JP7181135B2 - ophthalmic equipment - Google Patents

Description

The present invention relates to an ophthalmic device.

2. Description of the Related Art In ophthalmology, an apparatus for obtaining an image of an eye to be examined (ophthalmic imaging apparatus) and an apparatus for measuring characteristics of an eye to be examined (ophthalmic measurement apparatus) are used.

Examples of ophthalmologic imaging equipment include optical coherence tomography (OCT) for obtaining data, a fundus camera for photographing the fundus, and a laser scanning system for obtaining a fundus image using a confocal optical system. There is a scanning laser ophthalmoscope (SLO) that obtains . Patent Literature 1 discloses an ophthalmologic observation system that acquires a three-dimensional tomographic image of a subject's eye by OCT.

Examples of ophthalmologic measurement devices include an eye refraction tester (refractometer) that measures the refractive properties of the subject's eye, a wavefront analyzer that obtains aberration data of the subject's eye using a Hartmann-Shack sensor, and a corneal vertex and retinal fovea. There is an axial length measuring device that measures the distance (axial length) between the two.

The ophthalmologic apparatus exemplified above projects light toward the fundus of the subject's eye and obtains data based on the returned light. Therefore, when there is turbidity in the intermediate translucent body (lens, vitreous body, etc.), such as in a cataractous eye, the projected light and return light are affected by the turbidity, which may hinder suitable imaging and measurement.

In addition, the light source of an optical coherence tomography that obtains data using OCT emits light in the near-infrared wavelength band, for example. Therefore, the examiner cannot visually see the light (measurement light) projected from the light source toward the eye to be examined through an optical system having mirrors, lenses, etc., and the measurement light passes through the anterior segment of the eye to be examined. It is not possible to confirm the transmission position of transmission. Further, even when using a display unit such as a display, the examiner cannot confirm the transmission position where the measurement light passes through the anterior segment of the eye to be examined. Therefore, even if the examiner can confirm the cloudy region existing in the intermediate translucent body of the eye to be examined, it is difficult for the examiner to avoid the cloudy region and allow the measurement light to pass through the anterior segment of the eye to be examined. . In other words, the examiner can acquire an accurate photographed image of the anterior segment and fundus of the eye to be inspected only after operating the optical coherence tomography to capture images of the anterior segment and fundus of the eye to be inspected and then confirming the captured images. I noticed that it wasn't. Even if the examiner re-operates the optical coherence tomography and re-captures the subject's eye, the examiner cannot confirm the transmission position where the measurement light passes through the anterior segment of the subject's eye, so an accurate captured image cannot be obtained again. may not be possible. Therefore, in an ophthalmologic apparatus that projects measurement light onto an eye to be inspected and optically acquires data of the eye to be inspected, it is desired to shorten the time required for photographing and measuring while ensuring the accuracy and accuracy of photographing and measurement. there is

JP 2012-75640 A

SUMMARY OF THE INVENTION It is an object of the present invention to provide an ophthalmologic apparatus capable of shortening the time required for photographing and measuring while ensuring the accuracy and accuracy of photographing and measurement. do.

The subject is an ophthalmologic apparatus that optically acquires data of an eye to be inspected, in which at least part of light from a light source is projected onto the eye to be inspected as measurement light, and optical coherence tomography is performed on a three-dimensional region of the eye to be inspected. a data acquisition unit having an optical system that collects OCT data by applying a scan; and a data processing unit that specifies a transmission position where the measurement light passes through the anterior segment of the eye to be examined based on the arrangement of the optical system. and a display control unit for superimposing the image representing the transmission position specified by the data processing unit on the image of the eye to be examined and displaying the image on a display unit. be done.

According to the ophthalmologic apparatus of the present invention, the data processing unit identifies the transmission position where the measurement light passes through the anterior segment of the subject's eye based on the arrangement of the optical system that collects OCT data. Then, the display control unit causes the display unit to display the image representing the transmission position specified by the data processing unit so as to be superimposed on the image of the subject's eye. Therefore, the examiner can confirm the transmission position at which the measurement light passes through the anterior segment of the subject's eye by visually recognizing the display means. Therefore, the examiner can set the transmission position where the measurement light passes through the anterior segment of the eye to be examined at an intended position, and the measurement light is made incident inside the eye to be examined through the transmission position to obtain the data of the eye to be examined. can be obtained. As a result, it is possible to shorten the time required for photographing and measuring while ensuring the accuracy and accuracy of photographing and measurement.

In the ophthalmologic apparatus according to the present invention, preferably, the display control unit causes the display unit to display an image representing the transmission position specified by the data processing unit superimposed on the image of the anterior segment. and

According to the ophthalmologic apparatus according to the present invention, the examiner visually recognizes the image of the anterior segment of the subject's eye displayed on the display means by visually recognizing the measurement light passing through the anterior segment. can be confirmed. Therefore, the transmission position at which the measurement light passes through the anterior segment of the eye to be inspected can be set more reliably than the intended position, and the measurement light is made incident inside the eye to be inspected through the transmission position to obtain more data of the eye to be inspected. can be obtained with certainty.

In the ophthalmologic apparatus according to the present invention, preferably, the data processing unit identifies the projection direction of the measurement light based on the arrangement of the optical system, and determines whether the measurement light is projected based on the transmission position and the projection direction. A reaching position reaching the fundus of the eye to be inspected is further specified, and the display control unit further displays an image representing the reaching position specified by the data processing part on the image of the fundus on the display means. It is characterized by

According to the ophthalmologic apparatus of the present invention, the data processing unit identifies the projection direction of the measurement light based on the arrangement of the optical system that collects the OCT data, and determines the transmission position of the measurement light and the projection direction of the measurement light. to specify the arrival position where the measurement light reaches the fundus of the eye to be examined. Then, the display control unit causes the display unit to further display the image representing the reaching position specified by the data processing unit, superimposed on the image of the fundus. Therefore, by visually recognizing the display means, the examiner can confirm the arrival position of the measurement light reaching the fundus of the subject's eye in the image of the fundus. Therefore, the examiner can confirm the arrival position at which the measurement light reaches the fundus of the eye to be examined while setting the transmission position where the measurement light passes through the anterior segment of the eye to be examined at an intended position. As a result, it is possible to shorten the time required to capture an image of the fundus while ensuring accuracy and accuracy.

In the ophthalmologic apparatus according to the present invention, preferably, the display control unit superimposes an image representing the arrival position specified by the data processing unit on the three-dimensional scanned image of the fundus acquired by the data acquisition unit. It is characterized by further displaying on the display means.

According to the ophthalmologic apparatus of the present invention, the examiner can confirm the arrival position of the measurement light reaching the fundus of the subject's eye in the three-dimensional scan image of the fundus by viewing the display means. As a result, it is possible to shorten the time required to capture a three-dimensional scan image of the fundus while ensuring accuracy and accuracy.

In the ophthalmologic apparatus according to the present invention, preferably, the display control unit superimposes an image representing a trajectory obtained by the optical coherence tomography scanning of the arrival position specified by the data processing unit on the image of the fundus to display the image. It is characterized in that it is displayed on the means.

According to the ophthalmologic apparatus of the present invention, the examiner visually recognizes the trajectory of the position where the measuring light reaches the fundus of the subject's eye by optical coherence tomography scanning by viewing the display means. can be confirmed in the B-scan image of the eye fundus and the three-dimensional scan image of the fundus. As a result, it is possible to shorten the time for OCT scanning of the three-dimensional region of the fundus of the eye to be inspected while ensuring accuracy and accuracy.

In the ophthalmologic apparatus according to the present invention, preferably, the data processing unit analyzes the OCT data to further identify the opacified region of the anterior segment, and the display control unit performs It is characterized in that the image representing the opacity region is superimposed on the image of the eye to be examined and further displayed on the display means.

According to the ophthalmologic apparatus according to the present invention, the examiner can easily grasp the opacified region in the anterior segment of the eye to be inspected by visually recognizing the display means, and the measurement light is directed to the anterior segment of the eye to be inspected. can be set at a position that avoids the cloudy area while confirming the transmission position of the transmission. As a result, it is possible to improve the precision and accuracy of photographing and measurement, and to shorten the time required for photographing and measurement.

According to the present invention, it is possible to provide an ophthalmologic apparatus capable of shortening the time required for imaging and measurement while ensuring the accuracy and accuracy of imaging and measurement.

1 is a schematic diagram showing an example of the configuration of an ophthalmologic apparatus according to an embodiment of the present invention; FIG. It is a schematic diagram showing an example of the configuration of the OCT unit of the present embodiment. It is a schematic diagram showing an example of a configuration of an arithmetic control unit of the present embodiment. It is a schematic diagram showing an example of a configuration of an arithmetic control unit of the present embodiment. 1 is a front view showing an example of an ophthalmologic apparatus according to this embodiment; FIG. 1 is a side view showing an example of an ophthalmologic apparatus according to this embodiment; FIG. FIG. 4 is a top view showing the positional relationship between an eye to be examined and an anterior segment camera; FIG. 4 is a side view showing the positional relationship between an eye to be inspected and an anterior segment camera; 4 is a flowchart for explaining an example of the operation of the ophthalmologic apparatus according to this embodiment; FIG. 4 is a schematic diagram showing a state in which an image representing transmission positions of measurement light is superimposed on the image of the anterior segment and displayed on the display unit. FIG. 10 is a schematic diagram showing a state in which an image representing the reaching position of the measuring light is superimposed on the image of the fundus and displayed on the display unit; FIG. 10 is a schematic diagram showing a state in which an image representing the reaching position of the measurement light is superimposed on the three-dimensional scan image of the fundus and displayed on the display unit. 9 is a flowchart for explaining a modification of the operation of the ophthalmologic apparatus according to the present embodiment; FIG. 10 is a schematic diagram showing a state in which an image representing the transmission position of the measuring light and an image representing the opacified region are displayed on the display unit superimposed on the image of the anterior segment. FIG. 10 is a schematic diagram showing a state in which an image representing the reaching position of the measuring light and an image representing the opacified region are displayed on the display unit superimposed on the image of the fundus. FIG. 10 is a schematic diagram showing a state in which an image representing the arrival position of the measuring light and an image representing the opacity region are superimposed on the three-dimensional scan image of the fundus and displayed on the display unit.

Preferred embodiments of the invention are described in detail below with reference to the drawings.
Since the embodiments described below are preferred specific examples of the present invention, various technically preferable limitations are applied. Unless otherwise stated, the invention is not limited to these modes. Further, in each drawing, the same constituent elements are denoted by the same reference numerals, and detailed description thereof will be omitted as appropriate.

