WO2023053648A1

WO2023053648A1 - Ophthalmic device, method for controlling ophthalmic device, and program

Info

Publication number: WO2023053648A1
Application number: PCT/JP2022/026271
Authority: WO
Inventors: 祥聖森口; 朗子石川
Original assignee: 株式会社トプコン
Priority date: 2021-09-28
Filing date: 2022-06-30
Publication date: 2023-04-06
Also published as: JP2023048746A

Abstract

This ophthalmic device comprises an optical system, an angle change mechanism, a visual fixation system, a control unit, and an analysis unit. The optical system comprises: an objective lens; an imaging optical system that receives light from a subject's eye via the objective lens; and an OCT optical system that is coupled to a light path of the imaging optical system. The angle change mechanism changes the orientation of the optical axis of the optical system by tilting the optical system. The visual fixation system projects a visual fixation light flux toward the subject's eye from an emission position of the visual fixation light flux, the relative position of which can be changed with respect to the optical axis. The control unit changes the angle formed between the visual axis of the subject's eye and the optical axis on the basis of an OCT measurement position in an image of the subject's eye so as to cause the visual fixation light flux to be projected from an emission position corresponding to the OCT measurement position, and causes OCT measurement to be executed on the subject's eye while the visual fixation light flux is kept projected onto said eye. An image formation unit forms an OCT image of the subject's eye. The analysis unit identifies the position of the OCT image in the image of the subject's eye on the basis of the emission position.

Description

OPHTHALMOLOGICAL APPARATUS, OPHTHALMOLOGICAL APPARATUS CONTROL METHOD, AND PROGRAM

The present invention relates to an ophthalmologic apparatus, an ophthalmologic apparatus control method, and a program.

Ophthalmic equipment for screening and treatment of eye diseases is required to be able to easily observe and photograph the fundus of the eye to be examined in a wide field of view. Optical coherence tomography and scanning laser ophthalmoscopes (hereinafter referred to as SLOs) are known as such ophthalmologic apparatuses. The SLO is a device that scans the fundus with light and forms an image of the fundus by detecting the returned light with a light receiving device.

Various ophthalmologic devices have been proposed for observing the fundus in such a wide field of view.

For example, in Patent Document 1, in an ophthalmologic apparatus in which a fixation target is provided around an objective lens, a fixation target movement method is disclosed in which the fixation target is moved to the outer peripheral surface of the objective lens so as to change the distance from the objective lens. A fundus camera with mechanism is disclosed.

JP-A-2003-079579

In recent years, the area of interest in the fundus also extends to the peripheral area outside the central area of the fundus, including the optic disc and macula. Therefore, there is a demand for a method of capturing or measuring the peripheral region of the fundus more simply.

A more convenient wide-angle imaging or measurement method for the subject's eye is desired not only for the fundus but also for the anterior segment of the eye.

The present invention has been made in view of such circumstances, and one of its purposes is to provide a new technique for taking or measuring an eye to be examined more simply and at a wide angle.

A first aspect according to an embodiment includes an objective lens, an imaging optical system that receives light from an eye to be inspected via the objective lens, and an optical path coupled to the imaging optical system to transmit measurement light that has passed through the optical path. an OCT optical system for projecting onto the eye to be inspected via the objective lens and detecting interference light between the return light of the measurement light and the reference light; and the optical system by tilting the optical system. a fixation system for projecting a fixation light flux toward the eye to be examined from an emission position of the fixation light flux whose position relative to the optical axis is changeable; and the eye to be examined changing the angle formed by the visual axis of the eye to be examined and the optical axis based on the OCT measurement position in the image, and projecting the fixation light beam from the emission position corresponding to the OCT measurement position; A control unit that performs OCT measurement for the eye to be inspected by controlling the OCT optical system in a state where is projected, and an image forming unit that forms an OCT image of the eye to be inspected based on the detection result of the interference light. and an analysis unit that identifies the position of the OCT image in the image of the subject's eye based on the emission position.

In a second aspect according to the embodiment, in the first aspect, the control unit causes the fixation system to project the fixation light flux on each of the two or more OCT measurement positions, and the analysis unit causes the two or more OCT measurement positions to be projected. For each OCT measurement position, the position of the OCT image in the image of the subject's eye is specified based on the exit position in the fixation system.

In a third aspect according to the embodiment, in the first aspect or the second aspect, the fixation system is configured to extend from the outside of the objective lens to the eye to be examined from the emission position having a known positional relationship with respect to the optical axis. an external fixation system for projecting said fixation beam towards.

In a fourth aspect according to the embodiment, in the first aspect, the fixation system includes an internal fixation light source capable of changing a relative position with respect to the optical axis, and directs the fixation to the subject's eye via the objective lens. An internal fixation system for projecting a light beam, and an external fixation light source capable of changing a relative position with respect to the optical axis, wherein the external fixation has a known positional relationship with the optical axis from outside the objective lens. an external fixation system that projects the fixation light beam from the position of the light source toward the eye to be examined.

In a fifth aspect according to the embodiment, in the fourth aspect, when the OCT measurement position is within a predetermined range including the position corresponding to the optical axis in the image of the subject's eye, the control unit causes the internal fixation system to project the fixation light beam onto the eye to be examined, and the analysis unit identifies the position of the OCT image in the image of the eye to be examined based on the fixation position where the fixation light beam is projected, and When the OCT measurement position is outside the predetermined range including the position corresponding to the optical axis in the image of the eye to be examined, the control unit causes the external fixation system to project the fixation light flux onto the eye to be examined, The analysis unit specifies the position of the OCT image in the image of the subject's eye based on the fixation position onto which the fixation light flux is projected.

In a sixth aspect according to the embodiment, in the fourth aspect or the fifth aspect, the control unit projects the fixation light flux using the internal fixation system or the external fixation system for each of two or more OCT measurement positions. and the analyzing unit identifies the position of the OCT image in the image of the subject's eye based on the fixation position onto which the fixation light flux is projected, for each of the two or more OCT measurement positions.

In a seventh aspect according to the embodiment, in any one of the third to sixth aspects, the external fixation system is fixed with respect to the optical system.

In an eighth aspect according to the embodiment, in any one of the first aspect to the seventh aspect, the angle changing mechanism is a first angle changing mechanism that vertically changes the angle formed by the orientation of the optical axis with respect to the horizontal direction. and a second angle changing mechanism for changing the angle formed by the orientation of the optical axis with respect to the vertical direction in the horizontal direction.

A ninth aspect according to the embodiment is any one of the first to eighth aspects, including an operation unit, and the OCT measurement position is set based on the operation content of the image of the subject's eye using the operation unit. be done.

A tenth aspect according to the embodiment is an objective lens, an imaging optical system for receiving light from an eye to be inspected via the objective lens, and an optical path coupled to the imaging optical system for receiving measurement light passing through the optical path. an OCT optical system for projecting onto the eye to be inspected via the objective lens and detecting interference light between the return light of the measurement light and the reference light; and the optical system by tilting the optical system. and a fixation system for projecting a fixation light flux toward the subject's eye from a fixation light flux emission position whose position relative to the optical axis can be changed. A method for controlling an apparatus, wherein the angle formed by the visual axis of the eye to be inspected and the optical axis is changed based on the OCT measurement position in the image of the eye to be inspected, and the a control step of projecting a fixation light beam and controlling the OCT optical system while the fixation light beam is being projected to perform OCT measurement on the eye to be examined; A control method for an ophthalmologic apparatus, comprising: an image forming step of forming an OCT image of an eye to be inspected; and an analysis step of specifying a position of the OCT image in the image of the eye to be inspected based on the emission position.

In an eleventh aspect according to the embodiment, in the tenth aspect, the controlling step causes the fixation system to project the fixation light flux on each of the two or more OCT measurement positions, and the analyzing step includes: For each OCT measurement position, the position of the OCT image in the image of the subject's eye is specified based on the exit position in the fixation system.

In a twelfth aspect according to the embodiment, in the tenth aspect or the eleventh aspect, the fixation system extends from the outside of the objective lens to the eye to be examined from the emission position having a known positional relationship with respect to the optical axis. an external fixation system for projecting said fixation beam towards.

In a thirteenth aspect according to the embodiment, in the tenth aspect, the fixation system includes an internal fixation light source whose position relative to the optical axis can be changed, and directs the fixation to the eye to be inspected via the objective lens. An internal fixation system for projecting a light beam, and an external fixation light source capable of changing a relative position with respect to the optical axis, wherein the external fixation has a known positional relationship with the optical axis from outside the objective lens. an external fixation system that projects the fixation light beam from the position of the light source toward the eye to be examined.

In a fourteenth aspect according to the embodiment, in the thirteenth aspect, when the OCT measurement position is within a predetermined range including the position corresponding to the optical axis in the image of the subject's eye, the control step includes: to project the fixation light beam onto the eye to be examined, and the analyzing step identifies the position of the OCT image in the image of the eye to be examined based on the fixation position to which the fixation light beam is projected, and When the OCT measurement position is outside a predetermined range including the position corresponding to the optical axis in the image of the eye to be examined, the control step causes the external fixation system to project the fixation light beam onto the eye to be examined, The analyzing step identifies the position of the OCT image in the image of the subject's eye based on the fixation position onto which the fixation light flux is projected.

In a fifteenth aspect according to the embodiment, in the thirteenth aspect or the fourteenth aspect, the control step includes projecting the fixation light beam from the internal fixation system or the external fixation system on each of two or more OCT measurement positions. and the analyzing step identifies the position of the OCT image in the image of the subject's eye based on the fixation position onto which the fixation light beam is projected, for each of the two or more OCT measurement positions.

In a sixteenth aspect according to the embodiment, in any one of the twelfth to fifteenth aspects, the external fixation system is fixed with respect to the optical system.

In a seventeenth aspect according to the embodiment, in any one of the tenth to sixteenth aspects, the angle changing mechanism includes a first angle changing mechanism that vertically changes the angle formed by the orientation of the optical axis with respect to the horizontal direction. and a second angle changing mechanism for changing the angle formed by the orientation of the optical axis with respect to the vertical direction in the horizontal direction.

In the 18th aspect according to the embodiment, in any one of the 10th to 17th aspects, the OCT measurement position is set based on the operation content for the image of the subject's eye using the operation unit.

A nineteenth aspect according to the embodiment is a program that causes a computer to execute each step of the ophthalmologic apparatus control method according to any one of the tenth to eighteenth aspects.

It should be noted that it is possible to arbitrarily combine the configurations according to the plurality of aspects described above.

According to the present invention, it is possible to provide a new technique for more simply taking a wide-angle image or measuring the subject's eye.

It is a schematic diagram showing an example of the configuration of the optical system of the ophthalmologic apparatus according to the embodiment. 1 is a schematic diagram showing an example of the configuration of an external fixation unit according to an embodiment; FIG. FIG. 4 is a schematic diagram for explaining a fixation light flux according to the embodiment; FIG. 4 is a schematic diagram for explaining a fixation light flux according to the embodiment; It is a schematic diagram showing an example of the configuration of the optical system of the ophthalmologic apparatus according to the embodiment. 1 is a schematic diagram showing an example of the configuration of a control system of an ophthalmologic apparatus according to an embodiment; FIG. FIG. 4 is a schematic diagram for explaining swing motion and tilt motion of the ophthalmologic apparatus according to the embodiment; FIG. 4 is a schematic diagram for explaining fixation control according to the embodiment; 4 is a schematic diagram for explaining control of the ophthalmologic apparatus according to the embodiment; FIG. 4 is a schematic diagram for explaining control of the ophthalmologic apparatus according to the embodiment; FIG. It is a schematic diagram for explaining the operation of the ophthalmologic apparatus according to the embodiment. 1 is a schematic diagram showing an example of the configuration of a data processing unit of an ophthalmologic apparatus according to an embodiment; FIG. 1 is a schematic diagram showing an example of the configuration of a data processing unit of an ophthalmologic apparatus according to an embodiment; FIG. 4 is a flow chart showing an example of the operation of the ophthalmologic apparatus according to the embodiment; 4 is a flow chart showing an example of the operation of the ophthalmologic apparatus according to the embodiment; 4 is a flow chart showing an example of the operation of the ophthalmologic apparatus according to the embodiment; 4 is a flow chart showing an example of the operation of the ophthalmologic apparatus according to the embodiment;

An example of an embodiment of an ophthalmologic apparatus, a control method of the ophthalmologic apparatus, and a program according to the present invention will be described in detail with reference to the drawings. In addition, in the embodiments, it is possible to arbitrarily incorporate the techniques described in the documents cited in this specification.

An ophthalmologic apparatus according to an embodiment includes an optical system capable of imaging an eye to be inspected and OCT measurement, an angle changing mechanism for changing the direction of the optical axis of the optical system by tilting the optical system, and an optical system with respect to the optical axis. a fixation system for projecting a fixation light beam toward the subject's eye from a fixation light beam emission position (projection position, position of the fixation light source) whose relative position is changeable.

In some embodiments, the angle changing mechanism includes at least one of a swing mechanism and a tilt mechanism. The swing mechanism is, for example, a movement mechanism that swings the optical system in an arc shape in the horizontal direction around the pupil of the eye to be examined. As a result, the angle formed by the direction of the optical axis of the optical system with respect to the vertical direction (vertical plane) can be changed in the horizontal direction. The tilt mechanism is, for example, a movement mechanism that turns the optical system in an arc shape in the vertical direction around the pupil of the subject's eye. Thereby, the angle formed by the direction of the optical axis of the optical system with respect to the horizontal direction (horizontal plane) can be changed in the vertical direction.

