JP2023066499A - Ophthalmologic information processing device, ophthalmologic device, ophthalmologic information processing method, and program - Google Patents

Abstract

To provide a new technology to specify a change in a form of a tissue of an eye to be examined.SOLUTION: An ophthalmologic information processing device includes a layer thickness specification unit and a feature position specification unit. The layer thickness specification unit specifies the layer thickness in an A scan direction in a predetermined layer region in a measurement part on the basis of OCT data on the eye to be examined. The feature position specification unit specifies a feature position of an amount of change in the layer thickness in a direction intersecting with the A scan direction on the basis of the layer thickness specified by the layer thickness specification unit.SELECTED DRAWING: Figure 6

Description

The present invention relates to an ophthalmic information processing apparatus, an ophthalmic apparatus, an ophthalmic information processing method, and a program.

In recent years, attention has been focused on OCT, which uses a light beam from a laser light source or the like to form an image representing the surface morphology and internal morphology of an object to be measured. Since OCT is not invasive to the human body like X-ray CT (Computed Tomography), it is expected to be applied particularly in the medical and biological fields. For example, in the field of ophthalmology, apparatuses for forming images of the fundus, cornea, etc. have been put to practical use. A device using such an OCT technique (OCT device) can be applied to observe various parts of the subject's eye, and can acquire high-definition images, so it is applied to the diagnosis of various ophthalmic diseases. .

2. Description of the Related Art For wide-range observation of the fundus or screening of eye diseases, there is a demand for an apparatus capable of simply photographing or measuring the fundus of an eye to be examined in a wide field of view. For example, Patent Literature 1 discloses a configuration of an ophthalmologic apparatus for acquiring wide-angle OCT data.

JP 2019-025255 A

If it becomes possible to obtain wide-angle OCT data of an eye to be inspected, it will be possible to observe changes in the morphology of the tissue of the eye to be inspected in detail over a wide range. As a result, it becomes possible to easily identify various changes in the morphology of tissue, which were difficult to identify when it was impossible to obtain OCT data of the subject's eye at a wide angle.

Such a method of identifying changes in tissue morphology can be applied to OCT data of an eye to be examined regardless of whether the imaging angle of view (measurement range) is wide.

The present invention has been made in view of such circumstances, and one of its purposes is to provide a new technique for identifying changes in the morphology of tissue in an eye to be examined.

One aspect of the embodiment includes a layer thickness specifying unit that specifies a layer thickness in the A-scan direction of a predetermined layer region in a measurement site based on OCT data of an eye to be examined, and the layer specified by the layer thickness specifying unit. an ophthalmologic information processing apparatus, comprising: a feature position specifying unit that specifies a feature position of the amount of change in the layer thickness in a direction intersecting the A-scan direction based on the thickness.
Another aspect of the embodiment is an OCT optical system that includes an optical scanner and acquires the OCT data by projecting measurement light deflected by the optical scanner onto the eye to be examined, and the ophthalmologic information processing apparatus; An ophthalmic device comprising:
Still another aspect of the embodiment is a layer thickness specifying step of specifying a layer thickness in the A-scan direction of a predetermined layer region in a measurement site based on OCT data of an eye to be examined, and the layer thickness specified in the layer thickness specifying step and a characteristic position identifying step of identifying a characteristic position of the amount of change in the layer thickness in a direction intersecting the A-scan direction based on the layer thickness.
Yet another aspect of the embodiments is a program that causes a computer to execute each step of the ophthalmologic information processing method described above.

ADVANTAGE OF THE INVENTION According to this invention, the new technique for identifying the morphological change of the structure|tissue of an eye to be examined can be provided.