An ophthalmologic apparatus according to an embodiment is used to acquire data of an eye to be examined optically (that is, using light and optical technology). In particular, the ophthalmologic apparatus according to the embodiment can acquire data of the subject's eye by making light enter the eye through the pupil of the subject's eye.

Such an ophthalmic device includes, for example, at least one of an imaging function and a measurement function. Examples of ophthalmic devices with imaging functions include optical coherence tomography, fundus cameras, scanning laser ophthalmoscopes, and the like. Examples of ophthalmic devices with measurement functions include axial length measuring devices, eye refraction testing devices, wavefront analyzers, microperimeters, and perimeters.

In the following example, an ophthalmic imaging apparatus that combines swept-source OCT and a fundus camera is described, but embodiments are not limited thereto. The type of OCT is not limited to swept source OCT, and may be spectral domain OCT, for example.

The swept source OCT splits the light from the wavelength tunable light source into measurement light and reference light, generates interference light by superimposing the return light of the measurement light from the object on the reference light, and balances the interference light. This is a method of forming an image by performing Fourier transform or the like on detection data collected according to wavelength sweeping and measurement light scanning by detecting with a photodetector such as a photodiode.

Spectral domain OCT divides light from a low coherence light source into measurement light and reference light, generates interference light by superimposing the return light of the measurement light from the object on the reference light, and generates the interference light spectrum In this method, the distribution is detected by a spectrometer, and the detected spectral distribution is subjected to Fourier transform or the like to form an image.

Thus, the swept-source OCT is an OCT technique that acquires a spectral distribution by time division, and the spectral domain OCT is an OCT technique that acquires a spectral distribution by space division. Note that the OCT techniques that can be used in the embodiments are not limited to these, and embodiments that use arbitrary OCT techniques different from these (for example, time domain OCT) can also be adopted.

In this specification, "image data" and "images" based thereon are not distinguished unless otherwise specified. In addition, unless otherwise specified, the site or tissue of the subject's eye is not distinguished from the image representing it.

[Constitution]
FIG. 1 is a schematic diagram showing an example configuration of an ophthalmologic apparatus according to an embodiment of the present invention.
The exemplary ophthalmic apparatus 1 shown in FIG. 1 includes a fundus camera unit 2, an OCT unit 100, and an arithmetic and control unit 200. As shown in FIG. The retinal camera unit 2 is provided with an optical system and a mechanism for acquiring a front image of the eye to be examined E and an optical system and a mechanism for executing OCT. The OCT unit 100 is provided with an optical system and a mechanism for performing OCT. The arithmetic control unit 200 includes one or more processors configured to perform various types of processing (calculation, control, etc.). Furthermore, the ophthalmologic apparatus 1 includes two anterior eye cameras 300 for photographing the anterior eye from two directions.

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. The base 410 houses a driving system such as an optical system driving unit and an arithmetic control circuit. A housing 420 provided on the base 410 houses an optical system. The objective lens 22 is housed in the lens housing portion 430 that protrudes from the front surface of the housing 420 .

Furthermore, the ophthalmologic apparatus 1 includes a lens unit for switching the site to which OCT is applied. Specifically, the ophthalmologic apparatus 1 includes an anterior segment OCT attachment 400 for applying OCT to the anterior segment. The anterior segment OCT attachment 400 may be configured in the same manner as the optical unit disclosed in Japanese Unexamined Patent Application Publication No. 2015-160103, for example.

As shown in FIG. 1, the anterior segment OCT attachment 400 can be arranged between the objective lens 22 and the eye E to be examined. When the anterior segment OCT attachment 400 is placed in the optical path, the ophthalmologic apparatus 1 can apply an OCT scan to the anterior segment. On the other hand, when the anterior segment OCT attachment 400 is retracted from the optical path, the ophthalmologic apparatus 1 can apply an OCT scan to the posterior segment. Movement of the anterior segment OCT attachment 400 is performed manually or automatically.

In other embodiments, an OCT scan can be applied to the posterior segment when the attachment is placed in the optical path, and an OCT scan can be applied to the anterior segment when the attachment is retracted from the optical path. you can Moreover, the measurement site that can be switched by the attachment is not limited to the posterior segment and the anterior segment of the eye, and may be any site of the eye. In addition, the configuration for switching the part to which the OCT scan is applied is not limited to such an attachment, and for example, a configuration including a lens that can be moved along the optical path, or a lens that can be inserted into and removed from the optical path It is also possible to adopt a configuration with

In this embodiment, the "processor" includes, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an ASIC (Application Specific Integrated Circuit), a programmable logic device (e.g., SPLD (Simple Programmable Logic Device (CPLD), Programmable Logic Device), FPGA (Field Programmable Gate Array)) or the like. The processor implements the functions according to the embodiment by, for example, reading and executing a program stored in a storage circuit or storage device.

[Fundus camera unit 2]
The fundus camera unit 2 is provided with an optical system for photographing the fundus Ef of the eye E to be examined. The acquired digital image of the fundus oculi Ef (called a fundus image, a fundus photograph, etc.) is generally a front image such as an observed image or a photographed image. Observation images are obtained by moving image shooting using near-infrared light. The photographed image is a still image using flash light in the visible region.

The fundus camera unit 2 includes an illumination optical system 10 and an imaging optical system 30 . The illumination optical system 10 irradiates the eye E to be inspected with illumination light. The imaging optical system 30 detects return light of the illumination light with which the eye E to be examined is irradiated. Measurement light from the OCT unit 100 is guided to the subject's eye E through an optical path in the fundus camera unit 2 . Return light of the measurement light projected onto the eye E (for example, the fundus oculi Ef) is guided to the OCT unit 100 through the same optical path in the fundus camera unit 2 .

Light (observation illumination light) output from the observation light source 11 of the illumination optical system 10 is reflected by the concave mirror 12, passes through the condenser lens 13, passes through the visible cut filter 14, and becomes near-infrared light. Further, the observation illumination light is once converged in the vicinity of the photographing light source 15, reflected by the mirror 16, passed through the relay lens system 17, the relay lens 18, the diaphragm 19, and the relay lens system 20, to the perforated mirror 21. be guided. 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 eye E (fundus oculi Ef). do. The return light of the observation illumination light from the subject's eye E is refracted by the objective lens 22, passes through the dichroic mirror 46, passes through the hole formed in the central region of the apertured mirror 21, and passes through the dichroic mirror 55. , through a focusing lens 31 and reflected by a mirror 32 . Further, this return light passes through the half mirror 33A, is reflected by the dichroic mirror 33, and is imaged on the light receiving surface of the image sensor 35 by the imaging lens . The image sensor 35 detects returned light at a predetermined frame rate. Note that the focus of the imaging optical system 30 is adjusted so as to match the fundus oculi Ef or the anterior segment of the eye.

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

A liquid crystal display (LCD) 39 displays a fixation target (fixation target image). A part of the light beam output from the LCD 39 is reflected by the half mirror 33A, reflected by the mirror 32, passes through the focusing lens 31 and the dichroic mirror 55, and passes through the aperture of the apertured mirror 21. The luminous flux that has passed through the aperture of the perforated mirror 21 is transmitted through the dichroic mirror 46, refracted by the objective lens 22, and projected onto the fundus oculi Ef. A fixation target is typically used for eye guidance and fixation. The direction in which the line of sight of the subject's eye E is guided (and fixed), that is, the direction in which fixation of the subject's eye E is encouraged is called a fixation position.

By changing the display position of the fixation target image on the screen of the LCD 39, the fixation position can be changed. Examples of fixation positions include a fixation position for acquiring an image centered on the macula, a fixation position for acquiring an image centered on the optic disc, and a position between the macula and the optic disc ( There is a fixation position for acquiring an image centered on the center of the eye fundus, and a fixation position for acquiring an image of a site far away from the macula (eye fundus periphery).

A graphical user interface (GUI) or the like may be provided for specifying at least one such exemplary fixation position. Further, a GUI or the like for manually moving the fixation position (the display position of the fixation target) can be provided. It is also possible to apply a configuration that automatically sets the fixation position.

A configuration for presenting a fixation target whose fixation position is changeable to the eye to be examined E is not limited to a display device such as an LCD. For example, a device (fixation matrix) in which a plurality of light-emitting units (light-emitting diodes, etc.) are arranged in a matrix can be employed instead of the display device. In this case, the fixation position of the subject's eye E by the fixation target can be changed by selectively lighting a plurality of light emitting units. As another example, a device with one or more movable light emitters can generate a fixation target whose fixation position can be changed.

The alignment optical system 50 generates an alignment index used for alignment of the optical system with respect to the eye E to be examined. Alignment light output from a light-emitting diode (LED) 51 passes through a diaphragm 52, a diaphragm 53, and a relay lens 54, is reflected by a dichroic mirror 55, passes through the hole of the perforated mirror 21, and passes through the dichroic mirror 46. It is transmitted and projected onto the subject's eye E via the objective lens 22 . The return light of the alignment light from the eye to be examined E is guided to the image sensor 35 through the same path as the return light of the observation illumination light. Manual alignment or automatic alignment can be performed based on the received light image (alignment index image).

Note that the alignment method applicable to the embodiment is not limited to the method using such an alignment index, and the method using the anterior eye camera 300 (described later), or the method of projecting light obliquely onto the cornea. It may be any known technique, such as an optical lever technique configured to detect corneal reflected light in opposite directions.

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

Diopter correction lenses 70 and 71 can be selectively inserted in the imaging optical path between the apertured mirror 21 and the dichroic mirror 55 . The dioptric correction lens 70 is a plus lens (convex lens) for correcting high hyperopia. The dioptric correction lens 71 is a minus lens (concave lens) for correcting strong myopia.

The dichroic mirror 46 synthesizes the fundus imaging optical path and the OCT optical path (measurement arm). The dichroic mirror 46 reflects light in the wavelength band used for OCT and transmits light for fundus imaging. The measurement arm is provided with a collimator lens unit 40, a retroreflector 41, a dispersion compensation member 42, an OCT focusing lens 43, an optical scanner 44, and a relay lens 45 in order from the OCT unit 100 side.

The retroreflector 41 is movable along the path of the measuring light LS incident on it, thereby changing the length of the measuring arm. The change in measurement arm length is used, for example, for optical path length correction according to the axial length of the eye, adjustment of the interference state, and the like.

The dispersion compensating member 42, together with the dispersion compensating member 113 (described later) arranged on the reference arm,
It acts to match the dispersion characteristics of the measurement light LS and the reference light LR.