In some embodiments, the optical system includes a fixation system. The fixation system includes at least one of an internal fixation system and an external fixation system. The internal fixation system presents a fixation target by projecting a fixation light beam onto the subject's eye via an objective lens. The external fixation system presents a fixation target by projecting a fixation light beam onto the subject's eye without passing through an objective lens.

The ophthalmologic apparatus controls at least one of the angle changing mechanism and the fixation system based on the OCT measurement position set in the captured image (or observed image) of the subject's eye, and determines the emission position of the fixation light flux corresponding to the OCT measurement position. A fixation light beam is projected from the eye, and OCT measurement is performed on the subject's eye while the fixation light beam is being projected. The ophthalmologic apparatus identifies the position of the OCT image in the captured image based on the emission position of the fixation light flux. In some embodiments, the ophthalmologic apparatus performs registration processing between the captured image and the OCT image, and causes the display means to display the captured image and the OCT image after the registration processing.

This makes it possible to easily acquire a wide-angle OCT image of the subject's eye. In particular, since the search range for registration processing is determined from the emission position of the fixation light flux, the processing load can be significantly reduced.

In some embodiments, an ophthalmologic apparatus causes a fixation system to project a fixation light flux on each of two or more OCT measurement positions, and identifies the position of the OCT image in the captured image based on the emission position of the fixation light flux. .

In some embodiments, the ophthalmologic apparatus determines two or more OCT measurement positions based on the montage imaging range set in the captured image (or observation image) of the subject's eye, and determines the determined two or more OCT measurement positions. The fixation system sequentially projects the fixation light beams for each of the above, and sequentially specifies the positions of the OCT images in the captured image based on the emission positions of the fixation light beams. In some embodiments, the ophthalmologic apparatus performs overlap determination processing between an OCT image whose position is specified and an adjacent OCT image, and obtains the next OCT image based on the determination result. Get a montage image. In some embodiments, the ophthalmologic apparatus performs registration processing between the captured image and the OCT montage image, and causes the display means to display the captured image and the OCT montage image after the registration processing.

A control method for an ophthalmic device according to an embodiment includes one or more steps for controlling the above-described ophthalmic device. A program according to an embodiment causes a computer (processor) to execute each step of a method for controlling an ophthalmologic apparatus according to an embodiment. A recording medium according to the embodiment is a non-temporary recording medium (storage medium) in which the program according to the embodiment is recorded.

In this specification, a processor is, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an ASIC (Application Specific Integrated Circuit), a programmable logic device (for example, a SPLD (Simple Programmable Logic Device CPLD Logic Device), FPGA (Field Programmable Gate Array)), etc. The processor implements the functions according to the embodiment by, for example, reading and executing a program stored in a memory circuit or memory device. A memory circuit or device may be included in the processor. Also, a memory circuit or memory device may be provided external to the processor.

A case where the ophthalmologic apparatus according to the embodiment has a swing mechanism and a tilt mechanism will be described below, but the configuration according to the embodiment is not limited to this. For example, the ophthalmic device may have only one of the swing mechanism and the tilt mechanism.

In the following embodiments, the ophthalmic device includes an optical coherence tomography and a fundus camera. Although swept source OCT is applied to this optical coherence tomography, the type of OCT is not limited to this, and other types of OCT (spectral domain OCT, time domain OCT, Amphas OCT, etc.) may be applied. good.

Also, the ophthalmologic apparatus according to the embodiment may include any one of a scanning laser ophthalmoscope, a slit lamp ophthalmoscope, a surgical microscope, and the like. Also, the ophthalmic device according to the embodiment may include any one or more of an eye refraction tester, a tonometer, a specular microscope, a wavefront analyzer, a perimeter, a microperimeter, and the like.

Hereinafter, the x direction is the direction perpendicular to the optical axis direction of the objective lens (horizontal direction, horizontal direction), and the y direction is the direction perpendicular to the optical axis direction of the objective lens (vertical direction, vertical direction). and The z-direction is assumed to be the optical axis direction of the objective lens.

<Configuration>
〔Optical system〕
As shown in FIG. 1, the ophthalmologic apparatus 1 includes a fundus camera unit 2, an OCT unit 100, and an arithmetic control unit (not shown). The retinal camera unit 2 is provided with an optical system and a mechanism for acquiring a front image of the eye E to be examined. The OCT unit 100 is provided with a part of an optical system and a mechanism for performing OCT. Another part of the optical system and mechanism for performing OCT is provided in the fundus camera unit 2 . The calculation control unit includes one or more processors that perform various calculations and controls. In addition to these, arbitrary elements such as a member for supporting the subject's face (chin rest, forehead rest, etc.) and a lens unit for switching the target part of OCT (for example, attachment for anterior segment OCT) or unit may be provided in the ophthalmologic apparatus 1 . Furthermore, the ophthalmologic apparatus 1 includes a pair of

anterior eye cameras

5A and 5B.

[Fundus camera unit 2]
The fundus camera unit 2 is provided with an optical system for photographing the fundus Ef of the eye E to be examined. The acquired image of the fundus oculi Ef (referred to as a fundus image, fundus photograph, etc.) is a front image such as an observed image or a photographed image. Observation images are obtained by moving image shooting using near-infrared light. A photographed image is a still image using flash light. Furthermore, the fundus camera unit 2 can photograph the anterior segment Ea of the subject's eye E to acquire a front image (anterior segment image).

The retinal camera unit 2 includes an illumination optical system 10 and an imaging optical system 30. The illumination optical system 10 irradiates the eye E to be inspected with illumination light. The imaging optical system 30 detects return light of the illumination light from the eye E to be examined. The measurement light from the OCT unit 100 is guided to the subject's eye E through the optical path in the retinal camera unit 2, and its return light is guided to the OCT unit 100 through the same optical path.

Light (observation illumination light) output from an observation light source 11 of an illumination optical system 10 is reflected by a reflecting mirror 12 having a curved reflecting surface, passes through a condenser lens 13, and passes through a visible light cut filter 14. It becomes near-infrared light. Furthermore, the observation illumination light is once converged near the photographing light source 15 , reflected by the mirror 16 , and passed through the

relay lenses

17 and 18 , the diaphragm 19 and the relay lens 20 . Then, the observation illumination light is reflected by the periphery of the perforated mirror 21 (area around the perforation), passes through the dichroic mirror 46, is refracted by the objective lens 22, Illuminate part Ea). The return light of the observation illumination light from the subject's eye E is refracted by the objective lens 22, passes through the dichroic mirror 46, passes through the hole formed in the central region of the aperture mirror 21, and passes through the photographing focusing lens 31. through and reflected by mirror 32 . Further, this return light passes through the half mirror 33A, is reflected by the dichroic mirror 33, and is imaged on the light receiving surface of the image sensor 35 by the condenser lens . The image sensor 35 detects returned light at a predetermined frame rate. The focus of the imaging optical system 30 is adjusted so as to match the fundus oculi Ef or the anterior segment Ea.

The light (imaging illumination light) output from the imaging light source 15 irradiates the fundus oculi Ef through the same path as the observation illumination light. The return light of the imaging illumination light from the subject's eye E is guided to the dichroic mirror 33 through the same path as the return light of the observation illumination light, passes through the dichroic mirror 33 , is reflected by the mirror 36 , is reflected by the condenser lens 37 . An image is formed on the light receiving surface of the image sensor 38 .

For example, the display unit provided in the ophthalmologic apparatus 1 displays an image (observation image) based on the fundus reflected light detected by the image sensor 35 . Note that when the imaging optical system 30 is focused on the anterior segment, an observation image of the anterior segment of the subject's eye E is displayed. Also, an image (captured image) based on the fundus reflected light detected by the image sensor 38 is displayed on the display unit. Note that the display unit that displays the observed image and the display unit that displays the captured image may be the same or different. When the subject's eye E is illuminated with infrared light and photographed in the same manner, an infrared photographed image is displayed.

The ophthalmic device 1 includes a fixation system. The fixation system includes an internal fixation system and an external fixation system. The function of the internal fixation system is realized by an LCD (Liquid Crystal Display) 39 . The function of the external fixation system is realized by the external fixation unit 23 .

An LCD (Liquid Crystal Display) 39 displays a fixation target and a visual acuity measurement target. A part of the light flux output from the LCD 39 is reflected by the half mirror 33 A, reflected by the mirror 32 , passes through the photographing focusing lens 31 , and passes through the aperture of the apertured mirror 21 . The luminous flux that has passed through the aperture of the perforated mirror 21 is transmitted through the dichroic mirror 46, refracted by the objective lens 22, and projected onto the fundus oculi Ef.

The display pixels on the screen of the LCD 39 function as an internal fixation light source. By changing the display position of the fixation target on the screen of the LCD 39, the fixation position of the subject's eye E can be changed. Examples of fixation positions include the fixation position for acquiring an image centered on the macula, the fixation position for acquiring an image centered on the optic disc, and the center of the fundus between the macula and the optic disc. and a fixation position for acquiring an image of a site far away from the macula (eye fundus periphery). The ophthalmologic apparatus 1 according to some embodiments includes a GUI (Graphical User Interface) or the like for designating at least one of such fixation positions. The ophthalmologic apparatus 1 according to some embodiments includes a GUI or the like for manually moving the fixation position (the display position of the fixation target).

The configuration for presenting a movable fixation target to the eye to be examined E is not limited to a display device such as an LCD. For example, a movable fixation target can be generated by selectively lighting multiple light sources in a light source array (such as a light emitting diode (LED) array). Also, one or more movable light sources can generate a movable fixation target.

The external fixation unit 23 projects a fixation light flux onto the subject's eye E without passing through the objective lens 22 from an emission position whose position relative to the optical axis of the objective lens 22 (objective optical axis) can be changed. The external fixation unit 23, which can change the emission position of the fixation light flux with respect to the optical axis of the objective lens 22, is configured to be movable integrally with the fundus camera unit 2 (optical system including the LCD 39). For example, the external fixation unit 23 is fixed to a housing that houses the optical system that constitutes the retinal camera unit 2 .

A configuration example of the external fixation unit 23 is schematically shown in FIG. In FIG. 2, the same parts as those in FIG. 1 are denoted by the same reference numerals, and description thereof will be omitted as appropriate.

The external fixation unit 23 includes an annular member 23A that can be installed on or near the outer circumference of the objective lens 22, and one end connected to the outer circumference of the annular member 23A and the other end connected to the optical axis O (optical axis of the objective lens 22, and a fixation light source holding member 23B extending substantially radially from the objective optical axis. The fixation light source holding member 23B includes a plurality of fixation light sources (external fixation light sources) arranged in the radial direction. The plurality of fixation light sources are controlled by a control unit, which will be described later, so that one of them is turned on or all of them are turned off. In this embodiment, the plurality of fixation light sources are assumed to be fixation light sources 23-1 to 23-4.

The fixation light source holding member 23B is configured to be rotatable around the optical axis O. In some embodiments, the fixation light source holding member 23B is configured to rotate relative to the annular member 23A. In some embodiments, the annular member 23A and the fixation light source holding member 23B are configured to rotate integrally.

In some embodiments, the fixation light source holding member 23B automatically rotates around the optical axis O under the control of a control unit, which will be described later. For example, the control section can drive the rotation mechanism included in the external fixation unit 23 by controlling the fixation light source holding member 23B.

In some embodiments, the fixation light source holding member 23B is configured to be manually rotated around the optical axis O. For example, the external fixation unit 23 includes a sensor and is configured to be able to detect the angle in the radial direction of the manually rotated fixation light source holding member 23B. As in the case of automatically rotating the fixation light source holding member 23B, the external fixation unit 23 projects the fixation light flux onto the subject's eye E from a desired emission position while referring to the detection result obtained by the sensor. can be configured to allow

By rotating the fixation light source holding member 23B around the optical axis O and lighting any one of the fixation light sources 23-1 to 23-4, a variety of images with a wider range than the LCD 39, which is internal fixation, can be displayed. It becomes possible to project a fixation light beam onto the subject's eye E from any direction.

In some embodiments, the fixation light source holding member 23B includes two or more arm members coupled together. Each of the fixation light sources 23-1 to 23-4 is provided on one of two or more arm members. The arm members are rotatable at the coupling point. With such a folding mechanism, the fixation light source holding member 23B is configured to be storable.

In some embodiments, the fixation light source holding member 23B includes two or more arm members that are mutually slidable in the radial direction. Each of the fixation light sources 23-1 to 23-4 is provided on one of two or more arm members. With such a slide mechanism, the fixation light source holding member 23B is configured to be retractable.

In some embodiments, the external fixation unit 23 is configured to be detachable from the retinal camera unit 2.

3 schematically shows an example of the arrangement of the fixation light sources 23-1 to 23-4 of the external fixation unit 23. FIG. In FIG. 3, the same parts as those in FIGS. 1 and 2 are denoted by the same reference numerals, and description thereof will be omitted as appropriate.

A fixation light flux from an arbitrary display pixel of the LCD 39 is projected onto the subject's eye E via the objective lens 22 as a fixation target IFp. On the other hand, a fixation light beam from any one of the fixation light sources 23-1 to 23-4 is projected onto the subject's eye E without passing through the objective lens 22. FIG. At this time, the fixation light sources 23-1 to 23-4 are arranged at a distance R0 centering on the subject's eye E (for example, the pupil). Among the fixation light sources 23-1 to 23-4, the fixation light source (the fixation light source 23-4 in FIG. 3) having the shortest distance in the z direction from the eye E to be examined has a distance of Dw arranged to be larger. The distance Dw may be the working distance between the subject's eye E and the lens surface of the objective lens 22 .

Thereby, the adjustment states of the subject's eye E with respect to each of the fixation light sources 23-1 to 23-4 can be made uniform. As a result, it is possible to reduce the influence caused by the difference in the accommodation state of the subject's eye E depending on the fixation position of the external fixation.

