JP7231366B2 - Ophthalmic device and control method for the ophthalmic device - Google Patents

Description

The present invention relates to an ophthalmologic apparatus for optically examining an eye to be examined and a control method for the ophthalmic apparatus.

2. Description of the Related Art Conventionally, an optical coherence tomography is known as an ophthalmologic apparatus for optically examining an eye to be examined. Optical coherence tomography divides low-coherence light into two, guides one (signal light) to the fundus, and guides the other (reference light) to a predetermined reference object. This apparatus forms a tomographic image of the surface and deep tissue of the fundus based on the interference light obtained by superimposing the reference light (see, for example, Patent Document 1). The ophthalmologic apparatus disclosed in Patent Document 1 scans the fundus with signal light, which is low coherence light, and superimposes the fundus reflected light of the signal light on the reference light to obtain interference light.

JP 2007-117714 A

However, in the ophthalmologic apparatus, which is an optical coherence tomography, when the subject blinks while the signal light is guided to the fundus to obtain the judgment reflected light, the signal light is not guided to the fundus. . In this case, a cross-sectional image of the region of the fundus to which the signal light was not guided cannot be obtained. In the ophthalmologic apparatus described in Patent Document 1, no countermeasures are taken when the subject blinks or the like, and there is a possibility that a desired cross-sectional image cannot be obtained when the subject blinks or the like. be.

The present invention has been made to solve the above problems. It is an object of the present invention to provide an ophthalmic apparatus capable of obtaining an image and a control method thereof.

According to the present invention, an ophthalmologic apparatus for optically inspecting an eye to be inspected includes an inspection optical system for optically inspecting an inspection range of the fundus of the eye to be inspected and outputting a detection signal. an inspection unit, an image forming unit that forms a cross-sectional image of the fundus based on the detection signal detected by the inspection unit, and an imaging unit that acquires an anterior segment image by imaging the anterior segment of the subject's eye. a control unit that controls the ophthalmologic apparatus; and a determination unit that determines whether the inspection unit is capable of inspecting the inspection range based on the anterior segment image captured by the imaging unit. wherein, when the determination unit determines that the inspection unit is not in a state in which the inspection range can be inspected, the control unit controls the inspection unit to perform inspection of the inspection range again, and the imaging unit a calculator for calculating the displacement between the eye to be inspected and the optical system for inspection based on the image of the anterior segment taken by the controller; and a movement mechanism for moving the optical system for inspection; controls the movement mechanism so that the inspection optical system maintains a predetermined positional relationship with respect to the eye to be inspected according to the displacement calculated by the calculation unit, and the imaging unit controls two or more different directions; two or more anterior eye cameras that acquire two or more anterior eye images by imaging the anterior eye of the subject eye from and the two or more anterior eye images, and the two or more anterior eye cameras successively capture the plurality of anterior eye images at the same frame rate. When the calculation unit calculates the three-dimensional position of the eye to be inspected, the control unit matches the imaging timings of the two or more anterior eye cameras, and the inspection unit inspects the inspection range. This is achieved by an ophthalmologic apparatus characterized by controlling the imaging units so that imaging timings of the two or more anterior segment cameras are made different when the determination unit determines whether or not there is a possible state.

According to the ophthalmologic apparatus of this configuration, the inspection unit optically inspects the inspection range of the fundus of the subject's eye, thereby outputting a detection signal, and the image forming unit forms a cross-sectional image of the fundus based on the detection signal. The imaging unit captures an image of the anterior segment of the subject's eye to obtain an anterior segment image, and the determining unit determines whether the inspection region is ready for inspection based on the anterior segment image. A case where the inspection unit cannot inspect the inspection range is, for example, a case where the inspection unit does not output a detection signal because the subject blinks or the like. In such a case, the control unit controls the inspection unit to inspect the inspection range again. Therefore, a desired cross-sectional image can be obtained even when the examinee blinks or the like and the examination range of the fundus of the examinee's eye cannot be examined.
Further, according to the ophthalmologic apparatus of this configuration, the inspection unit is in a state in which the inspection range can be inspected using the anterior segment image used for maintaining the predetermined positional relationship of the inspection optical system with respect to the eye to be inspected. can determine whether
Further, according to the ophthalmologic apparatus of this configuration, the three-dimensional position of the eye to be examined is calculated based on the positions of two or more anterior eye cameras and the two or more anterior eye images, and the optical system for examination for the eye is calculated. A movement mechanism can be controlled to maintain a predetermined positional relationship.
Further, according to the ophthalmologic apparatus of this configuration, when the three-dimensional position of the eye to be examined is calculated and the predetermined positional relationship of the examination optical system with respect to the eye to be examined is maintained, the imaging timing of two or more anterior eye cameras is can be matched to accurately calculate the three-dimensional position of the subject's eye. On the other hand, when the inspection unit determines whether or not the inspection range can be inspected, the imaging interval (frame rate) of the imaging unit is shortened by varying the imaging timing of the anterior segment cameras. be able to. When the imaging interval of the imaging unit is shortened, the interval at which the inspection unit determines whether the inspection range can be inspected is shortened, and the accuracy of determination is improved.

The ophthalmologic apparatus of the present invention preferably includes a specifying unit that specifies an image region corresponding to the pupil of the subject's eye based on the anterior segment image captured by the imaging unit, and the determination unit includes the specifying It is characterized by determining whether or not the inspection unit is in a state in which it is possible to inspect the inspection range based on the identification result of the unit.
Since the pupil has a lower luminance than other parts, it is relatively easy to identify the image region corresponding to the pupil. Therefore, according to the ophthalmologic apparatus of this configuration, it is possible to accurately determine whether or not the inspection unit is in a state where the inspection range can be inspected through relatively easy processing.

In the ophthalmologic apparatus of the present invention, preferably, the determination unit determines that the inspection unit is not in a state in which the inspection range can be inspected when the image area is not specified by the specifying unit.
For example, when the inspection unit does not output a detection signal because the subject blinks or the like, the specifying unit does not specify the image region corresponding to the pupil of the subject's eye. According to the ophthalmologic apparatus of this configuration, even in such a case, it is possible to re-execute the examination of the examination range and obtain a desired cross-sectional image.

In the ophthalmologic apparatus of the present invention, preferably, the determination unit determines whether the inspection unit can inspect the inspection range based on the position of the image region specified by the specification unit. It is characterized by
For example, if the subject's line of sight is greatly shifted from the front, the position of the image region corresponding to the pupil identified by the identifying unit will be greatly displaced from the front. According to the ophthalmologic apparatus of this configuration, in such a case, it is possible to re-execute the examination of the examination range and obtain a desired cross-sectional image.

In the ophthalmologic apparatus of the present invention, preferably, when the determination unit determines that the inspection range is not in an inspectable state, the control unit optically inspects the entire inspection range again. It is characterized by controlling the inspection unit.
According to the ophthalmologic apparatus of this configuration, when the inspection range is not in an inspectable state, the entire area of the inspection range is optically inspected again. A cross-sectional image of the fundus can be acquired from the obtained detection signal.

In the ophthalmologic apparatus of the present invention, preferably, when the determination unit determines that the inspection range is not in a state in which inspection is possible, the control unit preferably determines whether the inspection range has not been inspected by the inspection unit. The inspection unit is controlled so as to inspect an inspection range.
According to the ophthalmologic apparatus of this configuration, when the inspection range is not in an inspectable state, only the area not inspected by the inspection unit is re-examined. image can be obtained.

In the ophthalmologic apparatus of the present invention, preferably, the examination unit divides light from a light source into signal light and reference light, scans the fundus of the subject's eye with the signal light, and scans the fundus of the subject's eye with the signal light. It is characterized in that the detection signal is detected according to the interference light obtained by causing the signal light and the reference light to interfere with each other.
According to the ophthalmologic apparatus of this configuration, a cross-sectional image of the object to be measured in a cross section perpendicular to the traveling direction of the light is obtained by detecting the detection signal corresponding to the interference light obtained by superimposing the reflected light and the reference light. can be formed.

According to the present invention, the above object is a method for controlling an ophthalmologic apparatus that optically inspects an eye to be inspected, wherein the ophthalmologic apparatus optically inspects an inspection range of the fundus of the eye to be inspected and outputs a detection signal. an inspection unit for outputting, a calculation unit for calculating a displacement between the eye to be inspected and the inspection optical system based on the anterior segment image captured by the imaging unit, and a movement for moving the inspection optical system and two or more anterior eye cameras for acquiring two or more anterior eye images by imaging the anterior eye of the subject's eye from two or more different directions, wherein the anterior eye of the subject's eye. an image capturing step of capturing an anterior eye segment image by capturing an image of the eye region; and based on the anterior segment image captured by the imaging step, the inspecting unit determines whether or not the inspection range can be inspected. a determination step, a control step of controlling the inspection unit to re-execute the inspection of the inspection range when the determination step determines that the inspection unit is not in a state in which the inspection range can be inspected, the inspection unit and an image forming step of forming a cross-sectional image of the fundus based on the detection signal detected by the control unit, according to the displacement calculated by the calculation unit, the inspection optical system for the eye to be examined controls the movement mechanism so as to maintain a predetermined positional relationship, and the calculator controls the position of the eye to be examined based on the positions of the two or more anterior eye cameras and the two or more anterior eye images A three-dimensional position is calculated, and two or more of the anterior eye cameras continuously capture a plurality of the anterior eye images at the same frame rate, and the control unit is configured such that the calculation unit is the subject's eye. When calculating a three-dimensional position, two or more of the anterior segment cameras are matched in imaging timing, and two or more when the determination unit determines whether the inspection unit is capable of inspecting the inspection range. is achieved by a method for controlling an ophthalmologic apparatus, characterized by controlling the imaging unit so as to change the imaging timing of the anterior segment camera .
According to the control method of the ophthalmologic apparatus of this configuration, even when the subject blinks and the examination range of the fundus of the subject's eye cannot be inspected, a desired cross-sectional image can be obtained. can.

INDUSTRIAL APPLICABILITY According to the present invention, an ophthalmologic apparatus capable of obtaining a desired cross-sectional image even when the examination range of the fundus of the subject's eye cannot be examined due to blinking of the examinee's eyes, and the like. A control method can be provided.

