for example. The display area 500R for the right eye is generated and the display is controlled (see FIGS. 9 and 12). Further, the display interval between the fundus tomographic image P3 and the corneal tomographic image P4 may be changed according to the axial length (intraocular distance) (see FIG. 12).

In the above embodiment, the axial length is measured as the intraocular distance of the subject E, but the tomographic image of the anterior segment of the anterior region of the subject E and the posterior eye of the arbitrary region of the posterior eye. The present invention can also be applied in the case of acquiring a partial tomographic image and measuring the intraocular distance between an arbitrary region of the anterior segment of the eye and an arbitrary region of the posterior segment of the eye. In this case, the specific site detection unit 308 detects an image of a specific site other than the foveal Fc from the posterior ocular tomographic image, and the display control unit 310 is in the posterior eye tomographic image based on this detection result. The image of a specific part of the image may be displayed in an identifiable manner.

In the above embodiment, the ophthalmic apparatus 1000 that performs reflex measurement and OCT measurement has been described as an example, but at least the ophthalmic apparatus capable of OCT measurement and the intraocular distance (axis length, etc.) of the eye E to be inspected. The type of ophthalmic apparatus used for measurement is not particularly limited.

1 Alignment system 3 Kerato measurement system 4 Fixed-lens projection system 5 Anterior lens observation system 6 Ref measurement projection system 7 Ref measurement Light-receiving system 8 OCT optical system 9 Processing unit 14 Stereo camera 31 Kerato plate 32 Keratling light source 40 Fixed vision unit 40D Moving mechanism 41 Liquid crystal panel 42 Relay lens 50 Front eye illumination light source 51 Objective lens 52 Dycroic filter 53 Aperture 55 Relay lens 56 Relay lens 58 Imaging lens 59 Imaging element 61 Ref measurement light source 61D Moving mechanism 62 Relay lens 63 Conical prism 64 Ring Aperture 65 Perforated prism 66 Rotary prism 67 Dycroic filter 71 Relay lens 72 Reflective mirror 73 Relay lens 74 Focusing lens 74D Movement mechanism 75 Reflection mirror 76 Dycroic filter 80D Movement mechanism 81 Reflection mirror 82 Relay lens 83 Dycroic filter 84 Reflection mirror 85 Relay Lens 87 Focusing lens 88 Optical scanner 89 Collimeter Lens unit 100 OCT unit 101 OCT light source 102 Optical fiber 103 Polarization controller 104 Optical fiber 105 Fiber coupler 110 Optical fiber 111 Collimeter 112 Optical path length correction member 113 Dispersion compensation member 114 Corner cube 115 Corner cube movement mechanism 116 Collimeter 117 Optical fiber 118 Polarization controller 119 Optical fiber 120 Attenuator 121 Optical fiber 122 Fiber coupler 123 Optical fiber 124 Optical fiber 125 Detector 128 Optical fiber 200 Moving mechanism 210 Control unit 211 Main control unit 212 Storage unit 220 Calculation unit 221A Eye refractive force calculation unit 221B Lens shape calculation unit 222 Image formation unit 223 Data processing unit 224 Intraocular distance calculation unit 270 Display unit 280 Operation unit 290 Communication unit 300 Image acquisition unit 302 Alignment control unit 304 Scan control unit 306 Tomographic image generation control unit 308 Specific site detection unit 310 Display control unit 312 Preview screen generation unit 320 Axial length measurement information 400A 1st live display screen 400B 2nd live display screen 402 Left and right eye information area 404 Observation image display area 406 Stereo image display area 408 Fundus tomographic image display area 410 Index 412 1st guideline 414 2nd guideline 420 Cornenal tomographic image display area 500 Preview -Screen 500L Left eye display area 500R Right eye display area 502L Left and right eye information area 502L Left and right eye information area 504L Axial length display area 504R Axial length display area 1000 Ophthalmology device 1002 Measuring head Cr Corneal E F Eye fundus Fc Central fossa KC clock L0 optical LC interference light LP1 observation system optical path LP2 branched optical path LP3 branched optical path LR reference optical LS measurement light LS1 OCT system return light P1 observation image P2 stereo image P3 fundus tomographic image P4 corneal tomographic image f1 optical fiber

Claims (11)