4 schematically shows another example of the arrangement of the fixation light sources 23-1 to 23-4 of the external fixation unit 23. FIG. In FIG. 4, the same parts as those in FIGS. 1 and 2 are denoted by the same reference numerals, and description thereof will be omitted as appropriate.

A fixation luminous flux from an arbitrary display pixel on the screen of the LCD 39 is projected as a fixation target IFp onto the subject's eye E via the objective lens 22, as in FIG. On the other hand, a fixation light beam from any one of the fixation light sources 23-1 to 23-4 is projected onto the subject's eye E without passing through the objective lens 22. FIG. At this time, the fixation light sources 23 - 1 to 23 - 4 are provided in a direction perpendicular to the optical axis of the objective lens 22 . The fixation light sources 23-1 to 23-4 are arranged so that the distance from the subject's eye E is greater than Dw. The distance Dw may be the working distance between the subject's eye E and the lens surface of the objective lens 22 .

Thereby, although the distances of the fixation light sources 23-1 to 23-4 with respect to the eye E to be examined are different, the fixation target can be presented to the eye E to be examined easily.

As described above, each of the fixation light sources 23-1 to 23-4 has a known positional relationship with respect to the optical axis of the objective lens 22 from outside the objective lens 22 (not via the objective lens 22). A fixation luminous flux can be projected toward the subject's eye E from the emission position.

As shown in FIG. 1, the focus optical system 60 generates a split index used for focus adjustment of the eye E to be examined. The focus optical system 60 is moved along the optical path (illumination optical path) of the illumination optical system 10 in conjunction with the movement of the imaging focusing lens 31 along the optical path (illumination optical path) of the imaging optical system 30 . The reflecting bar 67 can be inserted into and removed from the illumination optical path. When performing focus adjustment, the reflecting surface of the reflecting bar 67 is arranged at an angle in the illumination optical path. Focus light output from the LED 61 passes through a relay lens 62, is split into two light beams by a split index plate 63, passes through a two-hole diaphragm 64, is reflected by a mirror 65, and is reflected by a condenser lens 66 onto a reflecting rod 67. is once imaged on the reflective surface of , and then reflected. Further, the focused light passes through the relay lens 20, is reflected by the perforated mirror 21, passes through the dichroic mirror 46, is refracted by the objective lens 22, and is projected onto the fundus oculi Ef. The fundus reflected light of the focus light is guided to the image sensor 35 through the same path as the return light of the observation illumination light. Manual focus and autofocus can be performed based on the received light image (split index image).

The dichroic mirror 46 synthesizes the fundus imaging optical path and the OCT optical path. The dichroic mirror 46 reflects light in the wavelength band used for OCT and transmits light for fundus imaging. The optical path for OCT (the optical path of the measurement light) includes, in order from the OCT unit 100 side toward the dichroic mirror 46 side, a collimator lens unit 40, an optical path length changing section 41, an optical scanner 42, an OCT focusing lens 43, a mirror 44, and a relay lens 45 are provided.

The optical path length changing unit 41 is movable in the direction of the arrow shown in FIG. 1, and changes the length of the OCT optical path. This change in optical path length is used for optical path length correction according to the axial length of the eye, adjustment of the state of interference, and the like. The optical path length changing section 41 includes a corner cube and a mechanism for moving it.

The optical scanner 42 is arranged at a position optically conjugate with the pupil of the eye E to be examined. The optical scanner 42 deflects the measurement light LS passing through the OCT optical path. The optical scanner 42 is, for example, a galvanometer scanner capable of two-dimensional scanning.

The OCT focusing lens 43 is moved along the optical path of the measurement light LS in order to adjust the focus of the OCT optical system. Movement of the imaging focusing lens 31, movement of the focusing optical system 60, and movement of the OCT focusing lens 43 can be controlled in a coordinated manner.

[

Anterior segment cameras

5A and 5B]
The

anterior eye cameras

5A and 5B are used to determine the relative position between the optical system of the ophthalmologic apparatus 1 and the subject's eye E, similar to the invention disclosed in Japanese Patent Laid-Open No. 2013-248376. The

anterior eye cameras

5A and 5B are provided on the face of the subject's eye E side of a housing (fundus camera unit 2, etc.) housing an optical system. The ophthalmologic apparatus 1 analyzes two anterior segment images obtained substantially simultaneously from different directions by the

anterior segment cameras

5A and 5B, thereby determining the three-dimensional relative relationship between the optical system and the subject's eye E. find the position. The analysis of the two anterior segment images may be similar to the analysis disclosed in Japanese Patent Application Laid-Open No. 2013-248376. Also, the number of anterior segment cameras may be any number of two or more.

In this example, the position of the eye to be examined E (that is, the relative position between the eye to be examined E and the optical system) is obtained using two or more anterior eye cameras. It is not limited to this. For example, the position of the eye E to be examined can be obtained by analyzing a front image of the eye E to be examined (for example, an observed image of the anterior segment Ea). Alternatively, means for projecting an index onto the cornea of the subject's eye E can be provided, and the position of the subject's eye E can be obtained based on the projection position of this index (that is, the detection state of the corneal reflected light flux of this index).

[OCT unit 100]
As illustrated in FIG. 5, the OCT unit 100 is provided with an optical system for performing swept-source OCT. This optical system includes an interference optical system. This interference optical system has a function of dividing light from a wavelength tunable light source (wavelength swept light source) into measurement light and reference light, return light of the measurement light from the subject's eye E, and reference light passing through the reference light path. and a function of generating interference light and a function of detecting this interference light. A detection result (detection signal) of the interference light obtained by the interference optical system is a signal indicating the spectrum of the interference light, and is sent to the arithmetic control unit (control section 210, image forming section 220, data processing section 230).

The light source unit 101 includes, for example, a near-infrared tunable laser that changes the wavelength of emitted light at high speed. The light L0 output from the light source unit 101 is guided to the polarization controller 103 by the optical fiber 102, and the polarization state is adjusted. The light L0 whose polarization state has been adjusted is guided by the optical fiber 104 to the fiber coupler 105 and split into the measurement light LS and the reference light LR.

The reference light LR is guided to the collimator 111 by the optical fiber 110, converted into a parallel beam, passed through the optical path length correction member 112 and the dispersion compensation member 113, and 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 and the optical path length of the measurement light LS. The dispersion compensation member 113 acts to match the dispersion characteristics between the reference light LR and the measurement light LS. The corner cube 114 is movable in the incident direction of the reference light LR, thereby changing the optical path length of the reference light LR.

The reference light LR that has passed through the corner cube 114 passes through the dispersion compensating member 113 and the optical path length correcting member 112 , is converted by the collimator 116 from a parallel beam into a converged beam, and enters the optical fiber 117 . The reference light LR incident on the optical fiber 117 is guided to the polarization controller 118 to have its polarization state adjusted, guided to the attenuator 120 via the optical fiber 119 to have its light amount adjusted, and guided to the fiber coupler 122 via the optical fiber 121 . be killed.

On the other hand, the measurement light LS generated by the fiber coupler 105 is guided by the optical fiber 127 and converted into a parallel light beam by the collimator lens unit 40, and the optical path length changing unit 41, the optical scanner 42, the OCT focusing lens 43, and the mirror 44. and relay lens 45 . The measurement light LS that has passed through the relay lens 45 is reflected by the dichroic mirror 46, refracted by the objective lens 22, and enters the eye E to be examined. The measurement light LS is scattered and reflected at various depth positions of the eye E to be examined. The return light of the measurement light LS from the subject's eye E travels in the opposite direction along the same path as the forward path, is guided to the fiber coupler 105 , and reaches the fiber coupler 122 via the optical fiber 128 . It should be noted that the incident length of the optical fiber 127 into which the measurement light LS is incident is arranged at a position substantially conjugate with the fundus oculi Ef of the eye E to be examined.

The fiber coupler 122 combines (interferences) the measurement light LS that has entered via the optical fiber 128 and the reference light LR that has entered via the optical fiber 121 to generate interference light. The fiber coupler 122 generates a pair of interference lights LC by splitting the interference lights at a predetermined splitting ratio (for example, 1:1). A pair of interference lights LC are guided to detector 125 through

optical fibers

123 and 124, respectively.

The detector 125 is, for example, a balanced photodiode. A balanced photodiode includes a pair of photodetectors that respectively detect a pair of interference lights LC, and outputs a difference between a pair of detection results obtained by these photodetectors. The detector 125 sends this output (detection signal) to a DAQ (Data Acquisition System) 130 .

A clock KC is supplied from the light source unit 101 to the DAQ 130 . The clock KC is generated in the light source unit 101 in synchronization with the output timing of each wavelength swept within a predetermined wavelength range by the wavelength tunable light source. The light source unit 101, for example, optically delays one of the two branched lights obtained by branching the light L0 of each output wavelength, and then outputs 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. The DAQ 130 sends the sampling result of the detection signal from the detector 125 to the arithmetic control unit (control section 210, etc.).

In this example, an optical path length changing unit 41 for changing the length of the optical path (measurement optical path, measurement arm) of the measurement light LS and an optical path length changing unit 41 for changing the length of the optical path (reference optical path, reference arm) of the reference light LR corner cubes 114 are provided. However, only one of the optical path length changing portion 41 and the corner cube 114 may be provided. It is also possible to change the difference between the measurement optical path length and the reference optical path length by using optical members other than these.

[Control system]
FIG. 6 shows a configuration example of the control system of the ophthalmologic apparatus 1. As shown in FIG. In FIG. 6, some of the components included in the ophthalmologic apparatus 1 are omitted. In FIG. 6, the same parts as in FIGS. 1 to 5 are denoted by the same reference numerals, and the description thereof will be omitted as appropriate.

The control unit 210, the image forming unit 220, and the data processing unit 230 are provided, for example, in the arithmetic control unit described above.

<Control unit 210>
The control unit 210 executes various controls. Control unit 210 includes main control unit 211 and storage unit 212 .

<Main control unit 211>
The main controller 211 includes a processor (eg, control processor) and controls each part of the ophthalmologic apparatus 1 (including each element shown in FIGS. 1 to 5). For example, the main control unit 211 controls each part of the optical system of the retinal camera unit 2 shown in FIGS. , tilt mechanism 152 , image forming unit 220 , data processing unit 230 , and user interface (UI) 240 .

The control of the retinal camera unit 2 includes control of the

focus driving units

31A and 43A, control of the

image sensors

35 and 38, control of the optical path length changing unit 41, control of the optical scanner 42, and control of the external fixation unit 23. included.

The control for the focus drive unit 31A includes control for moving the photographing focus lens 31 in the optical axis direction. The control for the focus drive unit 43A includes control for moving the OCT focus lens 43 in the optical axis direction.

The control of the

image sensors

35 and 38 includes control of the light receiving sensitivity of the imaging element, control of the frame rate (light receiving timing, exposure time), control of the light receiving area (position, size, size), and readout of the light receiving result of the imaging element. control, etc.

Control over the LCD 39 includes control of the fixation position by internal fixation (the exit position of the fixation light beam, the projection position of the fixation light beam on the fundus). For example, the main control unit 211 displays the fixation target at a position on the screen of the LCD 39 corresponding to the fixation position set manually or automatically. Further, the main control unit 211 can change (continuously or stepwise) the display position of the fixation target displayed on the LCD 39 . Thereby, the fixation target can be moved (that is, the fixation position can be changed). The display position and movement mode of the fixation target are set manually or automatically. Manual setting is performed using, for example, a GUI. Automatic setting is performed by the data processing unit 230, for example.

The control over the optical path length changing unit 41 includes control for changing the optical path length of the measurement light LS. The main control unit 211 moves the optical path length changing unit 41 along the optical path of the measuring light LS by controlling the driving unit that drives the corner cubes of the optical path length changing unit 41 to change the optical path length of the measuring light LS. .

Control of the optical scanner 42 includes control of scan mode, scan range (scan start position, scan end position), scan speed, and the like. By controlling the optical scanner 42, the main control unit 211 can perform an OCT scan with the measurement light LS on a desired region of the measurement site (imaging site).

Control over the external fixation unit 23 includes control of the fixation position by external fixation. For example, the main control unit 211 controls the external fixation unit 23 according to the fixation position set manually or automatically, rotates the fixation light source holding member 23B around the optical axis O, Any one of the light sources 23-1 to 23-4 is turned on. As a result, the fixation light flux can be projected onto the subject's eye E from the emission position corresponding to the set fixation position without passing through the objective lens 22 . In addition, the main controller 211 can change (continuously or stepwise) the emission position of the fixation light flux by controlling the external fixation unit 23 . As a result, the fixation target for external fixation can be moved (that is, the fixation position can be changed). The position and movement mode of the fixation target for external fixation are set manually or automatically. Manual setting is performed using, for example, a GUI. Automatic setting is performed by the main control unit 211 or the data processing unit 230, for example.

The main control unit 211 also controls the observation light source 11, the photographing light source 15, the focus optical system 60, and the like.

Control over the OCT unit 100 includes control over the light source unit 101, control over the reference driver 114A, control over the detector 125, and control over the DAQ 130.

The control of the light source unit 101 includes control of turning on and off of the light source, control of the amount of light emitted from the light source, control of the wavelength sweep range, wavelength sweep speed, control of emission timing of light of each wavelength component, and the like. .

The control over the reference driver 114A includes control to change the optical path length of the reference light LR. The main control unit 211 moves the corner cube 114 along the optical path of the reference light LR by controlling the reference driving unit 114A to change the optical path length of the reference light LR.