1 is a schematic diagram showing an ophthalmologic apparatus according to a first embodiment; FIG. 2 is a schematic diagram of the OCT unit shown in FIG. 1; FIG. 1 is a functional block diagram showing an ophthalmologic apparatus according to a first embodiment; FIG. It is a figure which shows the ophthalmic apparatus of FIG. 1, A is a front view, B is a right side view. It is a figure which shows the positional relationship between a to-be-tested eye and an anterior segment camera, A is a top view, B is a side view. 4 is a flowchart showing processing executed by the ophthalmologic apparatus according to the first embodiment; FIG. 4 is a schematic diagram showing an example of a screen displayed by an ophthalmologic apparatus; FIG. 4 is a diagram showing an example of a scanning mode of signal light when the fundus is viewed from the direction in which the signal light is incident on the eye to be inspected. FIG. 4 is a diagram showing an example of an arrangement mode of scanning points on each scanning line on the fundus. FIG. 4 is a diagram showing a mode of a tomographic image formed by an image forming unit; FIG. 4 is a diagram showing an example of an anterior segment image acquired by an anterior segment camera; FIG. 4 is a diagram showing an example of an anterior segment image acquired by an anterior segment camera; 4 is a timing chart showing vertical synchronization signals of an anterior eye camera when auto-alignment is executed; 4 is a timing chart showing vertical synchronization signals of an anterior eye camera when performing OCT measurement.

[First embodiment]
A first embodiment of an ophthalmologic apparatus according to the present invention will be described in detail with reference to the drawings. The ophthalmologic apparatus according to the first embodiment is used for optical examination of an eye to be examined, and is an optical coherence tomography that obtains cross-sectional images using optical coherence tomography (OCT).

In this specification, images acquired by OCT may be collectively referred to as OCT images. Also, the measurement operation for forming an OCT image is sometimes called OCT measurement. In addition, it is possible to appropriately incorporate the contents of the literature described in this specification as the contents of the following embodiments.

In the following embodiments, optical coherence tomography using a so-called spectral domain type OCT equipped with a low coherence light source and a spectroscope will be described. It is also possible to apply the present invention to optical coherence tomography using OCT techniques of type and infas type.

The Swept Source OCT scans (wavelength sweeps) the wavelength of the light irradiated to the object to be measured, and generates interference light obtained by overlapping the reflected light of each wavelength with the reference light. In this method, spectral intensity distribution is acquired by sequential detection, and the morphology of the object to be measured is imaged by applying Fourier transform to it. Further, in-face (en-face) OCT refers to irradiating an object to be measured with light having a predetermined beam diameter, and analyzing the component of interference light obtained by superimposing the reflected light and the reference light. This is a method of forming an image of an object to be measured in a cross section perpendicular to the light traveling direction, and is also called a full-field type.

Also, in the following embodiments, an apparatus combining an OCT apparatus and a retinal camera will be described, but the application target of the present invention is not limited to such a multifunction machine. For example, it is also possible to apply the present invention to a multi-function machine composed of other combinations, or to an ophthalmologic apparatus as a single machine (for example, a single fundus camera).

[composition]
As shown in FIG. 1 , the ophthalmologic apparatus 1 includes a fundus camera unit 2 , an OCT unit 100 and an arithmetic control unit 200 . The retinal camera unit 2 has an optical system substantially similar to that of a conventional retinal camera. The OCT unit 100 is provided with an optical system for acquiring an OCT image of the fundus. The arithmetic control unit 200 has a computer that executes various kinds of arithmetic processing, control processing, and the like.

[Fundus camera unit]
The fundus camera unit 2 shown in FIG. 1 is provided with an optical system for obtaining a two-dimensional image (fundus image) representing the surface morphology of the fundus Ef of the eye E to be examined. The fundus image includes an observed image, a photographed image, and the like. The observed image is, for example, a monochrome moving image formed at a predetermined frame rate using near-infrared light. When the optical system is focused on the anterior segment Ea of the subject's eye E, the fundus camera unit 2 can acquire an observation image of the anterior segment Ea.

The captured image may be, for example, a color image obtained by flashing visible light, or a monochrome still image using near-infrared light or visible light as illumination light. The fundus camera unit 2 may be configured to be able to acquire images other than these, such as fluorescein fluorescence images, indocyanine green fluorescence images, autofluorescence images, and the like.

The retinal camera unit 2 is provided with a chin rest and a forehead rest for supporting the subject's face. The chin rest and forehead rest correspond to the support 440 shown in FIGS. 4A and 4B. In FIGS. 4A and 4B, reference numeral 410 denotes a base in which a driving system such as the optical system driving section 2A and an arithmetic control circuit are stored. Reference numeral 420 denotes a housing provided on the base 410 and housing an optical system. Further, reference numeral 430 denotes a lens accommodating portion that is provided to protrude from the front surface of the housing 420 and that accommodates the objective lens 22 .

The retinal camera unit 2 is provided with an illumination optical system 10 and an imaging optical system 30 . The illumination optical system 10 illuminates the fundus oculi Ef with illumination light. The imaging optical system 30 guides the fundus reflected light of this illumination light to imaging devices (CCD image sensors (sometimes simply called CCDs) 35 and 38). The imaging optical system 30 also guides the signal light from the OCT unit 100 to the fundus oculi Ef and guides the signal light to the OCT unit 100 via the fundus oculi Ef.

The observation light source 11 of the illumination optical system 10 is composed of, for example, a halogen lamp. Light (observation illumination light) output from an observation light source 11 is reflected by a reflecting mirror 12 having a curved reflecting surface, passes through a condenser lens 13, passes through a visible light cut filter 14, and becomes near-infrared light. Become. Further, 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 .

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, and illuminates the fundus oculi Ef. It is also possible to use an LED (Light Emitting Diode) as an observation light source.

The fundus reflected light of the observation illumination light is refracted by the objective lens 22, passes through the dichroic mirror 46, passes through a hole formed in the central region of the perforated mirror 21, passes through the dichroic mirror 55, and reaches the focusing lens. 31 and reflected by mirror 32 . Further, this fundus reflected light passes through the half mirror 39A, is reflected by the dichroic mirror 33, and is imaged on the light receiving surface of the CCD image sensor 35 by the condenser lens .

The CCD image sensor 35 detects the fundus reflected light, for example, at a predetermined frame rate. The display device 3 displays an image (observation image) based on the fundus reflected light detected by the CCD image sensor 35 . When the imaging optical system is focused on the anterior segment, an observation image of the anterior segment of the subject's eye E is displayed.

The imaging light source 15 is composed of, for example, a xenon lamp. 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 fundus-reflected light of the photographing illumination light is guided to the dichroic mirror 33 through the same path as that of the observation illumination light, passes through the dichroic mirror 33, is reflected by the mirror 36, and is reflected by the condenser lens 37 onto the CCD image sensor 38. An image is formed on the light receiving surface.

An image (captured image) based on the fundus reflected light detected by the CCD image sensor 38 is displayed on the display device 3 . The display device 3 that displays the observed image and the display device 3 that displays the captured image may be the same or different. In addition, when the subject's eye E is illuminated with infrared light and similar photographing is performed, an infrared photographed image is displayed. Moreover, it is also possible to use an LED as a light source for photographing.

An LCD (Liquid Crystal Display) 39 displays a fixation target and visual acuity measurement indices. The fixation target is an index for fixing the eye E to be examined, and is used during fundus photography, OCT measurement, and the like. A part of the light output from the LCD 39 is reflected by the half mirror 39A, reflected by the mirror 32, passes through the focusing lens 31 and the dichroic mirror 55, passes through the aperture of the apertured mirror 21, and is dichroic. It is transmitted through the mirror 46, refracted by the objective lens 22, and projected onto the fundus oculi Ef.

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. The fixation position of the subject's eye E may be, for example, a position for acquiring an image centered on the macula of the fundus oculi Ef or a position for acquiring an image centered on the optic papilla, similar to a conventional fundus camera. and a position for acquiring an image centered on the center of the fundus between the macula and the optic disc. It is also possible to arbitrarily change the display position of the fixation target.

Further, the retinal camera unit 2 is provided with an alignment optical system 50 and a focus optical system 60, like a conventional retinal camera. The alignment optical system 50 generates an index (alignment index) for aligning the apparatus optical system (inspection optical system) with the eye E to be examined. The focus optical system 60 generates an index (split index) for focusing on the fundus oculi Ef.

Light (alignment light) output from the LED 51 of the alignment optical system 50 passes through the apertures 52 and 53 and the relay lens 54, is reflected by the dichroic mirror 55, passes through the aperture of the apertured mirror 21, and reaches the dichroic mirror 46. and projected onto the cornea of the eye E to be examined by the objective lens 22 .

The cornea-reflected light of the alignment light passes through the objective lens 22, the dichroic mirror 46, and the hole, part of which passes through the dichroic mirror 55, passes through the focusing lens 31, is reflected by the mirror 32, and is reflected by the half mirror. 39 A, reflected by the dichroic mirror 33 , and projected onto the light receiving surface of the CCD image sensor 35 by the condenser lens 34 .

A received image (alignment index) by the CCD image sensor 35 is displayed on the display device 3 together with the observed image. The user carries out alignment by performing operations similar to those of a conventional fundus camera. Alternatively, the arithmetic and control unit 200 may analyze the position of the alignment index and move the optical system to perform alignment (auto-alignment function).

Note that, in this embodiment, automatic alignment can be performed using an anterior eye camera 300, which will be described later, so it is not essential to be able to perform automatic alignment using an alignment index. However, when the auto alignment using the anterior eye camera 300 is unsuccessful, the auto alignment using the alignment index may be performed, or the auto alignment using the anterior eye camera 300 and the alignment index may be used. It is also possible to configure such that automatic alignment can be used selectively.

When performing focus adjustment, the reflecting surface of the reflecting bar 67 is obliquely provided on the optical path of the illumination optical system 10 . Light (focus light) output from the LED 61 of the focus optical system 60 passes through the relay lens 62, is split into two light beams by the split index plate 63, passes through the two-hole diaphragm 64, is reflected by the mirror 65, An image is once formed on the reflecting surface of the reflecting bar 67 by the condenser lens 66 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 passes through the same path as the corneal reflected light of the alignment light and is detected by the CCD image sensor 35 . A received image (split index) by the CCD image sensor 35 is displayed on the display device 3 together with the observed image. The arithmetic control unit 200 analyzes the position of the split index and moves the focusing lens 31 and the focusing optical system 60 to perform focusing (autofocus function), as in the conventional art. Alternatively, focusing may be performed manually while visually recognizing the split indicator.