An OCT focusing lens 43 is moved along the measuring arm to focus the measuring arm. In addition, the movement of the imaging focusing lens 31, the movement of the focusing optical system 60, and the movement of the OCT focusing lens 43 can be controlled in a coordinated manner.

The optical scanner 44 is substantially arranged at a position optically conjugate with the pupil of the eye E to be examined. A light scanner 44 deflects the measuring light LS guided by the measuring arm. The optical scanner 44 is, for example, a galvanometer scanner capable of two-dimensional scanning. Typically, the optical scanner 44 includes a one-dimensional scanner (x-scanner) for deflecting the measurement light in the ±x directions and a one-dimensional scanner (y-scanner) for deflecting the measurement light in the ±y directions. and including. In this case, for example, either one of these one-dimensional scanners is placed at a position optically conjugate with the pupil, or a position optically conjugate with the pupil is placed between these one-dimensional scanners.

[OCT unit 100]
FIG. 2 is a schematic diagram showing an example of the configuration of the OCT unit of this embodiment.
The exemplary OCT unit 100 shown in FIG. 2 is provided with optics for performing swept-source OCT. This optical system includes interference optics. This interference optical system divides the light from the wavelength tunable light source into measurement light and reference light, and superimposes the return light of the measurement light projected on the subject's eye E and the reference light that has passed through the reference optical path to obtain interference light. and detect this interference light. Data (detection signal) obtained by detecting the interference light is a signal representing the spectrum of the interference light and is sent to the arithmetic control unit 200 .

The light source unit 101 includes, for example, a near-infrared tunable laser that changes the wavelength of emitted light at high speed. Light L0 output from the light source unit 101 is guided to the polarization controller 103 by the optical fiber 102 . This adjusts the polarization state of the light L0. Further, the light L0 is guided by the optical fiber 104 to the fiber coupler 105 and split into the measurement light LS and the reference light LR. The optical path of the measurement light LS is called a measurement arm or the like, and the optical path of the reference light LR is called a reference arm or the like.

The reference light LR generated by the fiber coupler 105 is guided by the optical fiber 110 to the collimator 111 , converted into a parallel beam, and guided to the retroreflector 114 via the optical path length correction member 112 and the dispersion compensation member 113 . The optical path length correction member 112 acts to match the optical path length of the reference light LR and the optical path length of the measurement light LS. The dispersion compensation member 113 works together with the dispersion compensation member 42 arranged on the measurement arm to match the dispersion characteristics between the reference light LR and the measurement light LS. The retroreflector 114 is movable along the optical path of the reference light LR incident thereon. Thereby the length of the reference arm is changed. A change in the reference arm length is used, for example, for optical path length correction according to the axial length of the eye, adjustment of the interference state, and the like.

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

On the other hand, the measurement light LS generated by the fiber coupler 105 is guided to the collimator lens unit 40 through the optical fiber 127 and converted into a parallel light beam, which is then converted into a parallel light beam by the retroreflector 41, the dispersion compensating member 42, the OCT focusing lens 43, and the optical scanner 44. , and a relay lens 45, reflected by a dichroic mirror 46, refracted by an objective lens 22, and projected onto an eye E to be examined. The measurement light LS is scattered and reflected at various depth positions of the eye E to be examined. The return light of the measurement light LS from the subject's eye E travels in the opposite direction through the measurement arm, is guided to the fiber coupler 105 , and reaches the fiber coupler 122 via the optical fiber 128 .

The fiber coupler 122 superimposes the measurement light LS input via the optical fiber 128 and the reference light LR input via the optical fiber 121 to generate interference light. The fiber coupler 122 splits the generated interference light at a predetermined splitting ratio (for example, 1:1) to generate a pair of interference lights LC. A pair of interference lights LC are guided to detector 125 through optical fibers 123 and 124, respectively.

Detector 125 includes, for example, a balanced photodiode. A balanced photodiode includes a pair of photodetectors that respectively detect a pair of interference lights LC, and outputs a difference between a pair of detection signals obtained by these. Detector 125 sends this output (a detected signal such as a differential signal) to data acquisition system (DAQ) 130 .

A clock KC is supplied from the light source unit 101 to the data collection system 130 . The clock KC is generated in the light source unit 101 in synchronization with the output timing of each wavelength swept within a predetermined wavelength range by the wavelength tunable light source. The light source unit 101, for example, splits the light L0 of each output wavelength to generate two split lights, optically delays one of these split lights, combines these split lights, and produces the resulting combined light. A clock KC is generated based on the detection signal. The data acquisition system 130 samples the detection signal (difference signal) input from the detector 125 based on the clock KC. Data collection system 130 sends the data obtained by this sampling to arithmetic and control unit 200 .

In this example, both an element for changing the measurement arm length (eg retroreflector 41) and an element for changing the reference arm length (eg retroreflector 114 or reference mirror) are provided. However, only one of these elements may be provided. Also, the elements for changing the difference (optical path length difference) between the measurement arm length and the reference arm length are not limited to these, and arbitrary elements (optical members, mechanisms, etc.) can be adopted. .

[Arithmetic control unit 200]
3A and 3B are schematic diagrams showing an example of the configuration of the arithmetic control unit of this embodiment.
The arithmetic control unit 200 controls each part of the ophthalmologic apparatus 1 . Further, the arithmetic control unit 200 executes various kinds of arithmetic processing. For example, the arithmetic and control unit 200 performs signal processing such as Fourier transform on the spectral distribution based on the group of sampling data obtained by the data acquisition system 130 for each series of wavelength scans (for each A line), so that each A Form a reflection intensity profile in the line. Furthermore, the arithmetic and control unit 200 forms image data by imaging the reflection intensity profile of each A-line. Arithmetic processing therefor is the same as in conventional swept source OCT.

The arithmetic control unit 200 includes, for example, a processor, RAM (Random Access Memory), ROM (Read Only Memory), hard disk drive, communication interface, and the like. Various computer programs are stored in a storage device such as a hard disk drive. The arithmetic and control unit 200 may include an operation device, an input device, a display device, and the like.

[User Interface 240]
User interface 240 includes display unit 241 and operation unit 242 . The display unit 241 of this embodiment is an example of the "display means" of the present invention. Display unit 241 includes display device 3 . The operation unit 242 includes various operation devices and input devices. The user interface 240 may include a device, such as a touch panel, that combines a display function and an operation function. It is also possible to construct embodiments that do not include at least a portion of user interface 240 . For example, the display device may be an external device connected to the ophthalmic imaging equipment.

[Anterior segment camera 300]
FIG. 4A is a front view showing an example of an ophthalmologic apparatus according to this embodiment.
FIG. 4B is a side view showing an example of the ophthalmologic apparatus according to this embodiment.
The anterior segment camera 300 photographs the anterior segment of the subject's eye E from two or more different directions. The anterior segment camera 300 includes an imaging device such as a CCD image sensor or a CMOS image sensor. In this embodiment, two anterior eye cameras 300 are provided on the subject side surface of the retinal camera unit 2 (see anterior eye cameras 300A and 300B shown in FIG. 4A). As shown in FIGS. 1 and 4A, the anterior cameras 300A and 300B are located off the optical path passing through the objective lens 22. As shown in FIG. One or both of the anterior cameras 300A and 300B may be designated 300 hereinafter.

In this embodiment, two anterior cameras 300A and 300B are provided, but typically the number of anterior cameras may be any number greater than or equal to two. Considering the arithmetic processing to be described later, a configuration capable of imaging the anterior segment from two different directions is sufficient (but not limited to this). One or more movable anterior eye cameras 300 may also be provided.

In this embodiment, an 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 imaging of the anterior segment. That is, one of the two or more anterior eye cameras may include the imaging optical system 30 . The anterior segment camera 300 according to this embodiment may be capable of photographing the anterior segment from two (or more) different directions.

Arrangements may be provided for illuminating the anterior segment. The anterior segment illumination means includes, for example, one or more light sources. Typically, at least one light source (eg, an infrared light source) can be provided near each of the two or more anterior cameras.

Two or more anterior segment cameras can image the anterior segment substantially simultaneously from two or more different directions. "Substantially simultaneously" means that in addition to the case where the imaging timings of two or more anterior segment cameras are simultaneous, for example, it is acceptable that there is a difference in the imaging timings that can be ignored due to eye movement. show. Such substantially simultaneous photographing makes it possible to obtain images of the subject's eye E at substantially the same position and orientation with two or more anterior eye cameras.

Photographing by two or more anterior segment cameras may be moving image photographing or still image photographing. In the case of video shooting, by controlling the shooting start timing to match, or by controlling the frame rate and the shooting timing of each frame, it is possible to realize substantially simultaneous shooting of the anterior segment as described above. . On the other hand, in the case of still image shooting, this can be achieved by controlling the shooting timing to match.

[Control system]
An example of the configuration of the control system (processing system) of the ophthalmologic apparatus 1 is shown in FIGS. 3A and 3B. The control section 210, the image forming section 220, and the data processing section 230 are provided in the arithmetic control unit 200, for example.

[Control unit 210]
The control unit 210 includes a processor and controls each unit of the ophthalmologic apparatus 1 . Control unit 210 includes main control unit 211 and storage unit 212 .

[Main control unit 211]
The main control unit 211 includes a processor and controls each element of the ophthalmologic apparatus 1 (including the elements shown in FIGS. 1 to 3B). The main control unit 211 is implemented by cooperation of hardware including circuits and control software.

The photographic focusing lens 31 arranged in the photographic optical path and the focusing optical system 60 arranged in the illumination optical path are moved by a photographic focusing driving section (not shown) under the control of the main control section 211 . A retroreflector 41 provided on the measurement arm is moved by a retroreflector (RR) driving section 41A under the control of the main control section 211 . The OCT focus lens 43 placed on the measurement arm is moved by the OCT focus driver 43A under control of the main controller 211 . The optical scanner 44 provided on the measurement arm operates under the control of the main controller 211 . A retroreflector 114 located on the reference arm is moved by a retroreflector (RR) driver 114A under the control of the main controller 211 . Each of the mechanisms illustrated here typically includes an actuator such as a pulse motor that operates under the control of main control section 211 .

The moving mechanism 150 moves, for example, at least the retinal camera unit 2 three-dimensionally. In a typical example, the moving mechanism 150 includes an x stage that can move in ±x directions (horizontal direction), an x moving mechanism that moves the x stage, and a y stage that can move in ±y directions (vertical direction). , a y-moving mechanism for moving the y-stage, a z-stage movable in the ±z direction (depth direction), and a z-moving mechanism for moving the z-stage. Each of these moving mechanisms includes an actuator such as a pulse motor that operates under control of the main control section 211 .