The control of the detector 125 includes control of the light receiving sensitivity of the detecting element, control of the frame rate (light receiving timing), control of the light receiving area (position, size, size), control of reading the light receiving result of the detecting element, and the like.

Control over the DAQ 130 includes fetch control (fetch timing, sampling timing) of the detection result of interference light obtained by the detector 125, readout control of the interference signal corresponding to the detection result of the fetched interference light, and the like.

The control for the

anterior eye cameras

5A and 5B includes control of the light receiving sensitivity of each camera, frame rate (light receiving timing) control, synchronization control of the

anterior eye cameras

5A and 5B, and the like.

The xyz movement mechanism 150 moves the fundus camera unit 2 (optical system) in the x, y, and z directions. In a typical example, the xyz movement mechanism 150 includes at least a mechanism for moving the retinal camera unit 2 in the x direction (horizontal direction), a mechanism for moving it in the y direction (vertical direction), and a mechanism for moving the fundus camera unit 2 in the z direction (vertical direction). direction, back and forth). The mechanism for moving in the x-direction includes, for example, an x-stage movable in the x-direction and an x-moving mechanism for moving the x-stage. The mechanism for moving in the y-direction includes, for example, a y-stage movable in the y-direction and a y-moving mechanism for moving the y-stage. The mechanism for moving in the z-direction includes, for example, a z-stage movable in the z-direction and a z-moving mechanism for moving the z-stage. Each movement mechanism includes a pulse motor as an actuator and operates under control from the main control unit 211 .

Control over the xyz movement mechanism 150 is used in alignment and tracking. Tracking is to move the apparatus optical system according to the eye movement of the eye E to be examined. Alignment and focus adjustment are performed in advance when tracking is performed. Tracking is a function of maintaining a suitable positional relationship in which alignment and focus are achieved by causing the position of the apparatus optical system to follow the movement of the eyeball. Some embodiments are configured to control the xyz movement mechanism 150 to change the optical path length of the reference beam (and thus the optical path length difference between the optical path of the measurement beam and the optical path of the reference beam). .

In the case of manual alignment, the user relatively moves the optical system and the subject's eye E by operating the user interface 240 so that the displacement of the subject's eye E with respect to the optical system is cancelled. For example, the main control unit 211 controls the xyz moving mechanism 150 to move the optical system relative to the eye E by outputting a control signal corresponding to the operation content of the user interface 240 to the xyz moving mechanism 150 .

In the case of auto-alignment, the main control unit 211 controls the xyz movement mechanism 150 so that the optical system is relatively moved with respect to the eye E to be examined so that the displacement of the eye E to be examined with respect to the optical system is cancelled. Specifically, as described in JP-A-2013-248376, arithmetic processing using trigonometry based on the positional relationship between the pair of

anterior eye cameras

5A and 5B and the subject's eye E is performed, and the main control unit 211 controls the xyz moving mechanism 150 so that the eye to be examined E has a predetermined positional relationship with respect to the optical system. In some embodiments, the main controller 211 outputs a control signal such that the optical axis of the optical system substantially coincides with the axis of the eye E to be examined and the distance of the optical system from the eye E to be examined is a predetermined working distance. to the xyz moving mechanism 150 to control the xyz moving mechanism 150 to move the optical system relative to the eye E to be examined. Here, the working distance is a default value also called a working distance of the objective lens 22, and corresponds to the distance between the subject's eye E and the optical system at the time of measurement (at the time of photographing) using the optical system.

The swing mechanism 151 swings the retinal camera unit 2 in the horizontal direction around the pupil of the eye E to be examined. Thereby, the horizontal component (horizontal angle) of the angle between the visual axis of the subject's eye E and the optical axis of the optical system can be changed. For example, the swing mechanism 151 is provided on a stage on which at least the retinal camera unit 2 is mounted and which is moved by the xyz movement mechanism 150 . The swing mechanism 151 includes a pulse motor as an actuator and operates under the control of the main controller 211 .

The tilt mechanism 152 pivots the retinal camera unit 2 vertically around the pupil of the eye E to be examined. This makes it possible to change the vertical component (elevation/depression angle) of the angle between the visual axis of the subject's eye E and the optical axis of the optical system. For example, the tilt mechanism 152 is provided on a stage on which at least the fundus camera unit 2 is mounted and which is moved by the xyz movement mechanism 150 . The tilt mechanism 152 includes a pulse motor as an actuator and operates under the control of the main controller 211 .

FIG. 7 shows an explanatory diagram of the angle changing operation by the swing mechanism 151 and the tilt mechanism 152 according to the embodiment. FIG. 7 represents a schematic diagram of the appearance of the ophthalmic apparatus 1 when viewed from the side.

The ophthalmologic apparatus 1 includes a base 1A and a pedestal 1B mounted on the base 1A so as to be movable in the front, rear, left, and right directions (horizontal direction) and in the vertical direction. A joystick 1C as an operation unit 240B is installed on the base 1B. For example, the gantry 1B is moved forward, backward, left, right, up and down on the base 1A by operating the joystick 1C. Note that an operation button as an operation unit 240B is arranged at the tip of the joystick 1C, and by pressing the operation button, it is possible to instruct the start of shooting.

The base 1A is provided with a chin rest and a forehead (not shown). The chin rest and forehead support fix the subject's (patient's) face to a head section 1D (housing) described later during measurement.

A head part 1D is provided on the base 1B. The head unit 1D accommodates the optical system of the retinal camera unit 2, the optical system of the OCT unit 100, and the arithmetic control unit (control unit 210), and is attached to the pedestal 1B via a swing mechanism 151 and a tilt mechanism 152 as an angle changing mechanism. Supported. The head part 1D is configured to be able to turn vertically and horizontally on the base 1B by means of a swing mechanism 151 and a tilt mechanism 152 .

For example, the swing mechanism 151 includes a base portion 1E, a support arm 1F, a rotation shaft portion 1G, and a horizontal rotation portion 1H. The base 1E is fixed on the base 1B. The support arm 1F is a rod-shaped member extending in the front-rear direction. One end of the support arm 1F is fixed on the base 1E, and the other end is arranged on a vertical line passing through the pupil Ep of the eye E to be examined. The rotating shaft portion 1G is a cylindrical member provided on the other end of the support arm 1F and extending in the vertical direction.

A bearing hole is formed in the horizontal rotation portion 1H. By inserting the rotating shaft portion 1G into the bearing hole, the horizontal rotating portion 1H can rotate about the rotating shaft extending in the vertical direction of the rotating shaft portion 1G with respect to the support arm 1F. be done.

As a result, the swing mechanism 151 aligns the horizontal position of the rotation shaft of the rotation shaft portion 1G with the pupil (for example, the center of the pupil) Ep of the eye E to be examined, so that the support arm 1F and the support arm 1F and the support arm 1F move around the pupil Ep. The tilt mechanism 152 can be rotated in the horizontal direction.

The tilt mechanism 152 includes a curved arm 1J.

The curved arm 1J guides the tilting motion of the head section 1D. The curved arm 1J includes, for example, a pair of curved arms that hold the head section 1D from both sides, and guides the movement of the head section 1D along the curved arms. Each curved arm is formed in an arc shape having a central axis line extending in the left-right direction set on an extension line of the rotation shaft portion 1G as a center of curvature. One end (lower end) of each curved arm is fixed to the horizontal rotating portion 1H.

Thereby, the tilt mechanism 152 can vertically rotate the head part 1D around the pupil Ep by aligning the position of the center of curvature of the curved arm 1J with the pupil Ep of the eye E to be examined.

In some embodiments, a sensor that detects the horizontal angle of the head section 1D by the swing mechanism 151 is provided, and the main control section 211 can acquire the horizontal angle of the head section 1D. In some embodiments, a sensor that detects the elevation/depression angle of the head unit 1D by the tilt mechanism 152 is provided, and the main control unit 211 can acquire the elevation/depression angle of the head unit 1D.

In FIG. 6, the main control unit 211 can display various information on the display unit 240A as a display control unit. For example, the main control unit 211 causes the display unit 240A to display an OCT image formed by the image forming unit 220, which will be described later, and a data processing result obtained by the data processing unit 230, which will be described later.

<Storage unit 212>
The storage unit 212 stores various data. The function of the storage unit 212 is implemented by a storage device such as a memory or a storage device. The data stored in the storage unit 212 includes, for example, control information, image data of a fundus image, image data of an anterior segment image, OCT data (including an OCT image), eye information to be examined, and the like. Examples of control information include shooting position table information and fixation control information. The imaging position table information and the fixation control information will be described later. The eye information to be examined includes information about the subject such as patient ID and name, information about the eye to be examined such as left/right eye identification information, and electronic medical record information. The storage unit 212 stores programs for executing various processors (control processor, image forming processor, data processing processor).

When fundus photography or OCT measurement is performed, the main control unit 211 according to the embodiment executes fixation control according to the distance from the optical axis O of the optical system to the OCT measurement position in the fundus oculi Ef.

FIG. 8 shows an explanatory diagram of fixation control according to the embodiment. FIG. 8 schematically shows an imaging range (a fundus imaging range using the imaging optical system 30, an OCT imaging range) from a position corresponding to the optical axis O in the fundus oculi Ef.

The central range including the position O1 corresponding to the optical axis O is the central fixation range Fc. In the central fixation range Fc, the main control unit 211 controls, for example, the LCD 39 to present internal fixation to the subject's eye E so as to fixate the center of the optical axis.

The peripheral range outside the central fixation range Fc is the inner fixation range Fi. In the internal fixation range Fi, the main control unit 211 controls, for example, the LCD 39 to present an internal fixation to the subject's eye E so as to fixate the fixation position in the internal fixation range Fi.

The peripheral range outside the inner fixation range Fi is the first outer fixation range Fo1. In the first external fixation range Fo1, the main controller 211 controls, for example, the external fixation unit 23 to fixate the fixation position in the first external fixation range Fo1. is turned on to present external fixation to the eye E to be examined.

The peripheral range outside the first external fixation range Fo1 is the second external fixation range Fo2. In the second external fixation range Fo2, the main control unit 211 controls, for example, the external fixation unit 23 to cause the external fixation light source 23-2 to fixate the fixation position in the second external fixation range Fo2. is turned on to present external fixation to the eye E to be examined.

The peripheral range outside the second outer fixation range Fo2 is the third outer fixation range Fo3. In the third external fixation range Fo3, the main control unit 211 controls, for example, the external fixation unit 23 to cause the external fixation light source 23-3 to fixate the fixation position in the third external fixation range Fo3. is turned on to present external fixation to the eye E to be examined.

The peripheral range outside the third outer fixation range Fo3 is the fourth outer fixation range Fo4. In the fourth external fixation range Fo4, the main control unit 211 controls, for example, the external fixation unit 23 to fixate the fixation position in the fourth external fixation range Fo4. is turned on to present external fixation to the eye E to be examined.

For example, when obtaining an OCT image by setting OCT measurement for a fundus image, it is desirable to specify the position of the OCT image in the fundus image. When the OCT measurement position is in the central fixation range Fc or the internal fixation range Fi including the position corresponding to the measurement optical axis (for example, the optical axis of the objective lens 22) in the fundus image, the main controller 211 controls the eye E control the fixation system to present an internal fixation at When the OCT image acquired by the OCT measurement performed in a state in which internal fixation is presented is associated with the fundus image, the analysis unit 231, which will be described later, calculates the fundus image based on the fixation position where the fixation light flux is projected. can identify the location of the OCT image (eg, OCT scan area) in .

When the OCT measurement position is outside the predetermined range including the position corresponding to the measurement optical axis in the fundus image (for example, any one of the first external fixation range Fo1 to the fourth external fixation range Fo4), the main control unit 211 controls the fixation system to present the eye E to be examined with an external fixation. When the OCT image acquired by the OCT measurement performed in the state where the external fixation is presented is associated with the fundus image, the analysis unit 231 performs OCT on the fundus image based on the fixation position where the fixation light flux is projected. The location of the image (eg, OCT scan area) can be identified.

The main control unit 211 according to the embodiment refers to photographing position table information in which fixation positions corresponding to photographing positions are associated in advance, thereby photographing a wide range of the fundus oculi Ef. As a result, a wide range of the fundus oculi Ef can be observed in detail without changing the direction of the subject's eye E (the direction of the line of sight).

FIG. 9 shows an overview of the shooting position table information according to the embodiment.

The shooting position table information includes multiple pieces of fixation position information and multiple pieces of shooting position information. Each piece of fixation position information is pre-associated with corresponding imaging position information. The fixation position information is, for example, information representing the projection position of the fixation target on the fundus. The imaging position information is information representing the imaging position on the fundus, which is the imaging target using the imaging optical system 30 . For example, in the photographing position table information, photographing position information SP-1 is associated with fixation position information FP-1, and photographing position information SP-2 is associated with fixation position information FP-2. . . , the photographing position information SP-n is associated with the fixation position information FP-n (n is an integer equal to or greater than 2).

Note that in this embodiment, the optical axis of the imaging optical system 30 is coupled to the optical axis of the OCT unit 100 substantially coaxially. Thereby, the OCT imaging position on the fundus measured using the OCT unit 100 can be uniquely specified from the imaging position on the fundus imaged using the imaging optical system 30 . Similarly, from the OCT imaging position on the fundus measured using the OCT unit 100, the imaging position on the fundus imaged using the imaging optical system 30 can be uniquely specified.

In some embodiments, the information representing the shooting position is information representing the shooting position itself. In some embodiments, the information representing the shooting position is information representing the shooting area including the shooting position. In this embodiment, the imaging position information is information representing any of the superior area, inferior area, temporal area, and nasal area with respect to the fovea. and Such imaging position table information is determined in advance in consideration of the configuration of the optical system.