The dichroic mirror 46 branches the optical path for OCT measurement from the optical path for fundus imaging. The dichroic mirror 46 reflects light in the wavelength band used for OCT measurement and transmits light for fundus imaging. The optical path for OCT measurement is provided with a collimator lens unit 40, an optical path length changing section 41, a galvanometer scanner 42, a focusing lens 43, a mirror 44, and a relay lens 45 in this order from the OCT unit 100 side. It is

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

The galvanometer scanner 42 changes the traveling direction of light (signal light LS) passing through the optical path for OCT measurement. Thereby, the fundus oculi Ef can be scanned with the signal light LS. The galvanometer scanner 42 includes, for example, a galvanometer mirror for scanning the signal light LS in the x direction, a galvanometer mirror for scanning in the y direction, and a mechanism for independently driving these. Thereby, the signal light LS can be scanned in any direction on the xy plane.

The anterior segment camera 300 captures images of the anterior segment Ea from different directions substantially simultaneously. In this embodiment, two cameras are provided on the subject-side surface of the retinal camera unit 2 (see anterior eye cameras 300A and 300B shown in FIG. 4A). Also, the anterior eye cameras 300A and 300B are provided at positions outside the optical path of the illumination optical system 10 and the optical path of the imaging optical system 30, respectively, as shown in FIGS. 1 and 4A. That is, the anterior eye cameras 300A and 300B are provided non-coaxially with the illumination optical system 10 and the photographing optical system 30 . Hereinafter, the two anterior eye cameras 300A and 300B may be collectively denoted by reference numeral 300. FIG.

In this embodiment, two anterior eye cameras 300A and 300B are provided, but the number of anterior eye cameras according to the embodiment may be any number of two or more (however, an alignment index is used In some cases, there is no need to provide an anterior eye camera). However, considering the arithmetic processing to be described later, it is sufficient that the anterior segment can be photographed substantially simultaneously from two different directions.

Also, in this embodiment, the anterior segment camera 300 is provided separately from the illumination optical system 10 and the imaging optical system 30, but at least the imaging optical system 30 can be used to perform similar anterior segment imaging. . That is, one of the two or more anterior segment cameras may be handled by a configuration including the imaging optical system 30 . In any case, this embodiment only needs to be configured so that the anterior segment can be imaged substantially simultaneously from two (or more) different directions.

It should be noted that "substantially simultaneously" means that, in photographing with two or more anterior eye cameras, a deviation in photographing timing to the extent that eye movement can be ignored is allowed. Thereby, two or more anterior eye cameras can acquire images when the subject's eye E is in substantially the same position (orientation).

In addition, photographing by two or more anterior segment cameras may be either moving image photographing or still image photographing, but in this embodiment, the case of photographing a moving image will be described in detail. In the case of moving image shooting, by controlling the shooting start timing to match, or by controlling the frame rate and the shooting timing of each frame, the above-described substantially simultaneous anterior segment shooting can be realized. Alternatively, signals substantially simultaneously input from two or more anterior eye cameras to the control unit 210 (described later) may be associated with each other. On the other hand, in the case of still image shooting, this can be achieved by controlling the shooting timing to match.

[OCT unit]
An example of the configuration of the OCT unit 100 will be described with reference to FIG. The OCT unit 100 is provided with an optical system for acquiring an OCT image of the fundus oculi Ef. This optical system has a configuration similar to that of a conventional spectral domain type OCT apparatus. That is, this optical system divides light (low coherence light) from a light source into reference light and signal light, and generates interference light by causing interference between the signal light passing through the fundus oculi Ef and the reference light passing through the reference light path. and is configured to detect the spectral components of this interfering light. This detection result (detection signal) is sent to the arithmetic control unit 200 .

In the case of a swept source type OCT apparatus, a wavelength swept light source is provided instead of a light source that outputs a low coherence light source, and an optical member for spectrally resolving interference light is not provided. In general, for the configuration of the OCT unit 100, any known technique can be applied according to the type of OCT.

The light source unit 101 outputs broadband low-coherence light L0. The low-coherence light L0 includes, for example, a near-infrared wavelength band (approximately 800 nm to 900 nm) and has a temporal coherence length of approximately several tens of micrometers. Note that near-infrared light having a wavelength band invisible to the human eye, for example, a center wavelength of about 1040 to 1060 nm may be used as the low coherence light L0.

The light source unit 101 includes a light output device such as a Super Luminescent Diode (SLD), an LED, or an SOA (Semiconductor Optical Amplifier). A low-coherence light L0 output from the light source unit 101 is guided to the fiber coupler 103 by the optical fiber 102 and split into the signal light LS and the reference light LR.

The reference light LR is guided by an optical fiber 104 and reaches an optical attenuator 105 . The optical attenuator 105 automatically adjusts the light amount of the reference light LR guided to the optical fiber 104 under the control of the arithmetic control unit 200 using a known technique. The reference light LR whose light amount has been adjusted by the optical attenuator 105 is guided by the optical fiber 104 and reaches the polarization adjuster (polarization controller) 106 .

The polarization adjuster 106 is, for example, a device that adjusts the polarization state of the reference light LR guided through the optical fiber 104 by applying external stress to the looped optical fiber 104 . Note that the configuration of the polarization adjuster 106 is not limited to this, and any known technique can be used. The reference light LR whose polarization state has been adjusted by the polarization adjuster 106 reaches the fiber coupler 109 .

The signal light LS generated by the fiber coupler 103 is guided by the optical fiber 107 and made into a parallel light beam by the collimator lens unit 40 . Furthermore, the signal light LS reaches the dichroic mirror 46 via the optical path length changing section 41 , the galvanometer scanner 42 , the focusing lens 43 , the mirror 44 and the relay lens 45 .

Then, the signal light LS is reflected by the dichroic mirror 46, refracted by the objective lens 22, and irradiated to the fundus oculi Ef. The signal light LS is scattered (including reflected) at various depth positions of the fundus oculi Ef. Backscattered light of the signal light LS by the fundus oculi Ef travels in the opposite direction along the same path as the forward path, is guided to the fiber coupler 103 , and reaches the fiber coupler 109 via the optical fiber 108 .

The fiber coupler 109 causes interference between the backscattered light of the signal light LS and the reference light LR that has passed through the optical fiber 104 . The interference light LC thus generated is guided by the optical fiber 110 and emitted from the emission end 111 . Further, the interference light LC is collimated by a collimator lens 112 , dispersed (spectrally resolved) by a diffraction grating 113 , condensed by a condensing lens 114 and projected onto a light receiving surface of a CCD image sensor 115 . Although the diffraction grating 113 shown in FIG. 2 is of a transmissive type, it is also possible to use other types of spectral elements such as a reflective diffraction grating.

The CCD image sensor 115 is, for example, a line sensor, detects each spectral component of the scattered interference light LC, and converts it into an electric charge. The CCD image sensor 115 accumulates this charge to generate a detection signal and sends it to the arithmetic control unit 200 .

Although this embodiment employs a Michelson-type interferometer, any type of interferometer, such as a Mach-Zehnder interferometer, may be employed as appropriate. Also, instead of the CCD image sensor, it is possible to use another type of image sensor, such as a CMOS (Complementary Metal Oxide Semiconductor) image sensor.

[Calculation control unit]
A configuration of the arithmetic control unit 200 will be described. The arithmetic control unit 200 analyzes the detection signal input from the CCD image sensor 115 and forms an OCT image of the fundus oculi Ef. Arithmetic processing therefor is similar to that of the conventional spectral domain type OCT apparatus. The arithmetic control unit 200 controls each part of the retinal camera unit 2 , the display device 3 and the OCT unit 100 . For example, the arithmetic control unit 200 causes the display device 3 to display an OCT image of the fundus oculi Ef.

In addition, as the control of the retinal camera unit 2, the arithmetic control unit 200 controls the operation of the observation light source 11, the photographing light source 15 and the LEDs 51 and 61, the operation control of the LCD 39, the movement control of the focusing lenses 31 and 43, and the movement of the reflecting bar 67. Movement control, movement control of the focus optical system 60, movement control of the optical path length changing unit 41, operation control of the galvanometer scanner 42, operation control of the anterior eye camera 300, and the like are performed.

As for the control of the OCT unit 100, the arithmetic control unit 200 controls the operation of the light source unit 101, the optical attenuator 105, the polarization adjuster 106, the CCD image sensor 115, and the like.

Arithmetic control unit 200 includes, for example, a microprocessor, RAM, ROM, hard disk drive, communication interface, etc., like a conventional computer. A computer program for controlling the ophthalmologic apparatus 1 is stored in a storage device such as a hard disk drive. The arithmetic and control unit 200 may include various circuit boards, such as a circuit board for forming OCT images. The arithmetic control unit 200 may also include an operation device (input device) such as a keyboard and mouse, and a display device such as an LCD.

The retinal camera unit 2, the display device 3, the OCT unit 100, and the arithmetic control unit 200 may be configured integrally (that is, in a single housing), or may be configured separately in two or more housings. may be

[Control system]
The configuration of the control system of the ophthalmologic apparatus 1 will be described with reference to FIG.
(control part)
A control system of the ophthalmologic apparatus 1 is configured around a control unit 210 . The control unit 210 includes, for example, the aforementioned microprocessor, RAM, ROM, hard disk drive, communication interface, and the like. The control unit 210 is provided with a main control unit 211 , a storage unit 212 , an optical system position acquisition unit 213 and an information determination unit 214 .

(main controller)
The main control unit 211 performs various operational controls described above. The movement control of the focusing lens 31 controls a focusing driving section (not shown) to move the focusing lens 31 in the optical axis direction. Thereby, the focus position of the photographing optical system 30 is changed. Further, the movement control of the focusing lens 43 controls a focusing driving section (not shown) to move the focusing lens 43 in the optical axis direction. Thereby, the focus position of the signal light LS is changed.

The main control section 211 can control the optical system driving section 2A to three-dimensionally move the optical system provided in the retinal camera unit 2 . This control is executed in auto alignment and tracking. Here, tracking means moving the device optical system in accordance with the eye movement of the eye E to be examined. Tracking is performed, for example, at a later stage than alignment (in some cases, focusing is also performed beforehand). Tracking is a function of maintaining a suitable positional relationship in alignment (and focus) by causing the position of the optical system of the device to follow the movement of the eyeball.