[Storage unit 212]
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, information on an eye to be examined, and the like. The eye information to be examined includes subject information such as a patient ID and name, left/right eye identification information, electronic medical record information, and the like.

The storage unit 212 stores in advance aberration information (not shown). In the aberration information, for each anterior eye camera 300, information on distortion occurring in the captured image due to the influence of the optical system mounted thereon is recorded. Here, the optical system mounted on the anterior eye camera 300 includes an optical element such as a lens that generates distortion aberration. Aberration information can be said to be a parameter that quantifies the distortion that these optical elements give to a captured image.

An example of a method of generating aberration information will be described. Considering the instrumental error (difference in distortion aberration) of the anterior eye camera 300, the following measurements are performed for each anterior eye camera 300. FIG. An operator prepares a predetermined reference point. A reference point is a shooting target used to detect distortion aberration. The operator takes multiple shots while changing the relative position between the reference point and the anterior eye camera 300 . Thereby, a plurality of photographed images of the reference point photographed from different directions are obtained. The operator generates the aberration information of the anterior eye camera 300 by analyzing the captured images with a computer. The computer that performs this analysis processing may be the data processing unit 230, or any other computer (computer for inspection before product shipment, computer for maintenance, etc.).

An analytical process for generating aberration information includes, for example, the following steps:
an extraction step of extracting an image region corresponding to a reference point from each photographed image;
A distribution state calculation step of calculating a distribution state (coordinates) of an image area corresponding to a reference point in each captured image;
Distortion aberration calculation step of calculating a parameter representing distortion aberration based on the obtained distribution state;
a correction coefficient calculation step of calculating coefficients for correcting distortion based on the obtained parameters;

Parameters related to the distortion aberration given to the image by the optical system include principal point distance, principal point position (vertical direction, lateral direction), lens distortion (radial direction, tangential direction), and the like. The aberration information is configured as information (for example, table information) in which identification information of each anterior eye camera 300 and correction coefficients corresponding thereto are associated with each other. The aberration information generated in this manner is stored in the storage section 212 by the main control section 211 . Generation of such aberration information and aberration correction based thereon are called camera calibration or the like.

[Image forming unit 220]
The imager 220 forms OCT image data based on the data collected by the data collection system 130 . Image forming unit 220 includes a processor. The image forming unit 220 is implemented by cooperation of hardware including circuits and image forming software.

The image forming section 220 forms cross-sectional image data based on the data collected by the data collection system 130 . This processing includes signal processing such as denoising (noise reduction), filtering, and fast Fourier transform (FFT), similar to conventional swept-source OCT.

The image data formed by the image forming unit 220 is a group of images formed by imaging reflection intensity profiles in a plurality of A-lines (scan lines along the z-direction) arranged in the area to which the OCT scan is applied. 1 is a data set containing image data (a group of A-scan image data);

The image data formed by the image forming unit 220 is, for example, one or more B-scan image data or stack data formed by embedding a plurality of B-scan image data in a single three-dimensional coordinate system. The image forming unit 220 can also construct volume data (voxel data) by voxelizing the stack data. Stack data and volume data are typical examples of three-dimensional scan image data represented by a three-dimensional coordinate system.

The image forming section 220 can process the 3D scan image data. For example, the image forming unit 220 may apply rendering to the 3D scanned image data to construct new image data. Rendering techniques include volume rendering, maximum intensity projection (MIP), minimum intensity projection (MinIP), surface rendering, and multiplanar reconstruction (MPR). Further, the image forming unit 220 can construct projection data by projecting the three-dimensional scan image data in the z-direction (A-line direction, depth direction). Also, the image forming unit 220 can construct a shadowgram by projecting a portion of the 3D scan image data in the z-direction. A part of the three-dimensional scan image data projected to construct the shadowgram is set using, for example, segmentation.

[Data processing unit 230]
The data processing unit 230 executes various data processing. For example, the data processing unit 230 can apply image processing or analysis processing to OCT image data, or apply image processing or analysis processing to observed image data or photographed image data. The data processing unit 230 includes, for example, at least one of a processor and a dedicated circuit board.

[Data Acquisition Unit 250]
Please refer to FIG. 3B below. The data acquisition unit 250 is configured to optically acquire data of the eye E to be examined. In particular, the data acquisition unit 250 can project light onto the fundus oculi Ef and acquire data of the subject's eye E based on the return light. The data acquisition unit 250 can acquire image data by applying OCT to the eye E to be examined. The data acquisition section 250 includes a group of elements forming a measurement arm provided in the retinal camera unit 2 , a group of elements provided in the OCT unit 100 , and an image forming section 220 . In another example, the data acquisition unit 250 may include a configuration (illumination optical system 10, imaging optical system 30, etc.) for acquiring a fundus image.

The data acquisition unit 250 of this example also functions as an OCT unit having an anterior segment OCT optical system that applies an OCT scan to the three-dimensional region of the anterior segment of the subject's eye E and collects OCT data. When the data acquisition unit 250 is used as an OCT unit, the anterior segment OCT attachment 400 is inserted into the optical path. When the data acquisition unit 250 acquires data of the subject's eye E by projecting light onto the fundus oculi Ef, the anterior segment OCT attachment 400 is retracted from the optical path.

Thus, in this example, both anterior segment OCT and fundus OCT can be performed, but embodiments are not limited to this. For example, instead of or in addition to fundus OCT, the ophthalmologic apparatus according to the embodiment can perform fundus photography (fundus camera, SLO), axial length measurement, eye refraction test, and eye aberration measurement (wavefront analyzer). , a visual field test (microperimeter, perimeter) may be performed.

Further, in this example, an optical system (a data acquisition optical system included in the data acquisition unit 250) for projecting light onto the fundus oculi Ef and acquiring data of the eye to be examined E, and an optical system for the anterior segment OCT (anterior segment OCT optical system) includes a common scanning optical system. This common scanning optical system includes a group of elements forming a measurement arm provided in the retinal camera unit 2 and a group of elements provided in the OCT unit 100 . In other embodiments, it is not necessary to adopt such a configuration, and for example, the data acquisition optical system and the anterior segment OCT optical system may be provided separately.

[Alignment system 260]
Alignment system 260 includes elements for aligning the data acquisition optics. The alignment system 260 may include an alignment optical system 50 for projecting an alignment index onto the subject's eye E (first configuration). The alignment system 260 also includes two anterior eye cameras 300 and a position information acquisition unit 231 (described later) that obtains the three-dimensional position of the subject's eye E from two anterior eye images obtained substantially simultaneously by these cameras. (second configuration). Further, the alignment system 260 may include a light projection system, a light receiving system, and a processor for determining the position of the subject's eye E from the output from the light receiving system for performing alignment using an optical lever (second 3).

The ophthalmologic apparatus 1 according to this embodiment includes both the first and second configurations among the first to third configurations. There may be one, either two or three. Alternatively, the alignment system 260 may include configurations other than the first to third configurations. In other words, the alignment method performed by the alignment system 260 is arbitrary.

[Example of control unit 210]
The controller 210 illustrated in FIG. 3B includes a drive controller 2101 and a display controller 2102 . A drive control unit 2101 controls the moving mechanism 150 . A display control unit 2102 controls the user interface 240 (display unit 241). The drive control unit 2101 and the display control unit 2102 are included in the main control unit 211 shown in FIG. 3A.

[Example of data processing unit 230]
The data processing unit 230 illustrated in FIG. 3B includes a position information acquisition unit 231, a determination unit 232, a cloudy area identification unit 233, a movement target determination unit 234, a transmission position identification unit 236, and an arrival position identification unit 237. and including.

[Position information acquisition unit 231]
The position information acquisition unit 231 analyzes the two anterior segment images acquired by the two anterior segment cameras 300 capturing the anterior segments of the eye E to be inspected substantially simultaneously, and obtains the 3 Dimensional position can be determined. An example of processing executed by the position information acquisition unit 231 will be described below.

First, the position information acquisition unit 231 can correct the distortion of the captured image obtained by the anterior eye camera 300 based on the aberration information stored in the storage unit 212 . This correction can be performed, for example, by known image processing techniques based on correction coefficients for correcting distortion. Note that when the distortion aberration that the optical system of the anterior eye camera 300 gives to the captured image is sufficiently small, the aberration information and the correction using it may be unnecessary.

Next, the position information acquisition unit 231 can specify an image region (pupil region) corresponding to the pupil of the subject's eye E based on the distribution of pixel values (eg, luminance values) of the captured image. Since the pupil is generally expressed with lower luminance than other parts, it is possible to specify the pupil region 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. For example, the pupil region can be identified by searching for a substantially circular, low-intensity image region.

Subsequently, the position information acquisition unit 231 can identify the central position of the identified pupillary region. Utilizing the fact that the pupil is substantially circular as described above, the position information acquisition unit 231 performs, for example, a process of identifying the contour of the pupil region, a process of obtaining an approximate ellipse (or approximate circle) of the contour, and a process of specifying the center position of this approximated ellipse (or approximated circle). The center position of the approximate ellipse (or approximate circle) specified in this way is used as the pupil center of the eye E to be examined. As another example of processing for obtaining the center of the pupil, the position information acquisition unit 231 can obtain the center of gravity of the pupil region and set it as the center of the pupil.

The position information acquisition unit 231 obtains the center of the pupil of the subject's eye E based on the position (and imaging magnification) of the anterior eye camera 300 and the position of the center of the pupil in the two captured images specified in the preceding processing. can be obtained.

FIG. 5A is a top view showing the positional relationship between the subject's eye and the anterior segment camera.
FIG. 5B is a side view showing the positional relationship between the subject's eye and the anterior segment camera.
The distance (baseline length) between the anterior eye camera 300A and the anterior eye camera 300B is represented by "B". The distance (shooting distance) between the base line of the anterior eye cameras 300A and 300B and the pupil center P of the subject's eye E is represented by "H". The distance (screen distance) between the anterior eye camera 300A and its screen plane is represented 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 z direction (depth resolution): Δz=H×H×Δp/(B×f)

For example, the position information acquisition unit 231 obtains the positions (known) of the anterior eye cameras 300A and 300B and the position corresponding to the pupil center P in the two captured images, and arranges them as shown in FIGS. 5A and 5B. The three-dimensional position of the pupil center P can be calculated by applying a known trigonometry that considers the relationship.