The main control unit 211 or the data processing unit 230 refers to the photographing position table information stored in the storage unit 212 to identify photographing position information from the fixation position information, or extract fixation position information from the photographing position information. can be specified.

In some embodiments, the storage unit 212 stores a plurality of photographing position table information corresponding to optical information (for example, pupil size or axial length) of the subject's eye. The main control unit 211 or the data processing unit 230 can select the imaging position table information corresponding to the optical information of the subject's eye from among the plurality of imaging position table information, and refer to the selected imaging position table information.

In some embodiments, the main control unit 211 can change the content of the shooting position table information based on an operation signal corresponding to the user's operation on the operation unit 240B.

Further, the main control unit 211 according to the embodiment refers to fixation control information in which information for controlling internal fixation and information for controlling external fixation corresponding to the fixation position are associated in advance. Thereby, internal fixation or external fixation can be presented to the subject's eye E according to the fixation position.

FIG. 10 shows an overview of fixation control information according to the embodiment.

The fixation control information includes multiple pieces of fixation position information, multiple pieces of internal fixation control information, and multiple pieces of external fixation control information. Each fixation position information is pre-associated with internal fixation control information and external fixation control information. Internal fixation control information is information for controlling internal fixation. Examples of information for controlling internal fixation include lighting/non-lighting of the LCD 39, display pixel positions on the screen of the LCD 39, light intensity of the fixation luminous flux, switching timing of lighting and non-lighting for blink control, and the like. There is information for External fixation control information is information for controlling external fixation. Examples of information for controlling external fixation include lighting/non-lighting of each of the external light sources 23-1 to 23-4, the rotation angle of the fixation light source holding member 23B, and the external light sources 23-1 to 23-4. There is information for controlling the amount of light of each, switching timing between lighting and non-lighting for blinking control of each of the external light sources 23-1 to 23-4, and the like.

For example, in the fixation control information, the fixation position information FP-1 is associated with the internal fixation control information ifc-1 and the external fixation control information ofc-1, and the fixation position information FP-2 is associated with the internal fixation control information ifc-1 and external fixation control information ofc-1. are associated with internal fixation control information ifc-2 and external fixation control information ofc-2 corresponding to . . . Correspondingly, internal fixation control information ifc-n and external fixation control information ofc-n are associated.

By referring to the fixation control information stored in the storage unit 212, the main control unit 211 can control either the LCD 39 or the external fixation unit 23 according to the fixation position information. .

In some embodiments, the storage unit 212 stores a plurality of pieces of fixation control information corresponding to optical information (for example, pupil size or axial length) of the subject's eye. The main control unit 211 can select the optical information of the subject's eye or the fixation control information corresponding to the imaging position from among a plurality of pieces of fixation control information, and refer to the selected fixation control information.

In some embodiments, the main control unit 211 can change the content of the fixation control information based on the operation signal corresponding to the user's operation content on the operation unit 240B.

Furthermore, when the montage imaging range is set for the fundus that is the imaging target, the main control unit 211 according to the embodiment controls two or more OCT measurement positions (imaging range) set so as to cover the montage imaging range. to sequentially perform OCT imaging, and form an OCT montage image from the acquired OCT images. Each time the imaging position is moved, the main control unit 211 presents the fixation target at the fixation position corresponding to the OCT measurement position after the movement.

In some embodiments, in the montage imaging, an OCT montage image is obtained by setting a montage imaging range for a photographic image or observation image of the fundus. In some embodiments, the montage imaging acquires color or near-infrared montage images by setting a montage imaging range for OCT images of the fundus.

FIG. 11 shows an operation explanatory diagram of montage shooting according to the embodiment. FIG. 11 is a schematic diagram for explaining the montage photographing operation when the montage photographing range PR is set for the fundus image IMG acquired using the photographing optical system 30 .

The montage shooting range PR is set automatically or manually. When automatically setting the montage shooting range PR, for example, the data processing unit 230 analyzes the fundus image IMG to specify a characteristic region, and specifies the montage shooting range PR so as to include the specified characteristic region. When manually setting the montage shooting range PR, for example, the montage shooting range PR is specified based on an operation signal corresponding to the details of the user's operation on the operation unit 240B.

When the montage imaging range PR is set, the main control unit 211 controls the data processing unit 230 to identify two or more OCT imaging positions (OCT measurement positions). An OCT imaging range is determined corresponding to each OCT imaging position. In FIG. 11, nine OCT imaging ranges PA1 to PA9 are specified based on nine OCT imaging positions.

The main control unit 211 or the data processing unit 230 determines the order of imaging based on the specified two or more OCT imaging positions. For example, the main control unit 211 can determine the order of photographing such that, after photographing a plurality of photographing positions in the horizontal direction, photographing positions adjacent in the vertical direction are photographed.

The main control unit 211 controls the OCT unit 100 and the like to sequentially perform OCT imaging for two or more OCT imaging positions in the determined imaging order. At this time, every time the OCT imaging position is moved, the main control unit 211 presents the fixation target at the fixation position corresponding to the OCT imaging position after movement. By moving the OCT imaging position, internal fixation is switched to external fixation, and external fixation is switched to internal fixation.

The main control unit 211 forms an OCT montage image from the OCT images acquired by multiple times of imaging. At this time, the main control unit 211 can perform registration processing between the OCT image and the fundus image IMG to form an OCT montage image.

<Image forming unit 220>
As shown in FIG. 6, the image forming unit 220 includes a processor (for example, an image forming processor), and generates an OCT image (image data) of the subject's eye E based on the output (detection signal sampling result) from the DAQ 130. Form. For example, the image forming unit 220 performs signal processing on the spectral distribution based on the sampling result for each A line, forms a reflection intensity profile for each A line, and images these A line profiles as in the conventional swept source OCT. and arrange them along the scan lines. The signal processing includes noise removal (noise reduction), filtering, FFT (Fast Fourier Transform), and the like. When performing another type of OCT, the image forming section 220 performs known processing according to that type.

<Data processing unit 230>
The data processing unit 230 includes a processor (for example, a data processing processor) and performs image processing and analysis processing on the image formed by the image forming unit 220 . At least two of the processor included in the main control unit 211, the processor included in the data processing unit 230, and the processor included in the image forming unit 220 may be configured by a single processor.

The data processing unit 230 executes known image processing such as interpolation processing for interpolating pixels between tomographic images to form image data of a three-dimensional image of the fundus oculi Ef or the anterior segment Ea. Note that image data of a three-dimensional image means image data in which pixel positions are defined by a three-dimensional coordinate system. Image data of a three-dimensional image includes image data composed of voxels arranged three-dimensionally. This image data is called volume data or voxel data. When displaying an image based on volume data, the data processing unit 230 performs rendering processing (volume rendering, MIP (Maximum Intensity Projection: maximum intensity projection), etc.) on this volume data so that it can be viewed from a specific viewing direction. Image data of a pseudo three-dimensional image is formed. This pseudo three-dimensional image is displayed on a display device such as the display unit 240A.

It is also possible to form stack data of a plurality of tomographic images as image data of a three-dimensional image. Stacked data is image data obtained by three-dimensionally arranging a plurality of tomographic images obtained along a plurality of scan lines based on the positional relationship of the scan lines. That is, stack data is image data obtained by expressing a plurality of tomographic images, which were originally defined by individual two-dimensional coordinate systems, by one three-dimensional coordinate system (that is, embedding them in one three-dimensional space). be.

In some embodiments, the data processing unit 230 generates a B-scan image by arranging the A-scan images in the B-scan direction. In some embodiments, the data processing unit 230 performs various renderings on the acquired three-dimensional data set (volume data, stack data, etc.) to obtain a B-mode image (B-scan image) (longitudinal section) in an arbitrary cross section. plane image, axial cross-sectional image), C-mode image (C-scan image) at an arbitrary cross-section (cross-sectional image, horizontal cross-sectional image), projection image, shadowgram, and the like. An arbitrary cross-sectional image, such as a B-scan image or a C-scan image, is formed by selecting pixels (pixels, voxels) on a specified cross-section from a three-dimensional data set. A projection image is formed by projecting a three-dimensional data set in a predetermined direction (z direction, depth direction, axial direction). A shadowgram is formed by projecting a portion of the three-dimensional data set (for example, partial data corresponding to a specific layer) in a predetermined direction. By changing the depth range in the layer direction to be integrated, it is possible to form two or more different shadowgrams. An image such as a C-scan image, a projection image, or a shadowgram whose viewpoint is the front side of the subject's eye is called an en-face image.

The data processing unit 230 generates B-scan images and front images (blood vessel-enhanced images, angiograms) in which retinal vessels and choroidal vessels are emphasized based on data (for example, B-scan image data) collected in time series by OCT. can be constructed. For example, time-series OCT data can be collected by repeatedly scanning substantially the same portion of the eye E to be examined.

In some embodiments, the data processing unit 230 compares time-series B-scan images obtained by B-scans of substantially the same site, and converts the pixel values of the portions where the signal intensity changes to the pixel values corresponding to the changes. An enhanced image in which the changed portion is emphasized is constructed by the conversion. Furthermore, the data processing unit 230 extracts information for a predetermined thickness at a desired site from the constructed multiple enhanced images and constructs an en-face image to form an OCT angiogram.

The data processing unit 230 includes an analysis unit 231, a montage shooting processing unit 231C, and a registration processing unit 231D.

<analysis unit 231>
The analysis unit 231 includes a characteristic part identification unit 231A, a three-dimensional position calculation unit 231B, a montage imaging processing unit 231C, and a registration processing unit 231D.

The analysis unit 231 can analyze the image of the subject's eye E and identify the characteristic regions depicted in the image. For example, the analysis unit 231 obtains the three-dimensional position of the subject's eye E based on the positions of the

anterior eye cameras

5A and 5B and the positions of the specified characteristic regions. The main control unit 211 aligns the optical system with respect to the eye to be examined E by relatively moving the optical system with respect to the eye to be examined E based on the determined three-dimensional position.

<Characteristic part specifying unit 231A>
The characteristic site identification unit 231A analyzes each of the captured images obtained by the

anterior segment cameras

5A and 5B to identify positions (referred to as characteristic positions) in the captured images corresponding to the characteristic sites of the anterior segment Ea. Identify. For example, the pupil region of the subject eye E, the pupil center position of the subject eye E, the pupil center position, the corneal center position, the corneal vertex position, the subject eye center position, or the iris are used as the characteristic site. A specific example of processing for specifying the pupil center position of the eye E to be examined will be described below.

First, the characteristic part specifying unit 231A specifies an image region (pupil region) corresponding to the pupil of the subject's eye E based on the distribution of pixel values (such as luminance values) of the captured image. Since the pupil is generally drawn with lower luminance than other parts, the pupil region can be identified by searching for the low-luminance image region. At this time, the pupil region may be specified in consideration of the shape of the pupil. In other words, the pupil region can be identified by searching for a substantially circular low-brightness image region.

Next, the characteristic part identifying section 231A identifies the central position of the identified pupil region. Since the pupil is substantially circular as described above, it is possible to specify the outline of the pupil region, specify the center position of this outline (the approximate circle or approximate ellipse), and set this as the pupil center position. Alternatively, the center of gravity of the pupil region may be obtained and the position of the center of gravity may be specified as the position of the center of gravity of the pupil.

Even when identifying characteristic positions corresponding to other characteristic regions, it is possible to identify the characteristic positions based on the distribution of pixel values of the captured image in the same manner as described above.

The characteristic part identifying unit 231A can sequentially identify characteristic positions corresponding to characteristic parts in the captured images sequentially obtained by the

anterior eye cameras

5A and 5B. In addition, the characteristic part identification unit 231A may identify the characteristic position every one or more frames of the captured images sequentially obtained by the

anterior eye cameras

5A and 5B.

The characteristic part identifying unit 231A can identify the characteristic part identified like steam as a characteristic region for identifying the montage shooting range.

<Three-dimensional position calculator 231B>
The three-dimensional position calculation unit 231B calculates the three-dimensional positions of the characteristic regions of the subject's eye E based on the positions of the

anterior eye cameras

5A and 5B and the characteristic positions corresponding to the characteristic regions identified by the characteristic region identification unit 231A. Identify as a three-dimensional position. The three-dimensional position calculation unit 231B, as disclosed in JP-A-2013-248376, calculates the positions (known) of the two

anterior eye cameras

5A and 5B and corresponding to characteristic regions in the two captured images. The three-dimensional position of the subject's eye E is calculated by applying a known trigonometric method to the position where the eye E is to be examined. The three-dimensional position calculated by the three-dimensional position calculator 231B is sent to the main controller 211. FIG. Based on the three-dimensional position, the main control unit 211 determines that the x- and y-direction positions of the optical axis of the optical system match the x- and y-direction positions of the three-dimensional position, and that the z-direction distance is The xyz moving mechanism 150 is controlled so as to achieve a predetermined working distance.

<Montage shooting processing unit 231C>
The montage imaging processing unit 231C selects two or more OCT imaging positions based on the size of the montage imaging range set automatically or manually and the size of the OCT imaging region (or fundus imaging region using the imaging optical system 30). Identify. The montage imaging processing unit 231C identifies two or more OCT imaging positions such that the peripheral region of each OCT image overlaps the peripheral region of the adjacent OCT image. In some embodiments, the size of the OCT imaging field is a predetermined size. In some embodiments, the size is determined based on the size of the feature region identified when setting the montage capture area.

The functions of the montage shooting processing unit 231C may be configured to be realized by the control unit 210 (main control unit 211).

<Registration processing unit 231D>
The registration processing unit 231D performs registration processing on the two images.