The optical system driving unit 2A of this embodiment moves the optical system mounted on the retinal camera unit 2, and the optical system mounted on the retinal camera unit 2 and the optical system mounted on the OCT unit 100 may be configured to be moved by the optical system driving section 2A. The optical system driving section 2A is an example of a "moving mechanism".

In addition, since the anterior eye camera 300 of this embodiment is provided in the housing of the retinal camera unit 2, the anterior eye camera 300 can be moved by controlling the optical system driving section 2A (shooting movement section). can be done. In addition, a photographing movement unit capable of independently moving two or more anterior eye cameras 300 can be provided.

Specifically, the photographing movement unit may include a drive mechanism (actuator, power transmission mechanism, etc.) provided for each anterior eye camera 300 . In addition, the photographing movement unit is configured to move two or more anterior eye cameras 300 by transmitting power generated by a single actuator through a power transmission mechanism provided for each anterior eye camera 300. may have been

The main control unit 211 also performs processing of writing data to the storage unit 212 and processing of reading data from the storage unit 212 .

(storage unit)
The storage unit 212 stores various data. The data stored in the storage unit 212 includes, for example, image data of an OCT image, image data of a fundus image, eye information to be examined, and the like. The eye information to be examined includes information about the subject such as patient ID and name, and information about the eye to be examined such as left/right eye identification information. The storage unit 212 also stores various programs and data for operating the ophthalmologic apparatus 1 .

(Optical system position acquisition unit)
The optical system position acquisition unit 213 acquires the current position of the examination optical system mounted on the ophthalmologic apparatus 1 . The inspection optical system is an optical system used for optically inspecting the eye E to be inspected. The examination optical system in the ophthalmologic apparatus 1 (a multifunction device of a fundus camera and an OCT apparatus) of this embodiment is an optical system for obtaining an image of an eye to be examined.

The optical system position acquisition unit 213 receives, for example, information indicating the content of movement control of the optical system drive unit 2A by the main control unit 211, and acquires the current position of the inspection optical system moved by the optical system drive unit 2A. do. A specific example of this processing will be described. The main control unit 211 controls the optical system driving unit 2A at predetermined timing (when the device is started, when patient information is input, etc.) to move the examination optical system to a predetermined initial position. After that, the main control section 211 records the control contents every time the optical system driving section 2A is controlled. As a result, a history of control contents is obtained. The optical system position acquisition unit 213 acquires the contents of control up to the present by referring to this history, and obtains the current position of the optical system for inspection based on the contents of control.

Further, each time the main control unit 211 controls the optical system driving unit 2A, it transmits the control details to the optical system position acquisition unit 213, and each time the optical system position acquisition unit 213 receives the control details, the optical system for inspection is changed. The current position may be obtained sequentially. As another configuration example, the optical system position acquisition unit 213 may be provided with a position sensor for detecting the position of the inspection optical system.

When the current position of the inspection optical system is acquired by the optical system position acquisition unit 213 as described above, the main control unit 211 controls the acquired current position and the subject eye E obtained by the analysis unit 231, which will be described later. The inspection optical system can be moved by the optical system drive unit 2A based on the three-dimensional position of . Specifically, the main control unit 211 recognizes the current position of the optical system for inspection from the acquisition result of the optical system position acquisition unit 213 , and recognizes the three-dimensional position of the subject's eye E from the analysis result of the analysis unit 231 .

Then, the main control unit 211 changes the position of the inspection optical system with the current position as a starting point so that the position of the inspection optical system with respect to the three-dimensional position of the eye E to be examined has a predetermined positional relationship. The predetermined positional relationship is such that the positions in the x-direction and the y-direction are the same, and the distance in the z-direction is the predetermined working distance. Here, the working distance is a default value that is also called a working distance, and means the distance between the subject's eye E and the inspection optical system during inspection using the inspection optical system.

(Information judgment unit)
The information determination unit 214 determines whether the information obtained by performing OCT is appropriate for performing OCT. Information acquired by OCT includes detection signals from the CCD image sensor 115 of the OCT unit 100 and information obtained by subjecting these detection signals to predetermined processing.

Examples of the latter include the following information: cross-sectional images (A-scan images, two-dimensional cross-sectional images) formed by the image forming unit 220 based on detection signals; information obtained during this cross-sectional image forming process; information (such as an image) formed by the image processing unit 230 based on one or more cross-sectional images formed by the image forming unit 220; information obtained by performing other processing on the detection signal.

(Image forming section)
The image forming unit 220 forms image data of a cross-sectional image of the fundus oculi Ef based on the detection signal from the CCD image sensor 115 . This processing includes processing such as noise removal (noise reduction), filtering, and FFT (Fast Fourier Transform), as in conventional spectral domain type OCT. When another type of OCT is applied, the image forming section 220 performs known processing according to that type. The image forming unit 220 is configured including, for example, the aforementioned circuit board. In this specification, "image data" and "images" based thereon may be regarded as the same.

(Image processing part)
The image processing section 230 performs various types of image processing and analysis processing on the image formed by the image forming section 220 . For example, the image processing unit 230 executes various correction processes such as brightness correction and dispersion correction of an image. In addition, the image processing section 230 performs various image processing and analysis processing on images (eye fundus image, anterior segment image, etc.) obtained by the retinal camera unit 2 .

The image processing unit 230 executes known image processing such as interpolation processing for interpolating pixels between cross-sectional images to form three-dimensional image data of the fundus oculi Ef. Note that three-dimensional image data means image data in which pixel positions are defined by a three-dimensional coordinate system. Three-dimensional image data 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 image 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 line-of-sight direction. Image data of a pseudo three-dimensional image is formed. The display unit 241 displays this pseudo three-dimensional image.

Furthermore, the image processing unit 230 is provided with an analysis unit 231 , an image determination unit 232 , and an image synthesis unit 233 .

(analysis part)
The analysis unit 231 obtains the three-dimensional position of the subject's eye E by analyzing two or more captured images substantially simultaneously obtained by two or more anterior eye cameras 300 . As an example of a configuration for executing this processing, the analysis unit 231 is provided with an image correction unit 2311 , a feature position identification unit 2312 , and a three-dimensional position calculation unit 2313 .

(Image corrector)
The image correction unit 2311 corrects the distortion of each captured image obtained by the anterior eye camera 300 based on the aberration information stored in the storage unit 212 . This processing is performed, for example, by a known image processing technique based on correction coefficients for correcting distortion. Note that the aberration information and image correction unit 2311 may not be provided when the distortion aberration that the optical system of the anterior eye camera 300 gives to the captured image is sufficiently small.

(Characteristic position specifying unit)
The characteristic position specifying unit 2312 analyzes each captured image (the distortion aberration of which is corrected by the image correcting unit 2311) to identify a position (characteristic position ) are identified. For example, the pupil center or the corneal vertex of the subject's eye E is used as the predetermined characteristic site. A specific example of processing for identifying the center of the pupil will be described below.

First, the characteristic position specifying unit 2312 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 position identifying section 2312 identifies the central position of the identified pupillary 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 (an approximated circle or approximated ellipse), and set this as the center of the pupil. Alternatively, the center of gravity of the pupil region may be obtained and the position of the center of gravity may be used as the center of the pupil. It should be noted that even when specifying a characteristic position corresponding to another characteristic part, it is possible to specify the characteristic position based on the distribution of pixel values of the captured image in the same manner as described above.

(Three-dimensional position calculator)
The three-dimensional position calculation unit 2313 calculates the characteristic regions of the subject's eye E based on the positions of the two or more anterior eye cameras 300 and the characteristic positions in the two or more captured images identified by the characteristic position identification unit 2312. Calculate the three-dimensional position. This process will be described with reference to FIGS. 5A and 5B.

FIG. 5A is a top view showing the positional relationship between the subject's eye E and the anterior eye cameras 300A and 300B. FIG. 5B is a side view showing the positional relationship between the subject's eye E and the anterior eye cameras 300A and 300B. The distance (baseline length) between the two anterior cameras 300A and 300B is denoted by "B". The distance (shooting distance) between the base line of the two anterior eye cameras 300A and 300B and the characteristic site P of the eye E to be examined is represented by "H". The distance (screen distance) between each anterior camera 300A and 300B and its screen plane is denoted by "f".

In such an arrangement state, the resolution of images captured by the anterior eye cameras 300A and 300B is expressed by the following equation. Here, Δp represents pixel resolution.
Resolution in the xy direction (planar resolution): Δxy = H Δp/f
Resolution in the z direction (depth resolution): Δz = H H Δp/(B x f)

5A and 5B for the positions of the two anterior eye cameras 300A and 300B (which are known) and the feature positions corresponding to the feature sites P in the two captured images. The three-dimensional position of the characteristic region P, that is, the three-dimensional position of the subject's eye E is calculated by applying known trigonometry in consideration of the arrangement relationship shown.

The three-dimensional position of the subject's eye E calculated by the three-dimensional position calculator 2313 is sent to the controller 210 . Based on the calculation result of the three-dimensional position, the control unit 210 aligns the optical axis of the optical system for inspection with the axis of the eye to be inspected E, and operates so that the distance of the optical system for inspection from the eye to be inspected E is a predetermined distance. The optical system driving section 2A is controlled so as to achieve the distance.

Further, when the anterior segment camera 300 simultaneously captures moving images of the anterior segment Ea from different directions, for example, the following processing (1) and (2) are performed to perform inspection of the movement of the eye E to be inspected. It is possible to perform optical system tracking.
(1) The analysis unit 231 sequentially analyzes two or more frames obtained substantially simultaneously in moving image shooting by two or more anterior eye cameras 300, thereby sequentially obtaining the three-dimensional position of the subject's eye E. .
(2) The control unit 210 sequentially controls the optical system driving unit 2A based on the three-dimensional position of the eye E to be examined that is sequentially obtained by the analysis unit 231. to follow.

Based on the three-dimensional position of the eye E acquired by the three-dimensional position calculator 2313, the analysis unit 231 can obtain the displacement between the eye E and the inspection optical system. This process is performed using the fact that the positions of the anterior eye camera 300 and the positions of the inspection optical system are known. The position of the inspection optical system is a predetermined position, for example, the position where the front surface of the objective lens 22 (the surface on the side of the subject's eye E) and the optical axis of the inspection optical system intersect. .