Note that even when a feature point other than the center of the pupil is applied, the position information acquisition unit 231 applies the same processing as described above to obtain a three-dimensional image of the feature point based on the pixel value distribution of the captured image. It is possible to determine the position.

The position information acquired by the position information acquisition unit 231 (for example, information indicating the three-dimensional position of the pupil center) is sent to the control unit 210 . The drive control unit 2101 applies alignment control to the moving mechanism 150 based on this position information. This alignment control is an example of the aforementioned auto alignment.

[Determination unit 232]
As described above, the data acquisition unit 250 projects light onto the fundus oculi Ef and acquires data of the subject's eye E based on the return light. The determination unit 232 determines whether or not to apply a three-dimensional OCT scan to the anterior segment of the eye E to be examined based on the data acquired by the data acquisition unit 250 . Typically, after the above-described auto-alignment is performed, the data acquisition section 250 acquires data, and the determination section 232 performs determination.

The data acquired by the data acquisition unit 250 of this example is, for example, OCT data. Examples of OCT data are A-scan image data for axial length measurement or imaging. In this case, the determination unit 232 determines, for example, whether or not the luminance of this A-scan image data exceeds a predetermined threshold. Typically, it is determined whether a statistical value (for example, sum, average, maximum value) of luminance values of a group of pixels included in the A-scan image data exceeds a threshold. If this statistic value does not exceed the threshold, it is suggested that the measurement light LS and/or its return light has passed through an opaque portion within the eye E to be examined. In this threshold processing, for example, a default threshold or a threshold set according to A-scan image data or the like is used.

Even when the data acquisition unit 250 acquires other types of data, if the light to be projected onto the fundus oculi Ef and/or its return light passes through the opacity part in the eye to be examined E, the acquired data information indicating the intensity of (eg, luminance) is reduced. The determination unit 232 can make similar determinations based on the intensity of the data acquired by the data acquisition unit 250 .

[Muddy area specifying unit 233]
The opacity region specifying unit 233 analyzes OCT data acquired by three-dimensional OCT scanning of the anterior segment of the subject's eye E to specify the opacity region of the anterior segment. The opacity region is an image region corresponding to opacity inside the eye E to be examined. The region of opacity corresponds to the opacity of the medium translucency as seen in cataractous eyes.

For example, the opacity region identifying unit 233 analyzes a three-dimensional OCT image of the anterior segment or a projection image (or shadowgram) based thereon. The opaque region specifying unit 233 can obtain the distribution of pixel values (for example, brightness values) of such an OCT image and specify the opaque region based on this distribution. OCT images of the anterior segment show opacified areas as shadows. The opaque region specifying unit 233 specifies pixels whose brightness value is equal to or less than a predetermined threshold value by applying threshold processing regarding brightness to the OCT image. The pixel group specified by this is set to the cloudy area. In this threshold processing, for example, a default threshold or a threshold set according to an OCT image or the like is used.

[Movement target determination unit 234]
The moving target determination unit 234 determines the moving target of the data acquisition optical system included in the data acquisition unit 250 based on the cloudy area specified by the cloudy area specifying unit 233 . The determined moving target is used for alignment of the data acquisition optical system.

For example, an image representing the anterior segment of the subject's eye E and the opacity area specified by the opacity area specifying part 233 (information indicating its position/distribution) are input to the moving target determination unit 234 . The image representing the anterior segment is, for example, the OCT data processed by the opacity region specifying unit 233, an image obtained by processing this OCT data (eg, projection image, shadowgram), the fundus camera unit 2 An image obtained by processing the anterior eye image obtained by the anterior eye image obtained by the anterior eye camera 300 and the two anterior eye images obtained by the two anterior eye cameras 300 (for example, a front image).

If the image representing the anterior segment is neither the OCT data subjected to processing by the opacity region specifying unit 233 nor the processed image of this OCT data, the data processing unit 230 extracts the image representing the anterior segment and this OCT A registration can be made between the data (or its processed image). Registration may be, for example, image matching using feature points. According to the registration, the position (distribution) of opacified regions in the image representing the anterior segment can be obtained.

In addition, when the image representing the anterior segment is OCT data subjected to processing by the opacity region specifying unit 233 or a processed image of this OCT data, the image representing the anterior segment and the opacity region Since there is a trivial correspondence between , there is no need to apply registration.

The movement target determination unit 234 can determine the movement target of the data acquisition optical system so that the image representing the anterior segment passes through a position different from the opacity region. In other words, the movement target determination unit 234 can determine the movement target of the data acquisition optical system so that the measurement light LS projected by the data acquisition unit 250 is guided while avoiding turbidity in the eye E to be examined.

The movement target determination unit 234 can determine the movement target of the data acquisition optical system in consideration of the beam diameter of the measurement light LS. For example, the movement target determination unit 234 can determine the movement target of the data acquisition optical system such that the entire beam cross section of the measurement light LS passes through the non-turbidity portion.

In order to reduce the speckle noise mixed in the image, the controller 210 can control the optical scanner 44 so as to temporally change the deflection direction of the measurement light LS. In this case, the movement target determining section 234 can determine the movement target of the data acquisition optical system in consideration of changes in the passing position of the measurement light LS. For example, the movement target determination unit 234 can determine the movement target of the data acquisition optical system so that the change range of the passing position of the measurement light LS at a predetermined depth position within the eye E to be examined does not overlap with the cloudy region. can. Since the optical scanner 44 is typically arranged at a position optically conjugated to the pupil of the eye E to be inspected, the measurement light LS passes through a location relatively far from the pupil (for example, the posterior surface of the crystalline lens). A movement target for the data acquisition optics can be determined such that the range of change in position does not overlap with the turbidity region. The distance between the pupil and the predetermined location may be, for example, a value obtained by measuring the subject's eye E or a value obtained from model eye data.

The movement target determined by the movement target determination unit 234 is, for example, information including at least the x-coordinate and the y-coordinate. The determined moving target is sent to the control unit 210 .

When automatically correcting the alignment of the data acquisition optical system, the drive control section 2101 can control the movement mechanism 150 based on the movement target determined by the movement target determination section 234 . For example, the drive control unit 2101 can control the movement mechanism 150 so that the data acquisition optical system is moved to a position corresponding to the x-coordinate and y-coordinate included in the movement target.

When manually correcting the alignment of the data acquisition optical system, the display control unit 2102 can cause the display unit 241 to display, for example, an image representing the anterior segment described above. The display control unit 2102 can display the alignment index image together with the image representing the anterior segment. The operation unit 242 is used by the user to perform alignment operations for the data acquisition optical system. The drive control section 2101 can control the moving mechanism 150 based on signals input from the operation section 242 . Thereby, the user can move the data acquisition optical system to a desired position.

When the alignment is manually corrected, the display control unit 2102 can cause the display unit 241 to display information for alignment operation (alignment support information) based on the movement target obtained by the movement target determination unit 234. can. Alignment assistance information may include, for example, information indicating a position corresponding to a moving target displayed together with an image representing the anterior segment. Alternatively, the alignment support information may be information indicating the operation direction (movement direction) and/or the operation amount (movement amount), such as an arrow image pointing from the current position of the data acquisition optical system to the position corresponding to the movement target. may contain. Such alignment support information is generated, for example, based on the x-coordinate and y-coordinate included in the moving target.

[Transmission position specifying unit 236]
The transmission position specifying unit 236 specifies a transmission position where the measurement light LS passes through the anterior segment of the subject's eye E based on the arrangement of at least one of the data acquisition optical system and the OCT optical system. The OCT optical system is an optical system that projects the measurement light LS onto the eye E to be examined, applies an OCT scan to the three-dimensional region of the eye E to be examined, and obtains OCT data. That is, the transmission position specifying unit 236 specifies a transmission position at which the measurement light LS passes through or passes through the cornea, pupil, or lens when entering the eye E through the pupil of the eye E to be inspected. The transmission position is an image position corresponding to a position where the measurement light LS is transmitted through the anterior segment of the eye E to be examined.

For example, information about the arrangement of the alignment system 260 is input to the transmission position specifying unit 236 . Information about the placement of the alignment system 260 may include information about the placement of the alignment optical system 50 for projecting the alignment index onto the eye E to be examined. Information about the placement of the alignment system 260 may also include information about the placement of the data acquisition optical system. Further, information on the arrangement of the alignment system 260 is obtained by the position information obtaining unit 231 that obtains the three-dimensional position of the subject's eye E from two anterior eye images obtained substantially simultaneously by the two anterior eye cameras 300. The position information of the subject's eye E may also be included. Also, the information about the arrangement of the alignment system 260 may include information about the arrangement of the light projection system and the light receiving system for performing alignment using an optical lever. Also, the information about the placement of the alignment system 260 may include information about alignment control executed based on the position information of the subject's eye E acquired by the position information acquisition unit 231 . The transmission position specifying unit 236 specifies at least the x-coordinate and the y-coordinate of the transmission position where the measurement light LS passes through the anterior segment of the eye E to be examined.

The display control unit 2102 can cause the display unit 241 to display an image that expresses the anterior segment described above with respect to the movement target determination unit 234 . The display control unit 2102 superimposes the image representing the transmission position of the measuring light LS in the anterior segment of the eye E to be examined, specified by the transmission position specifying unit 236, on the image of the anterior segment (image representing the anterior segment). Displayed on the display unit 241 . For example, the display control unit 2102 superimposes an image representing the transmission position of the measurement light LS on the front image of the anterior segment obtained by processing the two anterior segment images acquired by the two anterior segment cameras 300. to display on the display unit 241. The image of the anterior segment displayed on the display unit 241 by superimposing the image representing the transmission position of the measurement light LS is not limited to the front image obtained by the two anterior segment cameras 300, and may be a retroillumination image, an OCT tomographic image, or a It may be an OCT front image or the like.

[Arrived position specifying unit 237]
The reaching position specifying unit 237 specifies the projection direction of the measurement light LS projected onto the subject's eye E based on the arrangement of at least one of the data acquisition optical system and the OCT optical system. Further, the arrival position specifying unit 237 determines whether the measurement light LS is transmitted based on the transmission position of the measurement light LS specified by the transmission position specifying unit 236 and the projection direction of the measurement light LS specified by the arrival position specifying unit 237. A reaching position reaching the fundus oculi Ef of the eye E to be examined is specified. The arrival position is an image position corresponding to the position where the measurement light LS reaches the fundus Ef of the eye E to be examined.