For example, the registration processing unit 231D extracts two or more feature points from each of the two images, and aligns the two images so that the positions of the extracted feature points match. For example, feature points are blood vessels, blood vessel bifurcations, and lesions. In some embodiments, registration processor 231D performs an affine transform, a Helmert transform, or a free transform.

For example, the registration processing unit 231D extracts one or more characteristic regions from each of the two images, and performs least squares matching (LSM) on the extracted one or more characteristic regions from both images. The two images are aligned so that the sum of the squares of the grayscale differences between the two images is minimized. In some embodiments, registration processor 231D performs an affine transform, a Helmert transform, or a free transform.

For example, the registration processing unit 231D divides each of the two images into two or more partial images, and aligns the partial images based on the characteristic points or characteristic parts. In some embodiments, the registration processor 231D performs affine transformation, Helmert transformation, or free transformation for each partial image.

For example, the registration processing unit 231D obtains the degree of correlation between the two images, and aligns the two images so that the degree of correlation is greater than or equal to the threshold. In some embodiments, registration processor 231D performs an affine transform, a Helmert transform, or a free transform.

For example, the registration processing unit 231D divides each of the two images into two or more partial images, obtains the degree of correlation between the two images for each partial image, and maximizes the partial image whose degree of correlation is greater than or equal to the threshold. The two images are aligned as follows. In some embodiments, registration processor 231D performs an affine transform, a Helmert transform, or a free transform.

The registration processing unit 231D performs the above registration processing on the two OCT images. Examples of OCT images include projection images (live projection images), shadowgrams, C-scan images, en-face images, and OCT angiograms.

In some embodiments, the registration processing unit 231D performs the above registration processing on the fundus image and the OCT image. Examples of the fundus image include an observation image of the fundus obtained by the image sensor 35, a captured image of the fundus obtained by the image sensor 38, and a previously obtained fundus image. The observed image or captured image may be a near-infrared image or a color image.

Such a registration processing section 231D includes a scan area specifying section 2311D and an overlap determining section 2312D.

<Scan area specifying unit 2311D>
The scan area specifying unit 2311D specifies an OCT scan area (OCT image position) on the fundus image from the fixation position of the eye E to be examined.

Specifically, the scan area specifying unit 2311D refers to the imaging position table information shown in FIG. 9 to specify the imaging position information from the fixation position of the internal fixation or the external fixation, and the fundus oculi Ef from the imaging position information. Identify the shooting area in For example, the imaging area is an upper area, a lower area, an ear area, or a nasal area in the fundus oculi Ef. The scan area specifying unit 2311D extracts feature points in the specified imaging area. For example, the feature points are blood vessels, blood vessel bifurcations, or lesions. In some embodiments, extraction of feature points in the imaging area is performed by the feature site identification unit 231A.

Next, the scan area specifying unit 2311D (or the analysis unit 231) extracts feature points from the projection image created from the OCT data (for example, live OCT image) of the eye E to be examined. The scan area specifying unit 2311D specifies an OCT scan area corresponding to the imaging area in the fundus image so that the feature points extracted in the imaging area match the feature points extracted in the projection image.

<Overlap determination unit 2312D>
The overlap determination unit 2312D determines whether or not the peripheral regions of the two images obtained by montage photography overlap.

Since the two images to be determined are acquired with a gap of time between them, there is a possibility that there will be a positional deviation due to eyeball movement during that time. Therefore, the overlap determination unit 2312D according to the embodiment can determine not only whether or not the peripheral regions of the two images overlap, but also whether or not the two images have appropriate (good) image quality. can. For example, the overlap determination unit 2312D determines whether or not there is an overlap region between the two images, and when it is determined that there is an overlap region, further calculates the degree of correlation in the overlap region between the two images. When it is determined that the degree of correlation in the overlap region is equal to or greater than the threshold, the overlap determination unit 2312D determines that the two images acquired by montage photography overlap and that the two images have appropriate image quality. do.

The size of the peripheral area of the image for which the overlap determination unit 2312D performs determination processing may be a predetermined size, or the area where the two images overlap is specified, and the size of the specified area is adopted. You may

<User Interface 240>
User interface 240 includes a display section 240A and an operation section 240B. Display unit 240A includes display device 3 . The operation unit 240B includes various operation devices and input devices.

The user interface 240 may include a device such as a touch panel that combines a display function and an operation function. In other embodiments, at least a portion of the user interface may not be included on the ophthalmic device. For example, the display device may be an external device connected to the ophthalmic equipment.

<Communication unit 250>
The communication unit 250 has a function for communicating with an external device (not shown). The communication unit 250 has a communication interface according to a connection form with an external device. Examples of external devices include server devices, OCT devices, scanning laser ophthalmoscopes, slit lamp ophthalmoscopes, ophthalmic measurement devices, and ophthalmic treatment devices. Examples of ophthalmic measurement devices include eye refractometers, tonometers, specular microscopes, wavefront analyzers, perimeters, microperimeters, and the like. Examples of ophthalmic treatment devices include laser treatment devices, surgical devices, surgical microscopes, and the like. The external device may be a device (reader) that reads information from a recording medium, or a device (writer) that writes information to a recording medium. Furthermore, the external device may be a hospital information system (HIS) server, a DICOM (Digital Imaging and Communication in Medicine) server, a doctor terminal, a mobile terminal, a personal terminal, a cloud server, or the like.

The optical system from the OCT unit 100 to the objective lens 22 is an example of the "OCT optical system" according to the embodiment. The swing mechanism 151 or the tilt mechanism 152 is an example of the "angle changing mechanism" according to the embodiment. The optical system from the LCD 39 to the objective lens 22 or the external fixation unit 23 is an example of the "fixation system" according to the embodiment. The optical system from the LCD 39 to the objective lens 22 is an example of the "internal fixation system" according to the embodiment. The external fixation unit 23 is an example of the "external fixation system" according to the embodiment. A tilt mechanism is an example of a "first angle changing mechanism" according to the embodiment. The swing mechanism is an example of the "second angle changing mechanism" according to the embodiment.

<motion>
An operation example of the ophthalmologic apparatus 1 will be described.

14 to 17 show operation examples of the ophthalmologic apparatus 1 according to the embodiment. FIG. 14 shows a flowchart of a first operation example of the ophthalmologic apparatus 1 . FIG. 15 represents a flow diagram of an operation example of step S9 in FIG. 16 and 17 represent a flow chart of a second operation example of the ophthalmologic apparatus 1. FIG.

The storage unit 212 stores computer programs for realizing the processes shown in FIGS. The main control unit 211 executes the processes shown in FIGS. 14 to 17 by operating according to this computer program.

First, a first operation example of the ophthalmologic apparatus 1 will be described. In the first operation example, a fixation position is determined from an OCT imaging position specified in a fundus image (for example, a wide-angle fundus image), and internal fixation or external fixation is presented to the determined fixation position. OCT measurement is performed with (FIGS. 14 and 15).

(S1: Alignment)
First, the main controller 211 executes alignment.

For example, the main control unit 211 controls the

anterior segment cameras

5A and 5B to photograph the anterior segment Ea of the subject's eye E substantially simultaneously. The characteristic site identification unit 231A receives control from the main control unit 211, analyzes a pair of anterior segment images obtained substantially simultaneously by the

anterior segment cameras

5A and 5B, and identifies the pupil of the subject's eye E as a characteristic site. Identify the center position. The three-dimensional position calculator 231B obtains the three-dimensional position of the eye E to be examined. This processing includes arithmetic processing using trigonometry based on the positional relationship between the pair of

anterior eye cameras

5A and 5B and the subject's eye E, as described in Japanese Patent Application Laid-Open No. 2013-248376, for example.

Based on the three-dimensional position of the eye to be examined E calculated by the three-dimensional position calculator 231B, the main control unit 211 performs xyz calculation so that the optical system (for example, the fundus camera unit 2) and the eye to be examined E have a predetermined positional relationship. It controls the moving mechanism 150 . Here, the predetermined positional relationship is a positional relationship that enables imaging and examination of the subject's eye E using an optical system. As a typical example, when the three-dimensional position (x-coordinate, y-coordinate, z-coordinate) of the eye E to be examined is obtained by the three-dimensional position calculator 231B, the x-coordinate and y-coordinate of the optical axis of the objective lens 22 are the eye E and the difference between the z-coordinate of the objective lens 22 (front lens surface) and the z-coordinate of the eye to be examined E (corneal surface) is equal to a predetermined distance (working distance) , is set as the destination of the optical system.

(S2: Autofocus)
Subsequently, the main controller 211 starts autofocus.

For example, the main control unit 211 controls the focus optical system 60 to project the split index on the eye E to be examined. Under the control of the main control unit 211, the analysis unit 231 extracts a pair of split index images by analyzing the observed image of the fundus oculi Ef on which the split indices are projected, and calculates the relative relationship between the pair of split indices. Calculate the deviation. The main control unit 211 controls the focus driving unit 31A and the focus driving unit 43A based on the calculated deviation (direction of deviation, amount of deviation).

(S3: Set OCT imaging position)
Next, the main control unit 211 sets the OCT imaging position for a fundus image such as an infrared image (or moving image) of the fundus oculi Ef or a color fundus image of the fundus oculi Ef acquired in advance.

For example, the main control unit 211 sets the imaging position designated by the user operating the operation unit 240B while viewing the fundus image as the OCT imaging position. For example, the main control unit 211 causes the analysis unit 231 to analyze the fundus image to specify a characteristic region or a region of interest, and sets the position in the fundus image corresponding to the identified characteristic region or region of interest as the OCT imaging position.

(S4: Move optical system)
Next, the main control unit 211 performs fixation control so that the fixation light flux is projected to the fixation position on the fundus oculi Ef corresponding to the OCT imaging position set in step S3. When using external fixation, the main control unit 211 controls the external fixation unit 23, the swing mechanism 151, and the tilt mechanism 152 to change the direction of the visual axis of the eye E to be examined without changing the orientation of the eye E to be examined. and the direction of the optical axis of the optical system (measurement optical axis, objective optical axis).

For example, the main control unit 211 refers to the imaging position table information in FIG. 9 and specifies the fixation position information from the imaging position information corresponding to the OCT imaging position set in step S3. Next, the main control unit 211 refers to the internal fixation control information and the external fixation control information by referring to the fixation control information in FIG. When presenting the external fixation to the subject's eye E based on the external fixation control information, the main control unit 211 controls at least one of the external fixation unit 23, the swing mechanism 151, and the tilt mechanism 152 based on the external fixation control information. to control the emission position of the fixation light flux.

In some embodiments, the main control unit 211 causes the display unit 240A to display predetermined guidance information, and instructs the user to manually move at least one of the external fixation unit 23, the swing mechanism 151, and the tilt mechanism 152. encourage For example, the main control unit 211 acquires detection results from sensors provided in each of the external fixation unit 23 , the swing mechanism 151 and the tilt mechanism 152 . The main control unit 211 checks whether or not the external fixation unit 23, the swing mechanism 151, and the tilt mechanism 152 are set to desired states based on the acquired detection results. It is desirable to continue prompting the user for guidance until the predetermined state is set.

(S5: Presentation of fixation target)
Subsequently, the main control unit 211 causes the subject's eye E to present internal fixation or external fixation.

Specifically, the main control unit 211 presents internal fixation or external fixation to the subject's eye E as described above, based on internal fixation control information or external fixation control information. When presenting the internal fixation to the subject's eye E, the main control unit 211 controls the LCD 39 based on the internal fixation control information, and the fixation light beam is displayed from the display position of the LCD 39 designated based on the internal fixation control information. is emitted. When presenting an external fixation to the subject's eye E, the main control unit 211 controls the external fixation unit 23 based on the external fixation control information, and the fixation light source specified based on the external fixation control information Emits a fixation beam.

(S6: Adjust shooting position)
Subsequently, the main control unit 211 adjusts the shooting position.

Due to difficulty in eye movement and fixation of the subject's eye E, the desired imaging position may shift. Therefore, the main control unit 211 adjusts the shooting position based on the user's operation on the operation unit 240B. For example, while referring to a live OCT image (projection image or en-face image), the user operates the operation unit 240B to instruct to change the imaging position. Examples of adjustment of the imaging position include movement of the optical system with respect to the subject's eye E by the xyz movement mechanism 150, change of the emission position of the fixation light flux (including switching between internal fixation and external fixation), and offset with respect to the optical scanner 42. There are the application of a voltage, the change of the optical path length difference between the measurement light LS and the reference light LR, and the like.

In some embodiments, the process of step S6 is skipped.

(S7: OCT imaging)
Next, the main control unit 211 controls the OCT unit 100 and the like to perform OCT imaging at the OCT imaging position determined up to step S5 or the OCT imaging position adjusted at step S6. The main control unit 211 controls the image forming unit 220 to form an OCT image based on OCT data obtained by OCT imaging, and controls the data processing unit 230 to form a projection image or an en-face image.

(S8: fundus photography)
Subsequently, the main controller 211 controls the fundus camera unit 2 to photograph the fundus Ef. Thereby, a fundus image (for example, a color fundus image) of the fundus oculi Ef is obtained.

(S9: registration processing)
Next, the main control unit 211 controls the registration processing unit 231D to perform registration processing between the projection image or the en-face image acquired in step S7 and the fundus image acquired in step S8. .

The details of step S9 will be described later.

(S10: display)
Subsequently, the main control unit 211 causes the display unit 240A to display a synthesized image after aligning the projection image or the en-face image acquired in step S7 with the fundus image acquired in step S8.

This completes the first operation example of the ophthalmologic apparatus 1 (end).

The process of step S9 in FIG. 14 is executed according to the flow shown in FIG.