(Image judgment unit)
The image determination unit 232 analyzes the captured image obtained by at least one of the two or more anterior segment cameras 300 to determine whether the image of the anterior segment Ea is included in the predetermined region in the captured image. determine whether or not there is

This predetermined area is set in advance within the imaging range of the anterior eye camera 300, and is set as an area including the center of the imaging range, for example. Here, it is possible to change the range of the predetermined region according to the photographing conditions of the anterior eye camera 300 (the position of the anterior eye camera 300, the photographing magnification, etc.). Also, the range of the predetermined area can be determined according to the setting of feature points, which will be described later. In addition, the predetermined region can be set so as to correspond to the position of a support portion 440 (a chin rest, a forehead rest, etc.; see FIGS. 4A and 4B) that supports the subject's face or a position in the vicinity thereof. .

A specific example of processing executed by the image determination unit 232 will be described. First, the image determination unit 232 identifies an image region corresponding to a predetermined feature point of the anterior segment Ea from the captured image. The feature points include the pupil center, pupil contour, iris center, iris contour, corneal vertex, and the like. The specifying process of the image region corresponding to the feature point is similar to the process executed by the feature position specifying unit 2312, for example. It should be noted that when the feature point and the feature part are the same, the identification result by the characteristic position identification unit 2312 can be used for the processing performed by the image determination unit 232 .

Next, the image determination unit 232 determines whether or not the specified feature point is included in a predetermined area in (the frame of) the captured image. This processing is performed by comparing the coordinates corresponding to the predetermined area with the coordinates of the feature points.

The image determination section 232 sends this determination result to the control section 210 . When it is determined that the image of the anterior segment Ea is not included in the predetermined region, the control section 210 controls the optical system driving section 2A (shooting movement section) to move the anterior segment camera 300 to the support section 440 ( That is, it is moved away from the subject's face) and/or outwardly of the support 440 . The direction away from the support portion 440 is the −z direction in the coordinate system shown in FIG. 1 and the like.

Further, the outward direction of the support portion 440 is the direction in which the anterior segment camera 300 moves away from the optical axis of the inspection optical system. Directions away from the inspection optics can be defined in the horizontal direction (±x directions) and/or in the vertical direction (±y directions). That is, it is possible to define the direction away from the inspection optical system in any direction within the xy plane.

Further, the movement direction and/or movement distance of anterior eye camera 300 can be set based on, for example, the positional relationship between anterior eye camera 300 and support section 440 before movement. Further, by alternately performing the determination processing by the image determination unit 232 and the movement processing of the anterior eye camera 300, it is possible to control the anterior eye camera 300 to a suitable position. .

Alternatively, the moving direction and/or moving distance of the anterior eye camera 300 may be determined according to the distance (the number of pixels) between the image area corresponding to the feature point and the predetermined area. Also, the moving direction and/or the moving distance of the anterior eye camera 300 may be determined according to the distance between the image area corresponding to the feature point and the predetermined position (for example, the central position) within the predetermined area. is also possible.

(Image synthesizer)
The image synthesizing unit 233 forms a synthesized image of two or more photographed images substantially simultaneously obtained by two or more anterior eye cameras 300 . Examples of this composite image include a stereoscopic image based on two or more captured images and an image obtained by viewpoint conversion (viewpoint conversion image). The viewpoint of the viewpoint-converted image is set, for example, on the optical axis of the inspection optical system. These synthesized images are obtained by using a known image synthesizing process.

The image processing unit 230 that functions as described above includes, for example, the aforementioned microprocessor, RAM, ROM, hard disk drive, circuit board, and the like. A storage device such as a hard disk drive pre-stores a computer program that causes a microprocessor to perform the functions described above.

(user interface)
User interface 240 includes display unit 241 and operation unit 242 . The display unit 241 includes the display device of the arithmetic control unit 200 and the display device 3 described above. The operation section 242 includes the operation device of the arithmetic control unit 200 described above. The operation unit 242 may include various buttons and keys provided on the housing or outside of the ophthalmologic apparatus 1 .

For example, if the retinal camera unit 2 has a housing similar to that of a conventional retinal camera, the operation section 242 may include a joystick, an operation panel, etc. provided in this housing. The display section 241 may also include various display devices such as a touch panel provided in the housing of the retinal camera unit 2 .

[motion]
The operation of the ophthalmologic apparatus 1 will be described. In this operation example, an overall flow of a series of operations including auto-alignment will be described. The flowchart shown in FIG. 6 will be referred to below.

(S1: Display of shooting screen)
The control unit 210 causes the display unit 241 to display the shooting screen 1000 shown in FIG. 7A. In a display area (first display area) 1001 on the left side of the imaging screen 1000, an infrared observation image (front image of the anterior segment Ea) 2000 acquired by the retinal camera unit 2 is displayed as a moving image in real time. A moving image of the anterior segment image acquired by one of the anterior segment cameras 300A and 300B is displayed in a display region (second display region) 1002 on the right side of the imaging screen 1000 . A “Capture START” button 1003 is provided below the second display area 1002 .

(S2: Auto alignment)
When the “Capture START” button 1003 is operated (clicked), the control unit 210 causes the display unit 241 to display an alignment screen 1010 (see FIG. 7B) for auto-alignment. At least an image used for auto-alignment is displayed on the alignment screen 1010 .

Auto-alignment using two anterior eye images acquired by anterior eye cameras 300A and 300B will be described. In this example, two anterior segment images of the subject's eye E acquired by two anterior segment cameras 300A and 300B are synthesized and displayed. Each of these anterior segment images is acquired in real time, and a composite image thereof is displayed as a moving image in real time. That is, this composite display is a moving image display in which one frame is a composite image (still image) based on two anterior eye images (still images) obtained substantially simultaneously by the anterior eye cameras 300A and 300B.

A method for creating each frame (each synthesized image) will be described. A frame is based on two anterior images acquired substantially simultaneously by anterior cameras 300A and 300B, as described above. As a first example of the frame creation method, a partial image of one anterior segment image and a partial image of the other anterior segment image can be displayed side by side. As these partial images, different parts are used in each frame. Each partial image is obtained by trimming a part of the original anterior segment image. This processing is executed by the control unit 210 or the image processing unit 230 .

An alignment screen 1010 shown in FIG. 7B is provided with a first display area 1011 and a second display area. A first partial image 2110 corresponding to the upper half of the frame of the anterior segment image acquired by the anterior segment camera 300A is displayed in the first display area 1011 . A second partial image 2120 corresponding to the lower half of the frame of the anterior segment image acquired by the anterior segment camera 300B is displayed in the second display area 1012 .

The first display area 1011 and the second display area 1012 are arranged such that the former is positioned above and the latter is positioned below. Here, the lower end of the first display area 1011 and the upper end of the second display area 1012 are in contact with each other. Thus, in this example, two partial images are displayed in an arrangement according to their positional relationship.

When the retinal camera unit 2 is moved in the ±z direction by the optical system driving unit 2A, the positions of the anterior eye cameras 300A and 300B with respect to the eye to be examined E are changed, and the two partial images 2110 and 2120 are shifted relative to each other. Displace laterally. In addition, when the retinal camera unit 2 is moved in the xy direction by the optical system driving section 2A, the two partial images 2110 and 2120 are integrated as the positions of the anterior eye cameras 300A and 300B with respect to the subject's eye E change. Then, they are displaced in the first display area 1011 and the second display area 1012 in the direction corresponding to the moving direction of the apparatus optical system.

As described above, the analysis unit 231 analyzes the first partial image 2110 (or its entire original image) to determine the image region (first characteristic region) corresponding to the characteristic region of the eye E to be examined. Identify. Similarly, the analysis unit 231 identifies an image region (second characteristic region) corresponding to the characteristic region of the subject's eye E by analyzing the second partial image 2120 (or its entire original image). . Each feature region is, for example, a pupil (pupil contour, pupil center, etc.). In FIG. 7B, reference numeral 2110a denotes a first characteristic region corresponding to the pupil contour, and reference numeral 2120a denotes a second characteristic region corresponding to the pupil contour.

Furthermore, the analysis unit 231 calculates the displacement between the first characteristic region 2110a and the second characteristic region 2120a. This displacement includes displacement in the lateral direction. As described above, the displacement in the lateral direction corresponds to the displacement of the inspection optical system in the ±z directions. The analysis unit 231 obtains the movement direction and movement distance of the inspection optical system, which corresponds to the displacement between the first characteristic region 2110a and the second characteristic region 2120a calculated by the analysis unit 231 .

This processing is executed, for example, with reference to information in which displacements between feature regions are associated with moving directions and moving distances. This information is created in advance and stored in the storage unit 212 or the analysis unit 231 based on the positions where the two anterior eye cameras 300A and 300B are installed, the working distance, and the like.

The control unit 210 moves the retinal camera unit 2 in the +z direction or the −z direction by controlling the optical system driving unit 2A based on the movement distance and the movement direction obtained by the analysis unit 231 . By executing such processing, the first characteristic region 2110a and the second characteristic region 2120a are matched (that is, the first characteristic region 2110a and the second characteristic region 2120a are combined to form the pupil. A z-alignment is performed (see FIG. 7C) such that an image is formed showing .

A bracket 2101 and a circle 2102 surrounded by the bracket 2101 presented substantially in the center of the alignment screen 1010 shown in FIG. 7C indicate target positions in alignment. Bracket 2101 is the target location for the pupil contour and circle 2102 is the target location for the center of the pupil.

Also, the analysis unit 231 calculates the displacement between each position of the first characteristic region 2110a and the second characteristic region 2120a and the target position (bracket 2101, circle 2102). Furthermore, the analysis unit 231 obtains the movement direction and movement distance of the inspection optical system corresponding to the displacement calculated by the analysis unit 231 . This processing is executed, for example, with reference to information that associates the displacement between the feature region and the target position with the movement direction and movement distance. This information is created in advance and stored in the storage unit 212 or the analysis unit 231 based on the positions where the two anterior eye cameras 300A and 300B are installed, the working distance, and the like.