For example, information about the arrangement of the OCT optical system is input to the arrival position specifying unit 237 . Information about the placement of the OCT optical system includes, for example, information about the angle of the optical scanner 44 . Thereby, the arrival position specifying unit 237 specifies the projection direction of the measurement light LS projected onto the eye E to be inspected, for example, the angle between the optical axis of the objective lens 22 and the traveling direction of the measurement light LS. Then, for example, the arrival position specifying unit 237 determines based on the transmission position of the measurement light LS specified by the transmission position specifying unit 236 and the angle between the optical axis of the objective lens 22 and the traveling direction of the measurement light LS. to specify the reaching position where the measurement light LS reaches the fundus Ef of the eye E to be examined.

The display control unit 2102 can cause the display unit 241 to display an image representing the fundus oculi Ef of the eye E to be examined. The display control unit 2102 superimposes the image representing the arrival position of the measurement light LS on the fundus Ef of the eye E to be examined, which is specified by the arrival position specifying unit 237, on the image of the fundus Ef (image representing the fundus Ef of the eye E to be examined). to display on the display unit 241. For example, the display control unit 2102 causes the display unit 241 to display an image representing the arrival position of the measuring light LS superimposed on the front image of the fundus oculi Ef obtained by imaging using near-infrared light. The image of the fundus oculi Ef overlaid on the display unit 241 with the image representing the arrival position of the measurement light LS is not limited to the front image by near-infrared light, and may be a three-dimensional scan image or the like. The three-dimensional scan image is as described above with respect to image forming section 220 .

When the axial length data and the corneal curve data are stored in the storage unit 212 as the subject information, the reachable position specifying unit 237 determines based on the axial length data and the corneal curve data stored in the storage unit 212. The eyeball model may be modified by Alternatively, the axial length data and the corneal curve data may be stored in the storage unit 212 as a table set according to age, for example. Thereby, the reaching position specifying unit 237 can more accurately specify the reaching position where the measurement light LS reaches the fundus Ef of the eye E to be examined. Then, the display control unit 2102 can display an image representing the arrival position of the measuring light LS superimposed on the three-dimensional scan image corrected according to the subject's age, for example.

[motion]
FIG. 6 is a flowchart explaining an example of the operation of the ophthalmologic apparatus according to this embodiment.
FIG. 7 is a schematic diagram showing a state in which an image representing the transmission position of the measurement light is superimposed on the image of the anterior segment and displayed on the display unit.
FIG. 8 is a schematic diagram showing a state in which an image representing the reaching position of the measuring light is superimposed on the image of the fundus and displayed on the display unit.
FIG. 9 is a schematic diagram showing a state in which an image representing the arrival position of the measurement light is superimposed on the three-dimensional scan image of the fundus and displayed on the display unit.

(S1: Alignment start)
An example of the operation of the ophthalmologic apparatus 1 according to this embodiment will be described.
First, alignment of the data acquisition optical system using the alignment system 260 is started.
This alignment may be manual alignment, but is typically auto alignment.

Auto-alignment can be performed using, for example, the anterior eye camera 300, the position information acquisition unit 231, the drive control unit 2101, and the like (stereo camera method). Alternatively, the auto-alignment may be any one of alignment using an alignment index generated by the alignment optical system 50, alignment using an optical lever, alignment using a Purkinje image, and alignment using other methods. .

(S2: Alignment completed)
The alignment in step S1 is completed when the alignment of the data acquisition optical system with respect to the subject's eye E falls within a predetermined allowable range.

For example, according to the auto-alignment of the stereo camera system in this embodiment, the optical axis of the data acquisition optical system is substantially aligned with the pupil center of the eye E to be inspected (alignment in the xy direction), and the eye E to be inspected and the data The distance from the acquisition optical system (for example, the objective lens 22) is approximately matched to a predetermined working distance (alignment in the z direction).

Upon completion of the alignment, known tracking for moving the data acquisition optical system in accordance with the movement of the eye E to be examined may be started.

(S3: Acquire data by projecting light toward the fundus)
Upon completion of the alignment, the control section 210 causes the data acquisition section 250 to acquire data. The data acquisition unit 250 of this example projects the measurement light LS toward the fundus Ef of the eye E to be examined, detects the interference light LC generated by superimposing the return light and the reference light LR, and detects the interference light LC. A-scan image data, B-scan image data and/or three-dimensional scan image data are formed from the data collected by 130 .

(S4: Identify the transmission position of the measurement light)
When the alignment is completed and the measurement light LS is projected onto the eye E to be examined, the transmission position specifying unit 236 determines whether the measurement light LS is projected onto the eye E to be examined based on the arrangement of at least one of the data acquisition optical system and the OCT optical system. Identify the transmission position of the anterior segment of the eye. For example, information about the result of auto-alignment by the alignment system 260 is input to the transmission position specifying section 236 . Information about the result of auto-alignment includes, for example, information about alignment in the xy direction (x-coordinate and y-coordinate). In this case, the transmission position specifying unit 236 specifies the transmission position where the measurement light LS passes through the anterior segment of the subject's eye E based on the information about the alignment in the xy direction (x coordinate and y coordinate).

(S5: Display an image representing the transmission position of the measurement light superimposed on the image of the anterior segment)
Subsequently, the display control unit 2102 causes the display unit 241 to display an image representing the transmission position of the measuring light LS in the anterior segment of the eye E specified by the transmission position specification unit 236 so as to be superimposed on the image of the anterior segment. . For example, as shown in FIG. 7, the display control unit 2102 displays the image TP representing the transmission position of the measurement light LS in the anterior segment Ea of the eye E to be examined, which is specified by the transmission position specifying unit 236. The image is superimposed on the OCT front image (projection image or the like) 700 of the anterior segment Ea and displayed on the display unit 241 . More preferably, the image TP representing the transmission position of the measurement light LS is a circular image corresponding to a diameter of about 0.5 mm or more and 2 mm or less in the anterior segment Ea of the eye E to be examined.

(S6: Identify the arrival position of the measurement light)
Subsequently, the arrival position specifying unit 237 specifies the projection direction of the measurement light LS projected onto the subject's eye E based on the arrangement of at least one of the data acquisition optical system and the OCT optical system, and the transmission position specifying unit 236 Based on the specified transmission position of the measurement light LS and the projection direction of the measurement light LS specified by the arrival position specifying unit 237, the arrival position at which the measurement light LS reaches the fundus Ef of the subject's eye E is specified. For example, information about the angle of the optical scanner 44 is input to the arrival position specifying section 237 . In this case, the arrival position specifying unit 237 specifies the angle between the optical axis of the objective lens 22 and the traveling direction of the measurement light LS based on the information about the angle of the optical scanner 44, and the transmission position specifying unit 236 and the angle between the optical axis of the objective lens 22 and the traveling direction of the measurement light LS, the measurement light LS reaching the fundus Ef of the eye E to be examined based on the transmission position of the measurement light LS specified by Locate.

(S7: Display an image representing the arrival position of the measurement light superimposed on the image of the fundus)
Subsequently, the display control unit 2102 causes the display unit 241 to display an image representing the reaching position of the measuring light LS on the fundus Ef of the eye E identified by the reaching position identifying unit 237 so as to be superimposed on the image of the fundus Ef. For example, as shown in FIG. 8, the display control unit 2102 displays the image RP representing the arrival position of the measurement light LS in the fundus Ef of the eye E to be examined, which is specified by the arrival position specifying unit 237, as the retinal camera unit 2 (or , another fundus photographing device) is superimposed on the fundus image 500 and displayed on the display unit 241 . More preferably, the image RP representing the arrival position of the measurement light LS is a circular image corresponding to a diameter of approximately 0.5 mm or more and 2 mm or less at the fundus oculi Ef of the eye E to be examined.

In addition, the display control unit 2102 superimposes an image RPT representing the trajectory of the arrival position of the measurement light LS on the fundus oculi Ef of the eye E to be inspected E identified by the arrival position identification unit 237 on the fundus image 500 on the display unit 241 . to display. As shown in FIG. 8, the image RPT representing the trajectory of the arrival position of the measurement light LS obtained by the OCT scan is represented by a dashed line or a dotted line.

More preferably, the display control unit 2102 causes the display unit 241 to display the image TP representing the transmission position of the measuring light LS superimposed on the OCT front image 700 of the anterior segment Ea of the eye E to be examined, substantially at the same time. An image RP representing the arrival position of the measurement light LS is superimposed on the fundus image 500 and displayed on the display unit 241 . That is, the display control unit 2102 causes the display unit 241 to display the image shown in FIG. 7 and the image shown in FIG. 8 substantially simultaneously. As a result, the examiner visually recognizes the transmission position of the measuring light LS in the anterior segment Ea of the eye to be examined E and the measuring light LS in the fundus Ef of the eye to be examined E which are specified substantially simultaneously. The arrival position can be confirmed in the OCT front image 700 on which the image TP representing the transmission position is superimposed and displayed, and the fundus image 500 on which the image RP representing the arrival position is superimposed and displayed.

Further, the image of the fundus oculi Ef of the subject's eye E displayed on the display unit 241 in step S7 is not limited to the fundus oculi image 500 acquired by the retinal camera unit 2 . For example, as shown in FIG. 9, the display control unit 2102 causes the image forming unit 220 to form an image RP representing the arrival position of the measurement light LS on the fundus Ef of the eye to be examined E specified by the arrival position specifying unit 237. The image may be displayed on the display unit 241 superimposed on the three-dimensional scan image 500B expressed by the three-dimensional coordinate system. The three-dimensional scanned image 500B shown in FIG. 9 is generated based on, for example, an eyeball model based on axial length data and corneal curve data stored in the storage unit 212, and a fundus image acquired by the fundus camera unit 2. This image is a combination of the fundus model and the image.

In the image example shown in FIG. 9, a B-scan image 500A of the fundus oculi Ef obtained by fundus OCT of the OCT unit 100 is displayed. The examiner can confirm whether or not the measurement light LS has reached the fundus oculi Ef of the eye E to be examined by confirming the B-scan image 500A. Further, in the image example shown in FIG. 9, a B-scan image 500C of the anterior segment acquired by the anterior segment OCT of the OCT unit 100 is displayed on the upper right of the three-dimensional scanned image 500B. The examiner checks the image 501C representing the measurement light LS displayed in the B-scan image 500C of the anterior segment to check the state in which the measurement light LS is transmitted through the cornea, pupil, and lens of the eye E to be examined. can do. Note that the B-scan image 500A of the fundus oculi Ef and the B-scan image 500C of the anterior segment may not be images obtained substantially at the same time. For example, the B-scan image 500C of the anterior segment may be an image acquired in advance and stored in the storage unit 212 .