(S21: Specify the imaging area on the fundus from the fixation position)
First, the scan area specifying unit 2311D refers to the shooting position table information shown in FIG. 9 as described above, and specifies shooting position information from the fixation position determined by the processing up to step S4. The scan area specifying unit 2311D specifies the imaging area in the fundus image acquired in step S8 from the specified imaging position information.

(S22: Extract feature points of shooting area)
Next, the scan area identification unit 2311D extracts feature points in the imaging area identified in step S21 as described above.

(S23: Extract feature points from OCT image)
Subsequently, the scan area specifying unit 2311D (or the analysis unit 231) extracts feature points from the projection image created from the OCT data of the subject's eye E acquired in step S7 as described above.

(S24: Identify OCT scan area)
Next, as described above, the scan area specifying unit 2311D determines the photographing area in the fundus image so that the feature points of the fundus image extracted in step S22 and the feature points of the projection image extracted in step S23 match each other. Identify the OCT scan area corresponding to .

(S25: Matching process)
Subsequently, the registration processing unit 231D aligns the projection image based on the OCT data acquired in step S7 and the fundus image acquired in step S8 based on the OCT scan area specified in step S24. Execute the process. In some embodiments, the registration processing unit 231D registers the projection image based on the OCT data acquired in step S7 and the previously acquired fundus image based on the OCT scan area specified in step S24. to perform alignment processing. In this case, the fundus image acquired in advance is the fundus image acquired by the ophthalmologic apparatus 1 before executing the flow shown in FIG. It can be an image.

In this embodiment, the alignment (registration) of the projection image and the fundus image is performed within the OCT scan area specified in step S24, so the image search range is narrowed, and the processing load can be greatly reduced. can.

This completes the processing of step S9 in FIG. 14 (end).

Next, a second operation example of the ophthalmologic apparatus 1 will be described. In the second operation example, a plurality of OCT imaging positions are identified from a montage imaging range specified in a fundus image (for example, a wide-angle fundus image), and OCT imaging is sequentially performed on the identified plurality of imaging positions to perform OCT imaging. A montage image is acquired (FIGS. 16-17).

(S31: Alignment)
First, the main controller 211 performs alignment, as in step S1.

(S32: Autofocus)
Subsequently, the main control section 211 starts autofocus as in step S2.

(S33: Set montage shooting range)
Next, the main control unit 211 sets a montage photographing range for a fundus image such as an infrared image (or moving image) of the fundus oculi Ef or a color fundus image of the fundus oculi Ef acquired in advance.

For example, the main control unit 211 sets the imaging range designated by the user operating the operation unit 240B while viewing the fundus image as the montage imaging range. For example, the main control unit 211 causes the analysis unit 231 to analyze the fundus image to specify a characteristic region or a region of interest, and sets an imaging range of a predetermined size including the identified characteristic region or region of interest as the montage imaging range.

The main control unit 211 specifies two or more OCT imaging positions from the montage imaging range set in step S33 by controlling the montage imaging processing unit 231C. As described above, the montage imaging processing unit 231C is set so that the OCT imaging ranges corresponding to the respective OCT imaging positions overlap each other. Also, the main control unit 211 or the data processing unit 230 determines the imaging order based on the specified two or more OCT imaging positions.

(S34: Move optical system)
Next, the main control unit 211 projects the fixation light flux onto the fixation position on the fundus oculi Ef corresponding to one of the two or more OCT imaging positions, as in step S4, according to the imaging order determined in step S33. Perform fixation control so that

(S35: Presentation of fixation target)
Subsequently, the main control unit 211 causes the subject's eye E to present internal fixation or external fixation, as in step S5.

(S36: OCT imaging)
Next, the main controller 211 controls the OCT unit 100 and the like to perform OCT imaging at the OCT imaging positions determined up to step S34, as in step S7. The main control unit 211 controls the image forming unit 220 to form an OCT image based on OCT data obtained by OCT imaging, and controls the data processing unit 230 to form a projection image or an en-face image.

In some embodiments, the shooting position is adjusted between steps S35 and S36, as in step S5.

(S37: Overlap?)
Next, the main control unit 211 controls the overlap determination unit 2312D to determine whether or not two or more adjacent projection images (OCT images) acquired by repeatedly executing step S36 overlap each other. determine whether If only one projection image is acquired, the process of step S37 is skipped, and the operation of the ophthalmologic apparatus 1 proceeds to step S39.

For example, as described above, the overlap determination unit 2312D determines not only whether or not the peripheral regions overlap each other for each of two or more adjacent projection images, but also whether or not the two adjacent projection images have appropriate image quality. It is determined whether or not.

When it is determined that the two or more projection images adjacent to each other have an overlapping peripheral area and the image quality of the two adjacent projection images is appropriate for each other (step S37: Y), the ophthalmologic apparatus 1 operates. goes to step S39.

When it is determined that the peripheral regions of each of the two or more adjacent projection images do not overlap each other, or the two adjacent projection images do not have proper image quality (step S37: N), the ophthalmologic apparatus 1 operation proceeds to step S38.

(S38: End?)
Next, the main control unit 211 determines whether or not to end the process. For example, the main control unit 211 determines to end the process when the number of repetitions of step S35 is equal to or greater than a predetermined number. For example, the main control unit 211 determines to end the process when the evaluation value representing the image quality of the projection image determined in step S37 is equal to or less than a predetermined threshold.

When it is determined to end the process (step S38: Y), the operation of the ophthalmologic apparatus 1 ends (END). When it is determined not to end the processing (step S38: N), the operation of the ophthalmologic apparatus 1 proceeds to step S36, and OCT imaging is performed again.

(S39: Registration processing)
In step S37, for each of the two or more projection images adjacent to each other, when it is determined that the peripheral regions overlap and the two projection images adjacent to each other have appropriate image quality (step S37: Y), the main As in step S9, the control unit 211 controls the registration processing unit 231D to perform registration processing on each of two or more projection images adjacent to each other.

This forms part of an OCT montage image in which two or more projection images adjacent to each other are aligned.

(S40: next?)
Subsequently, the main control unit 211 determines whether or not to execute OCT imaging for the next imaging position. For example, the main control unit 211 determines whether or not to perform OCT imaging for the next imaging position according to the imaging order determined in step S34.

When it is determined in step S40 that OCT imaging is to be performed for the next imaging position (step S40: Y), the operation of the ophthalmologic apparatus 1 proceeds to step S34. As a result, OCT imaging is performed for the next imaging position. When it is determined in step S40 that OCT imaging is not to be performed for the next imaging position (step S40: N), the operation of the ophthalmologic apparatus 1 proceeds to step S41.

(S41: fundus photographing)
In step S40, when it is determined not to perform OCT imaging for the next imaging position (step S40: N), the main control section 211 controls the retinal camera unit 2 in the same manner as in step S8 to Execute shooting for Ef. Thereby, a fundus image (for example, a color fundus image) of the fundus oculi Ef is acquired.

(S42: display)
Subsequently, the main control unit 211 causes the display unit 240A to display the OCT montage image obtained by repeating steps S36 to S39. In some embodiments, the OCT montage image formed by repeating steps S36 to S39 is superimposed on the fundus image acquired in step S41 and displayed on the display unit 240A.

This completes the second operation example of the ophthalmologic apparatus 1 (end).

<Action>
An ophthalmologic apparatus, an ophthalmologic apparatus control method, and a program according to an embodiment will be described.

An ophthalmologic apparatus (1) according to some embodiments includes an optical system (optical systems shown in FIGS. 1, 2, and 5), an angle changing mechanism (swing mechanism 151, tilt mechanism 152), and a fixation system ( LCD 39, external fixation unit 23), control section (210, main control section 211), image forming section (220), and analysis section (231). The optical system includes an objective lens (22), an imaging optical system (30), and an OCT optical system (an optical system from the OCT unit 100 to the objective lens 22). The imaging optical system receives light from the subject's eye (E) via the objective lens. The OCT optical system is coupled to the optical path of the imaging optical system, projects the measurement light (LS) that has passed through the optical path onto the subject's eye via the objective lens, and produces interference light between the return light of the measurement light and the reference light (LR). (LC) is detected. The angle changing mechanism changes the direction of the optical axis of the optical system by tilting the optical system. The fixation system projects a fixation light flux toward the subject's eye from a fixation light flux emission position whose relative position to the optical axis can be changed. The control unit changes the angle formed by the visual axis of the subject's eye and the optical axis based on the OCT measurement position in the image of the subject's eye, and projects the fixation light beam from the emission position corresponding to the OCT measurement position. is projected, the OCT optical system is controlled to perform OCT measurement for the subject's eye. The image forming unit forms an OCT image of the subject's eye based on the detection result of the interference light. The analysis unit identifies the position of the OCT image in the image of the subject's eye based on the emission position.

According to such a configuration, while controlling the fixation system based on the OCT measurement position in the image of the eye to be inspected, the orientation of the optical axis of the optical system is changed by the angle changing mechanism, thereby widening the angle to the eye to be inspected. of OCT measurements can be performed. As a result, the subject's eye can be more easily photographed or measured at a wide angle without changing the orientation of the subject's face.

In some embodiments, the control unit causes the fixation system to project a fixation light flux on each of two or more OCT measurement positions. For each of the two or more OCT measurement positions, the analysis unit identifies the position of the OCT image in the image of the subject's eye based on the emission position in the fixation system.

According to such a configuration, it is possible to specify the position of the OCT image in the image of the subject's eye while controlling at least the fixation system for each of the two or more OCT measurement positions. Thereby, it becomes possible to acquire a composite image of multiple OCT images, such as a montage image.

In some embodiments, the fixation system is an external fixation system (external fixation system) that projects a fixation light flux toward the subject's eye from an exit position having a known positional relationship with respect to the optical axis from outside the objective lens. including a viewing unit 23).

According to such a configuration, the orientation of the optical axis of the optical system is changed by the angle changing mechanism while controlling the fixation system based on the OCT measurement position in the image of the subject's eye using the external fixation system. , it is possible to perform wide-angle OCT measurement on the subject's eye.

In some embodiments, the fixation system includes an internal fixation system (LCD 39) and an external fixation system (external fixation unit 23). The internal fixation system includes an internal fixation light source (display pixels on the screen of the LCD 39) whose position relative to the optical axis can be changed, and projects a fixation light beam onto the subject's eye via the objective lens. The external fixation system includes an external fixation light source (fixation light sources 23-1 to 23-4) whose relative position to the optical axis can be changed, and a known positional relationship to the optical axis is established from the outside of the objective lens. A fixation light beam is projected from the position of the external fixation light source provided toward the eye to be examined.

According to such a configuration, the internal fixation system and the external fixation system are used to control the fixation system based on the OCT measurement position in the image of the subject's eye, and the angle changing mechanism adjusts the optical axis of the optical system. By changing the orientation, it becomes possible to perform wide-angle OCT measurements on the subject's eye.

In some embodiments, when the OCT measurement position is within a predetermined range (central fixation range Fc or internal fixation range Fi) including a position corresponding to the optical axis in the image of the subject's eye, the control unit performs internal fixation. The system projects a fixation light beam onto the subject's eye, and the analysis unit identifies the position of the OCT image in the image of the subject's eye based on the fixation position where the fixation light beam is projected. When the OCT measurement position is outside the predetermined range (first external fixation range Fo1 to fourth external fixation range Fo4) including the position corresponding to the optical axis in the image of the subject's eye, the control unit controls the external fixation system. to project the fixation light flux onto the subject's eye, and the analysis unit specifies the position of the OCT image in the image of the subject's eye based on the fixation position where the fixation light flux is projected.

According to such a configuration, while switching between the internal fixation system and the external fixation system according to the OCT measurement position, the orientation of the optical axis of the optical system is changed by the angle changing mechanism. It becomes possible to perform wide-angle OCT measurements.

In some embodiments, the controller causes the internal fixation system or the external fixation system to project a fixation light beam on each of two or more OCT measurement positions. For each of the two or more OCT measurement positions, the analysis unit identifies the position of the OCT image in the image of the subject's eye based on the fixation position onto which the fixation light flux is projected.

According to such a configuration, the position of the OCT image in the image of the subject's eye can be specified for each of two or more OCT measurement positions while switching between the internal fixation system and the external fixation system according to the OCT measurement position. can be done. Thereby, it becomes possible to acquire a composite image of multiple OCT images, such as a montage image.

In some embodiments, the external fixation system is fixed relative to the optical system.

With such a configuration, since the positional relationship between the external fixation system and the optical axis is constant, the position of the OCT image in the image of the subject's eye can be easily processed based on the fixation position of the external fixation system. can be identified by

In some embodiments, the angle changing mechanism includes a first angle changing mechanism (tilt mechanism 152) that vertically changes the angle formed by the orientation of the optical axis with respect to the horizontal direction, and a tilt mechanism 152 that changes the angle formed by the orientation of the optical axis with respect to the vertical direction. and a second angle changing mechanism (swing mechanism 151) that changes the angle in the horizontal direction.

According to such a configuration, while controlling the fixation system based on the OCT measurement position in the image of the subject's eye, the orientation of the optical axis of the optical system is changed by the tilting motion and the swinging motion. , making it possible to perform wide-angle OCT measurements.

Some embodiments include an operation unit (240B), and the OCT measurement position is set based on the operation content for the image of the subject's eye using the operation unit.

According to such a configuration, it is possible to specify the position of the OCT image in the image of the subject's eye by performing OCT measurement on a desired OCT measurement position in the image of the subject's eye.