Interference optical system that divides the light from the light source into the measurement light and the reference light, irradiates the test eye with the measurement light, and detects the return light of the measurement light from the test eye and the interference light with the reference light. An interference optical system comprising an optical scanning unit that scans the measurement light and an optical path length changing unit that changes the optical path length of at least one of the measurement light and the reference light.
A first scanning control in which the optical scanning unit and the optical path length changing unit are controlled to scan the rear eye portion of the eye to be inspected with the measurement light, and the anterior eye portion of the eye to be inspected is scanned by the measurement light. 2 Scanning control, a scanning control unit that executes
A first tomographic image generation unit that generates a first tomographic image of the rear eye portion based on the detection signal of the interference light detected by the interference optical system under the first scanning control.
A second tomographic image generation unit that generates a second tomographic image of the anterior eye portion based on the detection signal detected by the interference optical system under the second scanning control.
The first tomographic image generated by the first tomographic image generation unit is displayed on the display unit during the first scanning control, and the second tomographic image generation unit is generated by the second tomographic image generation unit during the second scanning control. A display control unit that displays a tomographic image on the display unit,
An ophthalmic device equipped with. According to claim 1, the display control unit causes the display unit to display a guideline indicating a position where an image of a specific portion of the rear eye portion should be displayed on the screen of the display unit during the first scanning control. The ophthalmic device described. The ophthalmic apparatus according to claim 2, wherein the display control unit causes the display unit to display the guideline indicating a position where an image of the fovea centralis of the posterior eye portion should be displayed as the specific site. A specific site detection unit for detecting an image of the specific site from the first tomographic image is provided.
2. The ophthalmic device described in. The detection signal detected by the interference optical system in the first scanning control, the detection signal detected by the interference optical system in the second scanning control, and the first scanning control and the second scanning control. The ophthalmologic apparatus according to any one of claims 1 to 4, further comprising an intraocular distance calculation unit for calculating the intraocular distance between the anterior eye portion and the posterior eye portion based on the difference in optical path length. .. The intraocular distance calculated by the intraocular distance calculation unit, the first tomographic image generated by the first tomographic image generation unit, and the second tomographic image generated by the second tomographic image generation unit. The ophthalmic apparatus according to claim 5, further comprising a simultaneous display control unit for simultaneously displaying on the display unit. The ophthalmic apparatus according to claim 6, wherein the simultaneous display control unit changes the display interval between the first tomographic image and the second tomographic image according to the magnitude of the intraocular distance. When the eye to be inspected is the left and right eyes, the first scan control and the second scan control by the scan control unit and the generation of the first tomographic image by the first tomographic image generation unit for each of the left and right eyes. The second tomographic image generation unit generates the second tomographic image, the display control unit displays the first tomographic image and the second tomographic image on the display unit, and the intraocular distance calculation unit. And the calculation of the intraocular distance by
The ophthalmic apparatus according to claim 6 or 7, wherein the simultaneous display control unit simultaneously displays the intraocular distance for each of the left and right eyes, the first tomographic image, and the second tomographic image on the display unit. The simultaneous display control unit displays the intraocular distance, the first tomographic image, and the second tomographic image side by side on the display unit for each of the left and right eyes, and the large intraocular distance for each of the left and right eyes. The ophthalmic apparatus according to claim 8, wherein the display interval between the first tomographic image and the second tomographic image is changed accordingly. When the posterior eye portion is the fundus of the eye to be inspected and the anterior eye portion is the cornea of the eye to be inspected, the intraocular distance calculation unit calculates the axial length of the eye to be inspected as the intraocular distance. The ophthalmic apparatus according to any one of claims 5 to 9. Interference optical system that divides the light from the light source into the measurement light and the reference light, irradiates the test eye with the measurement light, and detects the return light of the measurement light from the test eye and the interference light with the reference light. A method for controlling an ophthalmic apparatus including an interference optical system including an optical scanning unit that scans the measurement light and an optical path length changing unit that changes the optical path length of at least one of the measurement light and the reference light. In
A first scanning control in which the optical scanning unit and the optical path length changing unit are controlled to scan the rear eye portion of the eye to be inspected with the measurement light, and the anterior eye portion of the eye to be inspected is scanned by the measurement light. 2 Scan control, a scan control step to execute, and
A first tomographic image generation step of generating a first tomographic image of the posterior eye portion based on the detection signal of the interference light detected by the interference optical system under the first scanning control.
A second tomographic image generation step of generating a second tomographic image of the anterior eye portion based on the detection signal detected by the interferometric optical system under the second scanning control, and a second tomographic image generation step.
The first tomographic image generated in the first tomographic image generation step is displayed on the display unit during the first scanning control, and the second tomographic image generated in the second tomographic image generation step during the second scanning control is displayed. A display control step for displaying a tomographic image on the display unit,
A method of controlling an ophthalmic appliance having.

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