In this case as well, the display control unit 2102 converts the image RPT representing the trajectory of the arrival position of the measuring light LS in the fundus oculi Ef of the eye to be examined E specified by the arrival position specifying unit 237 to the three-dimensional scanned image 500B. They can be superimposed and displayed on the display unit 241 . Even in this case, as shown in FIG. 9, the image RPT representing the trajectory of the arrival position of the measurement light LS obtained by the OCT scan is represented by a dashed line or a dotted line.

More preferably, the display control unit 2102 causes the display unit 241 to display the image TP representing the transmission position of the measuring light LS superimposed on the OCT front image 700 of the anterior segment Ea of the eye E to be examined, substantially at the same time. An image RP representing the arrival position of the measuring light LS is superimposed on at least one of the fundus image 500 and the three-dimensional scan image 500B and displayed on the display unit 241 . As a result, the examiner visually recognizes the transmission position of the measuring light LS in the anterior segment Ea of the eye to be examined E and the measuring light LS in the fundus Ef of the eye to be examined E which are specified substantially simultaneously. The arrival position is at least one of the OCT front image 700 overlaid with the image TP representing the transmission position and at least one of the fundus image 500 and the three-dimensional scan image 500B overlaid with the image RP representing the arrival position. can be confirmed.

(S8: Determining the movement target of the data acquisition optical system)
The movement target determination unit 234 determines the transmission position of the measurement light LS in the anterior segment Ea of the eye to be examined E identified in step S4, and the arrival position of the measurement light LS in the fundus oculi Ef of the eye to be examined E identified in step S6. , to determine the movement target of the data acquisition optics.

The movement target determination unit 234 determines the movement target such that the optical axis (measurement light LS) of the data acquisition optical system passes through a position different from the turbid region, for example. As described above, in determining the moving target, the beam diameter of the measurement light LS and/or the deflection range of the measurement light LS for speckle noise reduction may be considered.

The display control unit 2102 can display information indicating the determined movement target on the display unit 241 together with an image representing the anterior segment.

In addition, in the operation of the ophthalmologic apparatus 1 in the flowchart shown in FIG. 6, the movement target determination unit 234 automatically corrects the alignment of the data acquisition optical system. However, the alignment of the data acquisition optical system is not limited to automatic, and may be corrected manually. That is, when the examiner visually recognizes the display unit 241, the OCT front image 700 superimposed with the image TP representing the transmission position and the fundus image 500 superimposed with the image RP representing the arrival position and the three-dimensional scan are displayed. An operation for correcting the alignment of the data acquisition optical system may be performed using the operation unit 242 while referring to at least one of the images 500B.

(S9: Move data acquisition optical system)
The drive control unit 2101 controls the movement mechanism 150 to move the optical axis of the data acquisition optical system to the position (x coordinate, y coordinate) indicated by the movement target determined in step S8.

(S10: Acquire data by projecting light toward the fundus)
After the movement of the data acquisition optical system in step S9 is completed, the control section 210 causes the data acquisition section 250 to acquire data. Alternatively, in response to the fact that the ophthalmologic apparatus 1 has detected the completion of the alignment correction, the control section 210 causes the data acquisition section 250 to acquire data. The data acquisition unit 250 of this example projects the measurement light LS toward the fundus Ef of the eye E to be examined, detects the interference light LC generated by superimposing the return light and the reference light LR, and detects the interference light LC. OCT image data is formed from the data acquired by 130 .

For example, the OCT image data is A-scan OCT image data, and the data processing unit 230 calculates the cornea-retina distance from this A-scan OCT image data. This cornea-retina distance can be referred to as an approximation of the axial length of the eye. In other examples, the OCT image data is B-scan image data or 3D scan image data.

The data acquisition performed in step S10 is not limited to OCT, for example fundus photography (retinal camera, SLO), eye refraction examination, ocular aberration measurement (wavefront analyzer), or visual field examination (microperimeter, perimeter). may be With this, the operation illustrated in FIG. 6 is completed.

[Modification]
FIG. 10 is a flowchart illustrating a modification of the operation of the ophthalmologic apparatus according to this embodiment.
FIG. 11 is a schematic diagram showing a state in which an image representing the transmission position of the measurement light and an image representing the opacified region are displayed on the display unit while being superimposed on the image of the anterior segment.
FIG. 12 is a schematic diagram showing a state in which an image representing the arrival position of the measuring light and an image representing the opacity region are displayed on the display unit superimposed on the image of the fundus.
FIG. 13 is a schematic diagram showing a state in which an image representing the reaching position of the measuring light and an image representing the opacity region are superimposed on the three-dimensional scan image of the fundus and displayed on the display unit.

(S21-S27)
A modification of the operation of the ophthalmologic apparatus 1 according to this embodiment will be described.
First, steps S21 to S27 are executed in the same manner as steps S1 to S7 in FIG. 6, respectively.

(S28: Apply 3D OCT to the anterior segment)
Subsequently, the anterior segment OCT attachment 400 is inserted between the objective lens 22 and the eye E to be examined. The control unit 210 controls the data acquisition unit 250 to apply three-dimensional OCT to the anterior segment of the eye E to be examined.

The data acquisition unit 250 (image forming unit 220) can form an image representing the anterior segment (projection image, shadowgram, etc.) from the 3D OCT image data obtained by the 3D OCT of the anterior segment. can.

Aside from the anterior segment OCT, it is also possible to obtain an image representing the anterior segment using the fundus camera unit 2, the anterior segment camera 300, and the like.

(S29: Specify cloudy area in front image)
The opacity region specifying unit 233 analyzes the three-dimensional OCT image data (or an image expressing the anterior segment based thereon) acquired in step S28 to specify the opacity region of the anterior segment.

The display control unit 2102 superimposes the information indicating the opacity region specified by the opacity region specifying unit 233 on the image of the anterior segment and the image representing the transmission position of the measurement light LS in the anterior segment of the eye E to be examined, and displays the information on the display unit. 241 can be displayed. For example, as shown in FIG. 11, the display control unit 2102 converts an image 710 representing the opacity region specified by the opacity region specifying unit 233 to the anterior ocular segment Ea of the subject's eye E specified by the transmission position specifying unit 236. and an OCT front image (projection image or the like) 700 of the anterior segment Ea of the eye E to be examined are superimposed on the display unit 241 .

Further, the display control unit 2102 superimposes the information indicating the opacity region specified by the opacity region specifying unit 233 on the image of the fundus oculi Ef and the image representing the arrival position of the measurement light LS on the fundus oculi Ef of the eye E to be examined. 241 can be displayed. For example, as shown in FIG. 12, the display control unit 2102 causes the image 510 representing the opacity region specified by the opacity region specifying unit 233 to be measured at the fundus Ef of the subject's eye E specified by the reaching position specifying unit 237. The image RP representing the arrival position of the light LS and the fundus image 500 acquired by the fundus camera unit 2 (or other fundus photographing device) are superimposed and displayed on the display unit 241 . Image 510 representing the opaque area in FIG. 12 is an image of the area affected by image 710 representing the opaque area in FIG. That is, the image 510 representing the opaque area in FIG. 12 corresponds to the image 710 representing the opaque area in FIG.

In addition, the display control unit 2102 superimposes an image RPT representing the trajectory of the arrival position of the measurement light LS on the fundus oculi Ef of the eye E to be inspected E identified by the arrival position identification unit 237 on the fundus image 500 on the display unit 241 . to display. As shown in FIG. 12, the image RPT representing the trajectory of the arrival position of the measurement light LS obtained by the OCT scan is represented by a dashed line or a dotted line.

More preferably, the display control unit 2102 superimposes the image 710 representing the opacity region on the image TP representing the transmission position of the measuring light LS and the OCT front image 700 of the anterior segment Ea of the eye E to be examined, and displays the image on the display unit 241. Substantially at the same time as the timing to cause the display unit 241 to display the image 510 representing the opacity region so as to be superimposed on the image RP representing the arrival position of the measuring light LS and the fundus image 500 . That is, the display control unit 2102 causes the display unit 241 to display the image shown in FIG. 11 and the image shown in FIG. 12 substantially simultaneously. As a result, the examiner visually recognizes the display unit 241 to substantially simultaneously measure the transmission position of the measuring light LS in the anterior segment Ea of the eye to be examined E, the opacity region, and the fundus Ef of the eye to be examined E. An OCT front image 700 in which an image TP representing the transmission position and an image 710 representing the opacity region are superimposed and displayed, and an image RP representing the arrival position and an image 510 representing the opacity region are displayed. This can be confirmed with the superimposed fundus image 500 .

Further, for example, as shown in FIG. 13, the display control unit 2102 displays an image 510B representing the opacity region specified by the opacity region specifying unit 233 on the fundus Ef of the subject's eye E specified by the reaching position specifying unit 237. The image RP representing the arrival position of the measurement light LS and the three-dimensional scan image 500B represented by the three-dimensional coordinate system formed by the image forming section 220 may be superimposed on the display section 241 and displayed. Three-dimensional scanned image 500B is as described above with respect to FIG. Also, the B-scan image 500A of the fundus oculi Ef and the B-scan image 500C of the anterior segment shown in FIG. 13 are as described above with reference to FIG. Image 510B representing the opaque area in FIG. 13 is an image of the area affected by image 710 representing the opaque area in FIG. That is, the image 510B representing the opaque area in FIG. 13 corresponds to the image 710 representing the opaque area in FIG.

In this case as well, the display control unit 2102 converts the image RPT representing the trajectory of the arrival position of the measuring light LS in the fundus oculi Ef of the eye to be examined E specified by the arrival position specifying unit 237 to the three-dimensional scanned image 500B. They can be superimposed and displayed on the display unit 241 . Even in this case, as shown in FIG. 13, the image RPT representing the trajectory of the arrival position of the measurement light LS obtained by the OCT scan is represented by a dashed line or a dotted line.

The display control unit 2102 controls the display unit 241 to display the image 710 representing the opacity region superimposed on the image TP representing the transmission position of the measurement light LS and the OCT front image 700 of the anterior segment Ea of the eye E to be examined. Simultaneously, images 510 and 510B representing opacified regions are superimposed on at least one of the fundus image 500 and the three-dimensional scan image 500B and displayed on the display unit 241 . As a result, the examiner visually recognizes the display unit 241 to substantially simultaneously measure the transmission position of the measuring light LS in the anterior segment Ea of the eye to be examined E, the opacity region, and the fundus Ef of the eye to be examined E. An OCT front image 700 in which an image TP representing the transmission position and an image 710 representing the opacity region are superimposed on the arrival position and the opacity region of the light LS, and an image RP representing the arrival position and an image 510 representing the opacity region. 510B can be confirmed in at least one of the fundus image 500 and the three-dimensional scan image 500B overlaid and displayed.