The control unit 210 controls the optical system driving unit 2A based on the movement distance and movement direction obtained by the analysis unit 231, thereby moving the retinal camera unit in the +x direction or −x direction and/or +y direction or −y direction. move 2. Alignment in the xy direction is performed by performing such processing. By achieving both an alignment state in the xy direction and an alignment state in the z direction, the inspection optical system is arranged at a three-dimensionally suitable position with respect to the eye E to be inspected. At this time, the alignment screen 1010 is displayed as shown in FIG. 7C.

A “Capture STOP” button 1013 shown in FIGS. 7B and 7C is operated (clicked) to stop (or interrupt) the processing of this operation example.

(S3: Autofocus)
Upon completion of auto-alignment, control unit 210 performs auto-focusing using the split index in the manner described above.

(S4: Auto Pola)
Upon completion of autofocus, control unit 210 executes automatic polarization adjustment (auto Pola). Auto-Pola is performed, for example, by controlling the polarization adjuster 106 while determining the image quality of repetitively acquired OCT images (cross-sectional images) in real time.

(S5: OCT autofocus)
After auto Polar is completed, control unit 210 executes OCT autofocus. In the OCT autofocus, the optical path length of the signal light is adjusted by controlling the optical path length changing unit 41 so that the interference sensitivity of the signal corresponding to a predetermined portion of the fundus oculi Ef (for example, any layer of the retina or the choroid) is optimized. This is the process of changing the

(S6: Instruction to start measurement)
When the OCT autofocus is completed, the control unit 210 causes the display unit 241 to display information (not shown) to that effect. The user uses the operation unit 242 to perform a trigger operation for starting measurement of the fundus oculi Ef. It is also possible to apply a configuration that uses the completion of OCT autofocus as a trigger for starting measurement. In that case, step S6 is unnecessary.

(S7: Start OCT measurement)
When the image region corresponding to the pupil is identified, the control section 210 causes the OCT unit 100 to start OCT measurement of the fundus oculi Ef. The OCT unit 100 changes the traveling direction of the signal light LS passing through the optical path for OCT measurement, and controls the galvanometer scanner 42 to scan the fundus oculi Ef with the signal light LS.

FIG. 8 shows an example of scanning mode of the signal light LS for forming an image of the fundus oculi Ef. FIG. 8 shows an example of a scanning mode of the signal light LS when the fundus oculi Ef is viewed from the direction in which the signal light LS is incident on the subject's eye E (that is, viewed from the −z direction to the +z direction in FIG. 1). Also, FIG. 9 shows an example of an arrangement mode of scanning points on each scanning line on the fundus oculi Ef.

As shown in FIG. 8, the signal light LS is scanned within a predetermined rectangular scanning region R. As shown in FIG. In this scanning region R, a plurality (m lines) of scanning lines R1 to Rm are set in the x direction. A detection signal of the interference light LC is generated when the signal light LS is scanned along each scanning line Ri (i=1 to m).

Here, the direction of each scanning line Ri is called "main scanning direction", and the direction orthogonal thereto is called "sub-scanning direction". Therefore, the scanning of the signal light LS in the main scanning direction is performed by changing the orientation of the reflecting surface of the galvanomirror that scans in the y direction, and the scanning in the subscanning direction is performed by changing the orientation of the galvanomirror that scans in the x direction. It is done by changing the orientation of the reflective surface.

As shown in FIG. 9, a plurality of (n) scanning points Ri1 to Rin are set in advance on each scanning line Ri. In order to perform the scanning shown in FIG. 8, the control unit 210 first controls the galvanometer scanner 42 so that the incident target of the signal light LS on the fundus oculi Ef is the scanning start position RS (scanning point) on the first scanning line R1. R11). Subsequently, the control unit 210 controls the low-coherence light source 160 to flash the low-coherence light L0 and cause the signal light LS to enter the scanning start position RS. The CCD image sensor 115 receives interference light LC based on the fundus reflected light at the scanning start position RS of the signal light LS, and outputs a detection signal to the control unit 210 .

Next, the control unit 210 controls the galvanometer scanner 42 to scan the signal light LS in the main scanning direction, set the incident target to the scanning point R12, and flash the low coherence light L0 to the scanning point. The signal light LS is made incident on R12. The CCD image sensor 115 receives interference light LC based on the fundus reflected light of the signal light LS at the scanning point R12 and outputs a detection signal to the control unit 210 .

Similarly, the controller 210 sequentially moves the incident target of the signal light LS to the scanning points R13, R14, . By emitting light, a detection signal output from the CCD image sensor 115 corresponding to the interference light LC of each scanning point is acquired.

After completing the measurement at the last scanning point R1n of the first scanning line R1, the control unit 210 controls the galvanometer scanner 42 to move the incident target of the signal light LS to the second scanning along the line switching scanning r. Move to the first scanning point R21 on the line R2. By performing the above-described measurement for each scanning point R2j (j=1 to n) of the second scanning line R2, a detection signal corresponding to each scanning point R2j is obtained.

Similarly, measurement is performed for each of the third scanning line R3, . to get The symbol RE on the scanning line Rm is the scanning end position corresponding to the scanning point Rmn. Thereby, the control unit 210 acquires m×n detection signals corresponding to m×n scanning points Rij (i=1 to m, j=1 to n) in the scanning region R. Hereinafter, the detection signal corresponding to the scanning point Rij may be denoted as Dij.

The interlocking control of the movement of the scanning point and the output of the low-coherence light L0 as described above is performed, for example, by adjusting the transmission timing of the control signal to the galvanometer scanner 42 and the transmission timing of the control signal (output request signal) to the light source unit 101. It can be realized by synchronizing them with each other.

When operating the galvanomirror as described above, the control unit 210 stores the position of each scanning line Ri and the position of each scanning point Rij (coordinates in the xy coordinate system) as information indicating the details of the operation. It has become. This stored content (scanning position information) is used in image forming processing as in the conventional art.

(S8: Acquisition of anterior segment image)
When an instruction to start measurement is given, the control unit 210 controls the anterior eye camera 300 to image the anterior eye Ea of the subject's eye E and acquire an anterior eye image. In the auto-alignment of step S2, anterior eye camera 300 acquires anterior eye images from both anterior eye cameras 300A and 300B. In step S7, an anterior segment image may be obtained from at least one of the anterior segment cameras 300A and 300B.

(S9: Identify image area corresponding to pupil?)
When acquisition of the anterior segment image is completed, the control unit 210 controls the image determination unit 232 of the image processing unit 230 to specify an image region corresponding to the pupil of the anterior segment Ea. The characteristic position specifying unit 2312 of the image determination unit 232 extracts the pupillary contour of the anterior segment Ea from the anterior segment image obtained by the anterior segment camera 300, and defines the region surrounded by the pupillary contour as an image region corresponding to the pupil. Identify.

If the feature position specifying unit 2312 specifies the image area corresponding to the pupil, the control unit 210 proceeds to step S10, and if the feature position specifying unit 2312 cannot specify the image area corresponding to the pupil, step S11 proceed to A case where the characteristic position specifying unit 2312 cannot specify the image region corresponding to the pupil is, for example, a case where the OCT unit (examination unit) 100 does not output a detection signal because the subject blinks. In this case, the image determination unit 232 determines that the OCT unit 100 cannot inspect a scanning region (inspection range) R, which will be described later, based on the identification result of the characteristic position identification unit 2312, and advances the process to step S11. .

(S10: End of scanning of scanning area R?)
When the image region corresponding to the pupil is identified from the anterior segment image, the control unit 210 determines whether the scanning of the scanning region R by the OCT measurement started in step S9 has ended. If the control unit 210 determines that the scanning of the scanning region R has been completed, the process proceeds to step S12, and if it determines that the scanning of the scanning region R has not been completed, the processing proceeds to step S8.

Note that the processing time from when the anterior eye camera 300 picks up the anterior eye image in step S8 to when it is determined whether or not the scanning of the scanning region R is finished in step S10 is the same as that of a plurality of scanning points in the sub-scanning direction. is preferably shorter than the scanning interval of . To reliably determine for each scanning point that no detection signal is output from the OCT unit (examination unit) 100 due to blinking of the subject, etc., by specifying the image area corresponding to the pupil at intervals shorter than the scanning interval. can be done.

(S11: Store scanning points for which OCT measurement is not possible)
If the image region corresponding to the pupil is not specified from the anterior segment image, the control unit 210 stores scanning points that cannot be OCT-measured. The control unit 210 causes the storage unit 212 to store the scanning points Rij (i=1 to m, j=1 to n) to be scanned immediately after the determination of NO in step S9 as scanning points for which OCT cannot be measured.

When the detection signal is not output from the OCT unit (examination unit) 100 for a predetermined period longer than the scanning interval due to blinking of the subject, etc., the control unit 210 performs a process of determining NO in step S9 and stores the scanning points. multiple times. After step S11, the control unit 210 executes the process of step S8 again, and the anterior eye camera 300 acquires an anterior eye image.

(S12: Are there any scanning points that cannot be OCT measured?)
When the scanning of the scanning region R is completed, the control unit 210 determines whether or not there is a scanning point for which OCT measurement is impossible. The control unit 210 determines YES when a scanning point for which OCT measurement is impossible is stored in the storage unit 212 after the OCT measurement is started in step S7. Control unit 210 advances the process to step S8 when determining YES in step S12, and advances the process to step S13 when determining NO in step S10.

If there is an OCT-unmeasurable scanning point, the control unit 210 executes the processes from step S8 to step S11 again, and controls the OCT unit 100 to scan the OCT-unmeasurable scanning point again. That is, when the image determination unit 232 determines that the OCT unit 100 is not in a state in which the scanning region R can be scanned (inspected), the control unit 210 controls the OCT unit 100 to perform the inspection of the scanning region R again. do.

When inspecting the scanning region R again, the control unit 210 inspects the scanning region R by one of the following three methods. Control unit 210 may execute only one of the following three, or may select and execute one of the following three based on a user's instruction.

The first method is to optically inspect the entire scanning region R again. When the image determination unit 232 determines that the scanning region R is not in an inspectable state, the control unit 210 controls the OCT unit 100 to optically inspect the entire scanning region R again. That is, the controller 210 controls the OCT unit 100 to optically inspect all the scanning points within the scanning region R again.