A control method for an ophthalmologic apparatus (1) according to some embodiments includes a control step, an image forming step, and an analysis step. The ophthalmologic apparatus (1) includes an optical system (the optical system shown in FIGS. 1, 2, and 5), an angle changing mechanism (swing mechanism 151, tilt mechanism 152), and a fixation system (LCD 39, external fixation unit 23 ) and including. The optical system includes an objective lens (22), an imaging optical system (30), and an OCT optical system (an optical system from the OCT unit 100 to the objective lens 22). The imaging optical system receives light from the subject's eye (E) via the objective lens. The OCT optical system is coupled to the optical path of the imaging optical system, projects the measurement light (LS) that has passed through the optical path onto the subject's eye via the objective lens, and produces interference light between the return light of the measurement light and the reference light (LR). (LC) is detected. The angle changing mechanism changes the direction of the optical axis of the optical system by tilting the optical system. The fixation system projects a fixation light flux toward the subject's eye from a fixation light flux emission position whose relative position to the optical axis can be changed. The control step changes the angle formed by the visual axis of the subject's eye and the optical axis based on the OCT measurement position in the image of the subject's eye, projects the fixation light flux from the emission position corresponding to the OCT measurement position, and is projected, the OCT optical system is controlled to perform OCT measurement for the subject's eye. The image forming step forms an OCT image of the subject's eye based on the detection result of the interference light. The analyzing step identifies the position of the OCT image in the image of the eye to be examined based on the emission position.

According to such a method, while controlling the fixation system based on the OCT measurement position in the image of the eye to be inspected, the orientation of the optical axis of the optical system is changed by the angle changing mechanism, thereby widening the angle of view of the eye to be inspected. of OCT measurements can be performed. As a result, the subject's eye can be more easily photographed or measured at a wide angle without changing the orientation of the subject's face.

In some embodiments, the control step causes the fixation system to project a fixation light flux on each of the two or more OCT measurement positions. The analysis step identifies the position of the OCT image in the image of the subject's eye based on the emission position in the fixation system for each of the two or more OCT measurement positions.

According to such a method, it is possible to specify the position of the OCT image in the image of the subject's eye while controlling at least the fixation system for each of the two or more OCT measurement positions. Thereby, it becomes possible to acquire a composite image of multiple OCT images, such as a montage image.

In some embodiments, the fixation system is an external fixation system (external fixation system) that projects a fixation light flux toward the subject's eye from an exit position having a known positional relationship with respect to the optical axis from outside the objective lens. visual unit).

According to such a method, the direction of the optical axis of the optical system is changed by the angle changing mechanism while controlling the fixation system based on the OCT measurement position in the image of the subject's eye using the external fixation system. , it is possible to perform wide-angle OCT measurement on the subject's eye.

According to this method, the internal fixation system and the external fixation system are used to control the fixation system based on the OCT measurement position in the image of the subject's eye, and the angle changing mechanism adjusts the optical axis of the optical system. By changing the orientation, it becomes possible to perform wide-angle OCT measurements on the subject's eye.

In some embodiments, when the OCT measurement position is within a predetermined range (central fixation range Fc or internal fixation range Fi) including a position corresponding to the optical axis in the image of the subject's eye, the control step The system projects a fixation light beam onto the subject's eye, and the analysis unit identifies the position of the OCT image in the image of the subject's eye based on the fixation position where the fixation light beam is projected. When the OCT measurement position is outside the predetermined range (first external fixation range Fo1 to fourth external fixation range Fo4) including the position corresponding to the optical axis in the image of the subject's eye, the control step includes: to project the fixation light flux onto the subject's eye, and the analysis unit specifies the position of the OCT image in the image of the subject's eye based on the fixation position where the fixation light flux is projected.

According to such a method, while switching between the internal fixation system and the external fixation system according to the OCT measurement position, the angle change mechanism changes the direction of the optical axis of the optical system, so that It becomes possible to perform wide-angle OCT measurements.

In some embodiments, the control step causes the internal fixation system or the external fixation system to project a fixation light beam on each of the two or more OCT measurement positions. The analyzing step identifies the position of the OCT image in the image of the subject's eye based on the fixation position onto which the fixation light flux is projected, for each of the two or more OCT measurement positions.

According to this method, the position of the OCT image in the image of the subject's eye is specified for each of two or more OCT measurement positions while switching between the internal fixation system and the external fixation system according to the OCT measurement position. can be done. Thereby, it becomes possible to acquire a composite image of multiple OCT images, such as a montage image.

According to such a method, since the positional relationship between the external fixation system and the optical axis is constant, the position of the OCT image in the image of the subject's eye can be simply processed based on the fixation position of the external fixation system. can be identified by

According to such a method, while controlling the fixation system based on the OCT measurement position in the image of the subject's eye, the orientation of the optical axis of the optical system is changed by tilting and swinging motions, thereby achieving a simple configuration. , making it possible to perform wide-angle OCT measurements.

In some embodiments, the OCT measurement position is set based on the operation content for the image of the subject's eye using the operation unit.

According to such a method, it is possible to specify the position of the OCT image in the image of the eye to be inspected by performing OCT measurement on the desired OCT measurement position in the image of the eye to be inspected.

A program according to some embodiments causes a computer to execute each step of the ophthalmologic apparatus control method described above.

According to such a program, while controlling the fixation system based on the OCT measurement position in the image of the eye to be inspected, the orientation of the optical axis of the optical system is changed by the angle changing mechanism, thereby widening the angle of view of the eye to be inspected. of OCT measurements can be performed. As a result, the subject's eye can be more easily photographed or measured at a wide angle without changing the orientation of the subject's face.

The embodiment described above is merely an example of the present invention. A person who intends to implement this invention can arbitrarily make modifications (omissions, substitutions, additions, etc.) within the scope of the gist of this invention.

In some embodiments, the storage unit 212 stores a program that causes a computer to execute the control method of the ophthalmologic apparatus. Such a program may be stored in any computer-readable recording medium. The recording medium may be electronic media using magnetism, light, magneto-optics, semiconductors, and the like. Typically, recording media are magnetic tapes, magnetic disks, optical disks, magneto-optical disks, flash memories, solid state drives, and the like.

1 Ophthalmic Device 2 Fundus Camera Unit 10 Illumination Optical System 22 Objective Lens 23 External Fixation Unit 30 Photographing Optical System 39 LCD
100 OCT unit 151 swing mechanism 152 tilt mechanism 210 control unit 211 main control unit 220 image forming unit 230 data processing unit 231 analysis unit 231C montage imaging processing unit 231D registration processing unit E eye to be examined Ef fundus

Claims

an objective lens, an imaging optical system for receiving light from an eye to be inspected via the objective lens, and an optical path of the imaging optical system for receiving measurement light that has passed through the optical path and is coupled to the eye to be inspected via the objective lens. an OCT optical system that detects interference light between the return light of the measurement light and the reference light by projecting the measurement light onto the
an angle changing mechanism that changes the direction of the optical axis of the optical system by tilting the optical system;
a fixation system that projects a fixation light flux toward the subject's eye from an emission position of the fixation light flux whose position relative to the optical axis is changeable;
changing the angle formed by the visual axis of the eye to be examined and the optical axis based on the OCT measurement position in the image of the eye to be examined, and projecting the fixation light flux from the emission position corresponding to the OCT measurement position; a control unit that controls the OCT optical system in a state in which a fixation light beam is projected to execute OCT measurement for the eye to be examined;
an image forming unit that forms an OCT image of the subject's eye based on the detection result of the interference light;
an analysis unit that specifies the position of the OCT image in the image of the eye to be inspected based on the emission position;
An ophthalmic device, comprising:
The control unit causes the fixation system to project the fixation light flux on each of two or more OCT measurement positions,
2. The analysis unit, for each of the two or more OCT measurement positions, specifies the position of the OCT image in the image of the subject's eye based on the emission position in the fixation system. An ophthalmic device as described.
The fixation system includes an external fixation system that projects the fixation light beam from the outside of the objective lens toward the subject's eye from the emission position having a known positional relationship with respect to the optical axis. 3. An ophthalmic device according to claim 1 or claim 2.
The fixation system includes:
an internal fixation system including an internal fixation light source whose position relative to the optical axis can be changed, and projecting the fixation light flux onto the eye to be inspected via the objective lens;
including an external fixation light source whose position relative to the optical axis can be changed, from the outside of the objective lens toward the eye to be examined from a position of the external fixation light source having a known positional relationship with the optical axis an external fixation system that projects the fixation light flux;
The ophthalmic device of claim 1, comprising:
When the OCT measurement position is within a predetermined range including the position corresponding to the optical axis in the image of the subject's eye, the control unit causes the internal fixation system to project the fixation light flux onto the subject's eye, and The analysis unit identifies the position of the OCT image in the image of the subject's eye based on the fixation position to which the fixation light beam is projected,
When the OCT measurement position is outside a predetermined range including the position corresponding to the optical axis in the image of the subject's eye, the control unit causes the external fixation system to project the fixation light beam onto the subject's eye. 5. The ophthalmologic apparatus according to claim 4, wherein the analysis unit identifies the position of the OCT image in the image of the subject's eye based on the fixation position onto which the fixation light flux is projected.
The control unit causes the internal fixation system or the external fixation system to project the fixation light flux on each of two or more OCT measurement positions,
The analysis unit identifies, for each of the two or more OCT measurement positions, the position of the OCT image in the image of the subject's eye based on the fixation position onto which the fixation light flux is projected. 6. The ophthalmic device according to claim 4 or 5.
The ophthalmologic apparatus according to any one of claims 3 to 6, wherein the external fixation system is fixed with respect to the optical system.
The angle changing mechanism is
a first angle changing mechanism that vertically changes the angle formed by the orientation of the optical axis with respect to the horizontal direction;
a second angle changing mechanism that changes the angle formed by the orientation of the optical axis with respect to the vertical direction in the horizontal direction;
The ophthalmic apparatus according to any one of claims 1 to 7, comprising:
including an operation part,
The ophthalmologic apparatus according to any one of claims 1 to 8, wherein the OCT measurement position is set based on the content of operation performed on the image of the eye to be inspected using the operation unit.
an objective lens, an imaging optical system for receiving light from an eye to be inspected via the objective lens, and an optical path of the imaging optical system for receiving measurement light that has passed through the optical path and is coupled to the eye to be inspected via the objective lens. an OCT optical system that detects interference light between the return light of the measurement light and the reference light by projecting the measurement light onto the
an angle changing mechanism that changes the direction of the optical axis of the optical system by tilting the optical system;
A control method for an ophthalmologic apparatus including a fixation system for projecting a fixation light flux toward the subject's eye from a fixation light flux emission position whose position relative to the optical axis can be changed,
changing the angle formed by the visual axis of the eye to be examined and the optical axis based on the OCT measurement position in the image of the eye to be examined, and projecting the fixation light flux from the emission position corresponding to the OCT measurement position; a control step of performing OCT measurement on the subject's eye by controlling the OCT optical system in a state in which a fixation light beam is projected;
an image forming step of forming an OCT image of the subject's eye based on the detection result of the interference light;
an analysis step of identifying the position of the OCT image in the image of the eye to be inspected based on the emission position;
A method of controlling an ophthalmic device, comprising:
The control step causes the fixation system to project the fixation light flux on each of two or more OCT measurement positions;
11. The method according to claim 10, wherein the analysis step identifies the position of the OCT image in the image of the subject's eye based on the exit position in the fixation system for each of the two or more OCT measurement positions. A method of controlling the described ophthalmic device.
The fixation system includes an external fixation system that projects the fixation light beam from the outside of the objective lens toward the subject's eye from the emission position having a known positional relationship with respect to the optical axis. 12. The method for controlling an ophthalmologic apparatus according to claim 10 or 11.
The fixation system includes:
an internal fixation system including an internal fixation light source whose position relative to the optical axis can be changed, and projecting the fixation light flux onto the eye to be inspected via the objective lens;
including an external fixation light source whose position relative to the optical axis can be changed, from the outside of the objective lens toward the eye to be examined from a position of the external fixation light source having a known positional relationship with the optical axis an external fixation system that projects the fixation light flux;
The method of controlling an ophthalmologic apparatus according to claim 10, comprising:
When the OCT measurement position is within a predetermined range including the position corresponding to the optical axis in the image of the subject's eye, the control step causes the internal fixation system to project the fixation light beam onto the subject's eye, and The analysis step identifies the position of the OCT image in the image of the subject's eye based on the fixation position to which the fixation light flux is projected,
When the OCT measurement position is outside a predetermined range including the position corresponding to the optical axis in the image of the subject's eye, the control step causes the external fixation system to project the fixation light beam onto the subject's eye. 14. The control of the ophthalmologic apparatus according to claim 13, wherein the analyzing step identifies the position of the OCT image in the image of the subject's eye based on the fixation position onto which the fixation light flux is projected. Method.
the control step causes the internal fixation system or the external fixation system to project the fixation light flux on each of two or more OCT measurement positions;
The analysis step identifies the position of the OCT image in the image of the subject's eye based on the fixation position onto which the fixation light flux is projected, for each of the two or more OCT measurement positions. 15. The method for controlling an ophthalmologic apparatus according to claim 13 or 14.
The method of controlling an ophthalmologic apparatus according to any one of claims 12 to 15, wherein the external fixation system is fixed with respect to the optical system.
The angle changing mechanism is
a first angle changing mechanism that vertically changes the angle formed by the orientation of the optical axis with respect to the horizontal direction;
a second angle changing mechanism that changes the angle formed by the orientation of the optical axis with respect to the vertical direction in the horizontal direction;
The method for controlling an ophthalmologic apparatus according to any one of claims 10 to 16, comprising:
The method for controlling an ophthalmologic apparatus according to any one of claims 10 to 17, wherein the OCT measurement position is set based on an operation content for the image of the eye to be examined using an operation unit. .
A program characterized by causing a computer to execute each step of the method for controlling an ophthalmologic apparatus according to any one of claims 10 to 18.