(S30: Determination of movement target of data acquisition optical system)
The movement target determination unit 234 moves the data acquisition optical system based on the transmission position of the measurement light LS in the anterior segment Ea of the eye to be examined E identified in step S24 and the opacity region identified in step S29. Determine your goals.

The movement target determination unit 234 determines the movement target so that the optical axis (measurement light LS) of the data acquisition optical system passes through a position different from the cloudy area. As described above, in determining the moving target, the beam diameter of the measurement light LS and/or the deflection range of the measurement light LS for speckle noise reduction may be considered.

The display control unit 2102 can cause the display unit 241 to display information indicating the determined movement target together with an image representing the anterior segment and/or information indicating the opacified region.

Note that in the operation of the ophthalmologic apparatus 1 in the flowchart shown in FIG. 10, the movement target determination unit 234 automatically corrects the alignment of the data acquisition optical system. However, the alignment of the data acquisition optical system is not limited to automatic, and may be corrected manually. That is, when the examiner visually recognizes the display unit 241, the OCT front image 700 in which the image TP representing the transmission position and the image 710 representing the opacity region are superimposed and displayed, the image RP representing the arrival position, and the image representing the opacity region The operation unit 242 may be used to correct the alignment of the data acquisition optical system while referring to at least one of the fundus image 500 and the three-dimensional scan image 500B in which 510 and 510B are superimposed and displayed.

(S31: Move data acquisition optical system)
The drive control unit 2101 controls the movement mechanism 150 to move the optical axis of the data acquisition optical system to the position (x coordinate, y coordinate) indicated by the movement target determined in step S30.

(S32: Acquire data by projecting light toward the fundus)
After the movement of the data acquisition optical system in step S31 is completed, the control unit 210 causes the data acquisition unit 250 to acquire data in the same manner as in step S10 of FIG. Alternatively, in response to the fact that the ophthalmologic apparatus 1 has detected the completion of the alignment correction, the control section 210 causes the data acquisition section 250 to acquire data in the same manner as in step S10 of FIG. This completes the operation illustrated in FIG.

[effect]
According to the ophthalmologic apparatus 1 according to the present embodiment, the data processing unit 230 identifies the transmission position at which the measurement light LS passes through the anterior segment Ea of the subject's eye E based on the arrangement of the optical system that collects OCT data. . Then, the display control unit 2102 causes the display unit 241 to display the image TP representing the transmission position specified by the data processing unit 230 so as to be superimposed on the image of the eye E to be examined. Therefore, the examiner can confirm the transmission position at which the measurement light LS is transmitted through the anterior segment Ea of the eye E to be examined by viewing the display unit 241 . Therefore, the examiner can set the transmission position where the measurement light LS is transmitted through the anterior segment Ea of the eye E to be examined at an intended position, and allows the measurement light LS to enter the eye E through the transmission position. The data of the subject's eye E can be obtained by As a result, it is possible to shorten the time required for photographing and measuring while ensuring the accuracy and accuracy of photographing and measurement.

In addition, the examiner visually recognizes the image 700 of the anterior segment Ea of the eye to be examined E displayed on the display unit 241 by viewing the display unit 241, and the measurement light LS passing through the anterior segment Ea is You can check the transmission position. Therefore, the transmission position at which the measurement light LS is transmitted through the anterior segment Ea of the eye to be examined E can be set more reliably than the intended position, and the measurement light LS is made incident on the inside of the eye to be examined E through the transmission position. The data of the eye examination E can be obtained more reliably.

Further, the data processing unit 230 identifies the projection direction of the measurement light LS based on the arrangement of the optical system that collects the OCT data, and also determines the measurement light LS based on the transmission position of the measurement light LS and the projection direction of the measurement light LS. specifies the reaching position where reaches the fundus Ef of the eye E to be examined. Then, the display control unit 2102 causes the display unit 241 to further display the image RP representing the arrival position specified by the data processing unit 230 so as to be superimposed on the image 500 of the fundus oculi Ef. Therefore, by visually recognizing the display unit 241, the examiner can confirm the reaching position of the measuring light LS reaching the fundus Ef of the eye E to be examined in the image 500 of the fundus oculi Ef. Therefore, the examiner sets the transmission position where the measurement light LS passes through the anterior segment Ea of the eye E to be examined to an intended position, and confirms the arrival position where the measurement light LS reaches the fundus oculi Ef of the eye E to be examined. be able to. As a result, it is possible to shorten the time required to capture the image 500 of the fundus oculi Ef while ensuring accuracy and accuracy.

Further, by viewing the display unit 241, the examiner can confirm the arrival position of the measurement light LS reaching the fundus Ef of the eye E to be examined in the three-dimensional scan image 500B of the fundus Ef. As a result, it is possible to shorten the time required to capture the three-dimensional scan image 500B of the fundus oculi Ef while ensuring accuracy and accuracy.

By visually recognizing the display unit 241, the examiner can view the trajectory of the arrival position of the measuring light LS at the fundus oculi Ef of the eye to be examined E by the optical coherence tomography scanning on the image 500 of the fundus oculi Ef or the three-dimensional image of the fundus oculi Ef. It can be confirmed in the scanned image 500B. As a result, the OCT scan of the three-dimensional region of the fundus oculi Ef of the eye to be examined E can be performed in a reduced time while ensuring accuracy and precision.

Further, by visually recognizing the display unit 241, the examiner can easily grasp the opacified region in the anterior segment Ea of the eye E to be examined, and the measurement light LS is transmitted through the anterior segment Ea of the eye E to be examined. It is possible to set a position that avoids the opaque area while confirming the transmission position to be used. As a result, it is possible to improve the precision and accuracy of photographing and measurement, and to shorten the time required for photographing and measurement.

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.

1: Ophthalmic device 2: Fundus camera unit 3: Display device 10: Illumination optical system 11: Observation light source 12: Concave mirror 13: Condensing lens 14: Visible cut filter 15: Photographing light source 16: Mirror 17: Relay lens system 18: Relay lens 19: Diaphragm 20: Relay lens 21: Perforated mirror 22: Objective lens 30: Shooting optical system 31: Shooting focusing lens 32: Mirror 33: Dichroic mirror 33A: Half mirror 34: Imaging lens 35: Image sensor 36: Mirror 37: Imaging lens 38: Image sensor 39: LCD 40: Collimator lens unit 41: Retro reflector 41A: Retroreflector driving section 42: Dispersion compensating member 43: OCT focusing lens 43A: OCT focusing driving section 44: Optical scanner 45: Relay lens 46: Dichroic mirror 50: Alignment optical system 51: Light Emitting Diode 52, 53: Diaphragm 54: Relay Lens 55: Dichroic Mirror 60: Focusing Optical System 61: LED 62: Relay Lens 63: Split Index Plate 64: Double Aperture Diaphragm 65: Mirror 66: Condensing lens 67: Reflecting bar 70, 71: Dioptric correction lens 100: OCT unit 101: Light source unit 102: Optical fiber 103: Polarization controller 104: Optical fiber 105: Fiber coupler 110: Optical fiber 111: Collimator 112: Optical path length correction member 113: Dispersion compensator 114: Retroreflector 114A: Retroreflector driver 116: Collimator 117: Optical fiber 118: Polarized wave Controller 119: Optical fiber 120: Attenuator 121: Optical fiber 122: Fiber coupler 123, 124: Optical fiber 125: Detector 127, 128: Optical fiber 130: Data acquisition system 150: Moving mechanism 200: Arithmetic control unit 210: Control unit 211: Main control unit 212: Storage unit 220: Image forming unit 230: Data processing unit 231: Position information acquisition unit 232: Judging unit 233: Turbidity Area identification unit 234: Movement target determination unit 236: Transmission position identification unit 237: Arrival position identification unit 240: User -interface 241: display unit 242: operation unit 250: data acquisition unit 260: alignment system 300: anterior eye camera 300A, 300B: anterior eye camera 400: anterior eye OCT attachment 410 : base 420: housing 430: lens housing 440: support 500: fundus image 500A: B scan image 500B: three-dimensional scan image 500C: B scan image 501C: image representing measurement light , 510, 510B: image representing opacified region 700: OCT front image 710: image representing opacified region 2101: drive control unit 2102: display control unit E: eye to be examined Ea: anterior segment Ef: fundus KC: clock L0: light LC: interference light LR: reference light LS: measurement light P: center of pupil RP: image representing arrival position RPT: image representing trajectory TP: transmission position image to represent

Claims (6)

An ophthalmic device for optically acquiring data of an eye to be examined,
a data acquisition unit having an optical system for projecting at least part of light from a light source as measurement light onto the eye to be inspected and applying optical coherence tomography scanning to a three-dimensional region of the eye to be inspected to acquire OCT data;
a data processing unit that specifies a transmission position where the measurement light passes through the anterior segment of the eye to be inspected based on the arrangement of the optical system;
a display control unit that causes a display unit to display an image representing the transmission position specified by the data processing unit so as to be superimposed on the image of the subject's eye;
An ophthalmologic device comprising: 2. The ophthalmologic apparatus according to claim 1, wherein the display control unit causes the display unit to display the image representing the transmission position specified by the data processing unit so as to be superimposed on the image of the anterior segment. The data processing unit specifies a projection direction of the measurement light based on the arrangement of the optical system, and determines a reaching position where the measurement light reaches the fundus of the subject's eye based on the transmission position and the projection direction. further specify,
3. The ophthalmologic apparatus according to claim 2, wherein the display control unit causes the display unit to further display the image representing the reaching position specified by the data processing unit so as to be superimposed on the image of the fundus. The display control unit causes the display unit to further display an image representing the arrival position specified by the data processing unit, superimposed on the three-dimensional scan image of the fundus acquired by the data acquisition unit. The ophthalmic device according to claim 3. 3. The display control unit causes the display unit to display an image representing a locus obtained by the optical coherence tomography scanning of the arrival position specified by the data processing unit, superimposed on the image of the fundus oculi. 5. The ophthalmic device according to 3 or 4. The data processing unit analyzes the OCT data to further identify the opacified region of the anterior segment,
6. The display controller according to any one of claims 1 to 5, wherein the display controller superimposes the image representing the opacity region identified by the data processor on the image of the subject's eye and further displays the image on the display unit. 10. An ophthalmic device according to claim 1.

Images