A second method is to optically inspect again all scanning lines including scanning points that have not been inspected by the OCT unit 100 in the scanning region R. FIG. When the image determination unit 232 determines that the scanning region R is not in an inspectable state, the control unit 210 re-optically scans all the scanning lines including the scanning points that have not been inspected by the OCT unit in the scanning region R. The OCT unit 100 is controlled to inspect in a realistic manner. The control unit 210 reads out the OCT-unmeasurable scanning points stored in the storage unit 212, and specifies the scanning line including the read out scanning points. The controller 210 controls the OCT unit 100 to optically inspect all identified scan lines again.

A third method is a method of optically inspecting again those scanning points in the scanning region R that have not been inspected by the OCT unit 100 . When the image determination unit 232 determines that the scanning region R is not in an inspectable state, the control unit 210 optically inspects again the scanning points that have not been inspected by the OCT unit in the scanning region R. It controls the OCT unit 100 . The control unit 210 reads the OCT-impossible scanning points stored in the storage unit 212, and specifies the read scanning points. The controller 210 controls the OCT unit 100 to optically inspect all identified scanning points again.

(S13: Form OCT image)
If it is determined that there is no scanning point that cannot be OCT-measured, the image forming section 220 forms an OCT image based on the detection signal from the OCT unit 100 . The control unit 210 causes the storage unit 212 to store the formed OCT image. When three-dimensional scanning is applied, the image processing section 230 forms three-dimensional image data based on a plurality of cross-sectional images formed by the image forming section 220 . The control unit 210 causes the storage unit 212 to store the formed three-dimensional image data. Control unit 210 terminates the processing of the flowchart shown in FIG. 6 in response to completion of step S13.

The image forming unit 220 forms an image of the fundus oculi Ef in the depth direction (z direction shown in FIG. 1) at the scanning point Rij based on the detection signal Dij corresponding to each scanning point Rij. FIG. 10 shows a mode of a tomographic image formed by the image forming section 220. As shown in FIG. For each scanning line Ri, the image forming unit 220 forms a tomographic image Gi of the fundus oculi Ef along the scanning line Ri based on the images in the depth direction at n scanning points Ri1 to Rin thereon.

At this time, the image forming unit 220 refers to the position information of each scanning point Ri1 to Rin (the above-described scanning position information) to determine the arrangement and spacing of each scanning point Ri1 to Rin, thereby forming this scanning line Ri. It is designed to Through the above processing, m tomographic images G1 to Gm at different positions in the sub-scanning direction (y direction) are obtained.

The image processing unit 230 executes processing for forming a three-dimensional image of the fundus oculi Ef based on a tomographic image of the fundus oculi Ef along each scanning line Ri (main scanning direction). A three-dimensional image of the fundus oculi Ef is formed based on m pieces of tomographic images obtained by the above arithmetic processing. The image processing unit 230 forms a three-dimensional image of the fundus oculi Ef by performing known interpolation processing for interpolating images between adjacent tomographic images Gi and G(i+1).

At this time, the image processing unit 230 refers to the positional information of each scanning line Ri to determine the arrangement and spacing of each scanning line Ri to form this three-dimensional image. In this three-dimensional image, a three-dimensional coordinate system (x, y, z) is set based on the position information of each scanning point Rij (the above-described scanning position information) and the z coordinate in the image in the depth direction. . An image Gmj shown in FIG. 10 represents an image in the depth direction (z direction) at scanning point Rmj on scanning line Rm.

The actions and effects of the ophthalmologic apparatus 1 of the present embodiment described above will be described.
According to the ophthalmologic apparatus 1 of the present embodiment, the OCT unit 100 optically inspects the scanning region (inspection range) R of the fundus oculi Ef of the eye E to be inspected, thereby outputting a detection signal and forming an image based on the detection signal. A section 220 forms a cross-sectional image of the fundus. The anterior eye camera 300 captures the anterior eye Ea of the subject's eye E to acquire an anterior eye image, and the image determination unit 232 allows the OCT unit 100 to inspect the scanning region R based on the anterior eye image. Determine whether or not

A case where the OCT unit 100 cannot inspect the scanning region R is, for example, a case where the OCT unit 100 does not output a detection signal because the subject blinks. In such a case, the control section 210 controls the OCT unit 100 to inspect the scanning region R again. Therefore, a desired cross-sectional image can be obtained even when the subject blinks or the like and the scanning region R of the fundus Ef of the subject's eye E cannot be inspected.

In the ophthalmologic apparatus 1 of the present embodiment, when the image determination unit 232 determines that the scanning region R is not in an inspectable state, the control unit 210 performs OCT so as to optically inspect the entire scanning region R again. Control unit 100;
According to the ophthalmologic apparatus 1 of the present embodiment, since the entire scanning region R is optically inspected again when the scanning region R is not in a state that can be inspected, the user does not need to perform a re-examination operation. A cross-sectional image of the fundus oculi Ef can be acquired from the detection signals obtained by continuous inspection.

In the ophthalmologic apparatus 1 of the present embodiment, when the image determination unit 232 determines that the scanning region R is not in a state that can be inspected, the control unit 210 determines whether the scanning region R has not been inspected by the OCT unit 100 . Control the OCT unit 100 to inspect the inspection range.
According to the ophthalmologic apparatus 1 of this configuration, when the scanning region R is not in a state that can be inspected, only the region that has not been inspected by the OCT unit 100 is re-examined. A cross-sectional image of the fundus oculi Ef can be obtained.

According to the ophthalmologic apparatus 1 of the present embodiment, the OCT unit 100 can inspect the scanning region R using the anterior segment image used for maintaining the predetermined positional relationship of the inspection optical system with respect to the eye E to be inspected. state can be determined.
According to the ophthalmologic apparatus 1 of the present embodiment, the three-dimensional position of the eye to be examined E is calculated based on the positions of the two or more anterior eye cameras 300A and 300B and the two or more anterior eye images. The optical system driving section 2A can be controlled so as to maintain a predetermined positional relationship of the inspection optical system.

[Second embodiment]
Next, an ophthalmologic apparatus according to a second embodiment of the present invention will be described.
The present embodiment is a modified example of the first embodiment, and is assumed to be the same as the first embodiment except for the case where it is specifically described below, and the description below is omitted.

The ophthalmologic apparatus 1 of the first embodiment determines whether the OCT unit 100 is ready to inspect the scanning region R by determining whether the image region corresponding to the pupil can be specified. That is, the ophthalmologic apparatus 1 of the first embodiment determines that the OCT unit 100 cannot inspect the scanning region R when the subject blinks and cannot identify the image region corresponding to the pupil. there were.

In contrast, the ophthalmologic apparatus of this embodiment determines whether the OCT unit 100 is ready to inspect the scanning region R based on the position of the image region corresponding to the pupil. That is, the eye apparatus of the present embodiment determines that the OCT unit 100 cannot inspect the scanning region R when the subject's line of sight is greatly shifted from the front and the image region corresponding to the pupil is shifted from the front. It is.

The processing executed by the ophthalmologic apparatus of this embodiment is the same as that of the first embodiment except for the processing of step S9 shown in FIG. 6 of the first embodiment. Processing executed instead of step S9 shown in FIG. 6 of the first embodiment will be described below.

When acquisition of the anterior segment image is completed, the control unit 210 of the present embodiment controls the image determination unit 232 of the image processing unit 230 to specify an image region corresponding to the pupil. The characteristic position specifying unit 2312 of the image determination unit 232 extracts the pupillary contour of the anterior segment Ea from the anterior segment image obtained by the anterior segment camera 300, and defines the region surrounded by the pupillary contour as an image region corresponding to the pupil. Identify.

If the position of the image region specified by the feature position specifying unit 2312 is included in the inspection range A1 indicating that the scanning region R can be inspected by the OCT unit 100, the control unit 210 proceeds to step S10. If it is not included in the inspectable range A1, the process proceeds to step S11.

A case where the position of the image region specified by the characteristic position specifying unit 2312 is not included in the inspection range A1 is, for example, a case where the subject's line of sight is greatly shifted from the front and the image region corresponding to the pupil is shifted from the front. is. In this case, the image determination unit 232 determines that the OCT unit 100 cannot inspect a scanning region (inspection range) R, which will be described later, based on the position of the image region specified by the characteristic position specifying unit 2312, and step S11. proceed to

Here, the testable range A1 refers to a range in which the signal light LS passing through the optical path for OCT measurement is not blocked by the iris of the subject's eye E when the scanning region R is scanned with the signal light LS. 11 and 12 are diagrams showing an example of an anterior segment image acquired by the anterior segment camera 300B. Reference numeral 2120a indicates an area specified by the image determination unit 232 as an image area corresponding to the pupil contour.

As shown in FIG. 11, the control unit 210 controls the OCT unit 100 to scan when the entire second characteristic region 2120a, which is the image region identified by the characteristic position identification unit 2312, is included in the inspection range A1. It is determined that the region R is ready for inspection, and the process proceeds to step S10. On the other hand, as shown in FIG. 12, when a part of the second feature region 2120a, which is the image region specified by the feature position specifying unit 2312, is not included in the inspection range A1, the control unit 210 100 determines that the scanning region R can be inspected, and proceeds to step S10.

For example, if the subject's line of sight deviates significantly from the front, the positions of the image regions corresponding to the pupils identified by the characteristic position identifying unit 2312 deviate greatly from the front. According to the ophthalmologic apparatus of this embodiment, even if the position of the image area corresponding to the pupil deviates greatly from the front, the scanning area R can be inspected again to obtain a desired cross-sectional image. .

[Third embodiment]
Next, an ophthalmologic apparatus according to a third embodiment of the present invention will be described.
The present embodiment is a modified example of the first and second embodiments, and is assumed to be the same as the first and second embodiments except for cases where it is specifically described below, and the description below is omitted. do.

The present embodiment relates to a process of appropriately adjusting the timing at which the anterior eye cameras 300A and 300B acquire an anterior eye image of the anterior eye Ea of the subject's eye E to acquire an anterior eye image. In the first embodiment, at least one of the anterior eye cameras 300A and 300B acquires an anterior eye image in step S8 of FIG. In this embodiment, both anterior eye cameras 300A and 300B acquire anterior eye images.

The ophthalmologic apparatus of this embodiment performs processing using two anterior segment images of the subject's eye E acquired by the two anterior segment cameras 300A and 300B in the auto alignment of step S2 in FIG. Control unit 210 performs control so that the vertical synchronization signals of anterior eye cameras 300A and 300B are output at the same timing when auto-alignment is performed.

As shown in FIG. 13, control unit 210 outputs vertical synchronization signals for anterior eye cameras 300A and 300B at times T1, T3, T5, T7, T9, and T11. In each of the anterior eye cameras 300A and 300B, the output interval of the vertical synchronization signal is a constant first frame rate Fr1.

The auto-alignment performed in step S2 is to obtain the movement direction and the movement distance of the inspection optical system from two anterior eye images of the subject's eye E acquired by the two anterior eye cameras 300A and 300B. Therefore, the two anterior segment images used for auto-alignment must be acquired at the same timing. Therefore, in the auto-alignment of step S2 in FIG. 6, the control unit 210 controls so that the vertical synchronization signals of the anterior eye cameras 300A and 300B are output at the same timing, and the imaging timing of the anterior eye cameras 300A and 300B is adjusted. are matched.

The ophthalmologic apparatus of the present embodiment performs processing using two anterior segment images of the subject's eye E acquired by the two anterior segment cameras 300A and 300B in the OCT measurement started in step S7 of FIG. ing. After the OCT measurement is started, the control unit 210 controls so that the vertical synchronization signals of the anterior eye cameras 300A and 300B are output at different timings, thereby making the imaging timings of the anterior eye cameras 300A and 300B different. .

As shown in FIG. 14, the control unit 210 outputs vertical synchronization signals for the anterior eye camera 300A at times T1, T3, T5, T7, T9, and T11. Further, the control unit 210 outputs vertical synchronization signals for the anterior eye camera 300B at timings T2, T4, T6, T8, T10, and T12. In each of the anterior eye cameras 300A and 300B, the output interval of the vertical synchronization signal is a constant first frame rate Fr1. Therefore, the anterior eye cameras 300A and 300B continuously capture anterior eye images at the same first frame rate Fr1.

As shown in FIG. 14, the timing of outputting the vertical synchronization signal of the anterior eye camera 300A and the timing of outputting the vertical synchronization signal of the anterior eye camera 300B are shifted by the second frame rate Fr2. Therefore, when the anterior eye camera 300A and the anterior eye camera 300B are viewed as one imaging unit, the frame rate of this imaging unit is the second frame rate Fr2, and the second frame rate Fr2 is half the first frame rate Fr1. interval.

During execution of OCT measurement, the control unit 210 acquires an anterior segment image with the anterior segment camera 300A and an anterior segment camera 300B, and specifies an image region corresponding to the pupil. The shorter the time interval for acquiring the anterior segment image in step S8 (the higher the frame rate), the more reliably the scanning points for which OCT cannot be measured can be stored.

Therefore, after starting the OCT measurement (after step S7), the control unit 210 outputs the timing (imaging timing) for outputting the vertical synchronization signal of the anterior eye camera 300A and the vertical synchronization signal of the anterior eye camera 300B. The timing (imaging timing) is controlled to be shifted by the second frame rate Fr2. As a result, the apparent acquisition interval of the anterior segment image becomes the second frame rate Fr2, which is half the first frame rate Fr1, and the scanning points for which OCT cannot be measured can be reliably stored.

According to the ophthalmologic apparatus of the present embodiment, when performing auto-alignment for calculating the three-dimensional position of the eye to be examined E and maintaining a predetermined positional relationship of the examination optical system with respect to the eye to be examined E, the anterior segment camera The three-dimensional position of the subject's eye E can be accurately calculated by matching the imaging timings of the anterior eye camera 300A and the anterior eye camera 300B.

On the other hand, when determining whether or not the OCT unit 100 is ready to inspect the scanning region R, the imaging timings of the anterior eye camera 300A and the anterior eye camera 300B are made different so that the anterior eye camera 300 imaging interval (frame rate) can be shortened. When the imaging interval of the anterior segment camera 300 is shortened, the interval at which the OCT unit 100 determines whether or not the scanning region R can be inspected is shortened, and the accuracy of determination is improved.

Although two cameras, the anterior eye camera 300A and the anterior eye camera 300B, have been described in the present embodiment, two or more anterior eye cameras may be used. When two or more anterior eye cameras are used, the imaging timings of all the anterior eye cameras are matched when auto-alignment is performed. On the other hand, when determining whether the OCT unit 100 can inspect the scanning region R, the imaging timings of the plurality of anterior eye cameras are made different.

The embodiments of the present invention have been described above. However, the present invention is not limited to the above embodiments, and various modifications can be made without departing from the scope of the claims. Some of the configurations of the above embodiments may be omitted, or may be arbitrarily combined in a manner different from the above.

A computer program for implementing the above embodiments can be stored in any computer-readable recording medium. As this recording medium, for example, a semiconductor memory, an optical disk, a magneto-optical disk (CD-ROM/DVD-RAM/DVD-ROM/MO, etc.), a magnetic storage medium (hard disk, etc.), etc. can be used.

DESCRIPTION OF SYMBOLS 1... Ophthalmic apparatus 2... Fundus camera unit 100... OCT unit 200... Calculation control unit 210... Control part 212... Storage part 220... Image formation Section 230 Image processing section 231 Analysis section 232 Image determination section 233 Image synthesizing section 241 Display section 300, 300A, 300B Anterior eye Partial camera 2312 Feature position specifying unit 2313 Three-dimensional position calculation unit A1 Inspection possible range Ea Anterior segment Ef Fundus LC Interference light , LR...reference light, LS...signal light

Claims (8)

An ophthalmic device for optically examining an eye to be examined,
an inspection unit including an inspection optical system that optically inspects an inspection range of the fundus of the eye to be inspected and outputs a detection signal;
an image forming unit that forms a cross-sectional image of the fundus based on the detection signal detected by the examination unit;
an imaging unit for imaging the anterior segment of the eye to be inspected to obtain an anterior segment image;
a control unit that controls the ophthalmologic apparatus;
a determination unit that determines whether the inspection unit is capable of inspecting the inspection range based on the anterior segment image captured by the imaging unit;
When the determination unit determines that the inspection unit is not in a state in which the inspection range can be inspected, the control unit controls the inspection unit to re-execute the inspection of the inspection range,
a calculation unit that calculates the displacement between the eye to be examined and the inspection optical system based on the anterior segment image captured by the imaging unit;
a moving mechanism for moving the inspection optical system,
The control unit controls the movement mechanism so that the inspection optical system maintains a predetermined positional relationship with respect to the eye to be inspected according to the displacement calculated by the calculation unit,
The imaging unit captures images of the anterior ocular segment of the subject eye from two or more different directions to obtain two or more anterior ocular segments.
having two or more anterior eye cameras that acquire the anterior eye images;
The calculation unit calculates the three-dimensional position of the subject eye based on the positions of the two or more anterior eye cameras and the two or more anterior eye images,
The two or more anterior eye cameras continuously capture a plurality of the anterior eye images at the same frame rate,
When the calculation unit calculates the three-dimensional position of the eye to be inspected, the control unit matches the imaging timings of the two or more anterior eye cameras, and the inspection unit is in a state in which the inspection range can be inspected. The ophthalmologic apparatus characterized in that, when the determining unit determines whether or not, the imaging unit is controlled such that the imaging timings of the two or more anterior eye cameras are differentiated. a specifying unit that specifies an image region corresponding to the pupil of the eye to be inspected based on the anterior segment image captured by the imaging unit;
2. The ophthalmologic apparatus according to claim 1, wherein the determination unit determines whether the inspection unit is capable of inspecting the inspection range based on the identification result of the identification unit. 3. The ophthalmologic apparatus according to claim 2, wherein the determination unit determines that the inspection unit is not capable of inspecting the inspection range when the image region is not specified by the specifying unit. 3. The method according to claim 2, wherein the determining unit determines whether the inspection unit is capable of inspecting the inspection range based on the position of the image area specified by the specifying unit. ophthalmic equipment. When the determination unit determines that the inspection range is not in an inspectable state, the control unit controls the inspection unit to optically inspect the entire inspection range again. An ophthalmic device according to any one of claims 1 to 4. When the determination unit determines that the inspection range is not in an inspectable state, the control unit causes the inspection unit to inspect a re-inspection range that has not been inspected by the inspection unit, out of the inspection range. 5. The ophthalmologic apparatus according to any one of claims 1 to 4, wherein the ophthalmic apparatus controls the . The inspection unit divides light from a light source into signal light and reference light, scans the fundus of the subject's eye with the signal light, and causes the signal light and the reference light that have passed through the fundus to interfere with each other. The ophthalmologic apparatus according to any one of claims 1 to 6, wherein the detection signal is detected according to the interference light. A control method for an ophthalmologic apparatus for optically examining an eye to be examined, comprising:
The ophthalmologic apparatus includes an inspection unit that optically inspects an inspection range of the fundus of the eye to be inspected and outputs a detection signal;
a calculation unit that calculates the displacement between the eye to be examined and the inspection optical system based on the anterior segment image captured by the imaging unit;
a moving mechanism for moving the inspection optical system;
two or more anterior segment cameras that acquire two or more anterior segment images by imaging the anterior segment of the subject's eye from two or more different directions;
an imaging step of imaging the anterior segment of the eye to be inspected to obtain an anterior segment image;
a determination step of determining whether the inspection unit is capable of inspecting the inspection range based on the anterior segment image captured by the imaging step;
a control step of controlling the inspection unit to perform the inspection of the inspection range again when the determination step determines that the inspection unit is not in a state in which the inspection range can be inspected;
an image forming step of forming a cross-sectional image of the fundus based on the detection signal detected by the examination unit;
a control unit controlling the moving mechanism so that the inspection optical system maintains a predetermined positional relationship with respect to the eye to be inspected according to the displacement calculated by the calculation unit;
The calculation unit calculates the three-dimensional position of the subject eye based on the positions of the two or more anterior eye cameras and the two or more anterior eye images,
The two or more anterior eye cameras continuously capture a plurality of the anterior eye images at the same frame rate,
When the calculation unit calculates the three-dimensional position of the eye to be inspected, the control unit matches the imaging timings of the two or more anterior eye cameras, and the inspection unit is in a state in which the inspection range can be inspected. A control method for an ophthalmologic apparatus, characterized in that, when the determination unit determines whether or not, the imaging unit is controlled such that imaging timings of two or more anterior eye cameras are differentiated.

Images