It is a schematic diagram showing an example of the configuration of the optical system of the ophthalmologic apparatus according to the embodiment. It is a schematic diagram showing an example of the configuration of the optical system of the ophthalmologic apparatus according to the embodiment. 1 is a schematic diagram showing an example of a configuration of a processing system of an ophthalmologic apparatus according to an embodiment; FIG. 1 is a schematic diagram showing an example of a configuration of a processing system of an ophthalmologic apparatus according to an embodiment; FIG. 1 is a schematic diagram showing an example of a configuration of a processing system of an ophthalmologic apparatus according to an embodiment; FIG. 1 is a schematic diagram showing an example of a configuration of a processing system of an ophthalmologic apparatus according to an embodiment; FIG. It is a schematic diagram for explaining the operation of the ophthalmologic apparatus according to the embodiment. It is a schematic diagram for explaining the operation of the ophthalmologic apparatus according to the embodiment. It is a schematic diagram for explaining the operation of the ophthalmologic apparatus according to the embodiment. It is a schematic diagram for explaining the operation of the ophthalmologic apparatus according to the embodiment. FIG. 4 is a flow diagram of an operation example of the ophthalmologic apparatus according to the embodiment; FIG. 4 is a flow diagram of an operation example of the ophthalmologic apparatus according to the embodiment; FIG. 4 is a flow diagram of an operation example of the ophthalmologic apparatus according to the embodiment; FIG. 4 is a flow diagram of an operation example of the ophthalmologic apparatus according to the embodiment; It is a schematic diagram showing an example of a configuration of a processing system of an ophthalmologic apparatus according to a modification of the embodiment. FIG. 7 is a schematic diagram for explaining processing executed by an ophthalmologic apparatus according to a comparative example of the embodiment; It is a schematic diagram showing an example of a configuration of a processing system of an ophthalmologic apparatus according to a modification of the embodiment. It is a schematic diagram for explaining the operation of the ophthalmologic apparatus according to the modification of the embodiment. It is a schematic diagram for explaining the operation of the ophthalmologic apparatus according to the modification of the embodiment. FIG. 11 is a flow diagram of an operation example of an ophthalmologic apparatus according to a modification of the embodiment; It is a schematic diagram for explaining the operation of the ophthalmologic apparatus according to the modification of the embodiment. It is a schematic diagram for explaining the operation of the ophthalmologic apparatus according to the modification of the embodiment.

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

Changes in the morphology of tissue in the eye to be examined are considered useful for early detection and diagnosis of diseases (ocular diseases). For example, if morphological changes in a given tissue can be identified or detected with high accuracy, early detection and diagnosis of diseases may be possible before morphological changes specific to the disease occur.

The ophthalmologic information processing apparatus according to the embodiment can specify the feature position of the layer thickness change amount by focusing on the layer thickness change amount of a predetermined layer region in the measurement site of the subject's eye.

Examples of measurement sites include the fundus and the anterior segment of the eye. Examples of layer regions include a layer region that constitutes the retina, a layer region that constitutes the vitreous body, the lens, the anterior chamber, the cornea, and a tissue region that constitutes the anterior segment of the eye. Examples of layers that make up the retina include the inner limiting membrane, nerve fiber layer, ganglion cell layer, inner reticular layer, inner nuclear layer, outer reticular layer, outer nuclear layer, outer limiting membrane, photoreceptor layer, and retinal pigment layer. It contains cortex, Bruch's membrane, choroid, and sclera. Corneal epithelial cells, basement membrane, Bowman's membrane, stromal layer, Descemet's membrane, and endothelial cells are examples of layer regions that constitute the cornea. Examples of regions of tissue that make up the anterior segment are Schlemm's canal, iris, ciliary body, and angle.

Specifically, the ophthalmologic information processing apparatus according to the embodiment specifies the layer thickness in the A-scan direction of a predetermined layer region in the measurement site based on the OCT data of the eye to be examined. The ophthalmologic information processing apparatus identifies the feature position of the amount of change in layer thickness in the direction intersecting the A-scan direction (for example, the B-scan direction) based on the identified layer thickness.

The OCT data is obtained, for example, by dividing light from an OCT light source into measurement light and reference light, projecting the measurement light onto the eye to be inspected, returning light of the measurement light from the eye to be inspected, and reference light passing through the reference light path. It is obtained by detecting interfering light. The OCT data may be two-dimensional OCT data or three-dimensional OCT data. In some embodiments, the ophthalmic information processing device is configured to acquire OCT data obtained by an externally provided OCT device. In some embodiments, the functionality of the ophthalmic information processing device is implemented by an ophthalmic device capable of acquiring OCT data.

In some embodiments, the ophthalmologic information processing apparatus performs disease risk determination and generates a risk determination result based on the amount of change in layer thickness at the specified feature position. Examples of diseases include Central Serous Chorioretinopathy (CSC), severe myopia, Age-related Macular Degeneration (AMD), glaucoma, and other choroidal diseases.

In some embodiments, the ophthalmic information processing apparatus generates a layer thickness variation profile that represents a layer thickness variation along an A-scan cross direction (e.g., a B-scan direction), and compares the generated layer thickness variation The volume profile is displayed on the display means. At this time, the ophthalmologic information processing apparatus causes the display means to display information indicating the position corresponding to the characteristic position in the layer thickness variation profile, or displays information indicating the variation in the characteristic position in the layer thickness variation profile to the display means. It is possible to display In some embodiments, the ophthalmologic information processing apparatus causes the display means to display a layer thickness variation profile and a tomographic image of an eye to be examined formed based on OCT data, and displays a position corresponding to a characteristic position in the tomographic image. The information to be displayed is displayed on the display means.

This makes it possible to identify (detect) changes in the morphology of the tissue of the subject's eye with high accuracy. As a result, it has become possible to determine the risk of a disease even when the morphological changes peculiar to the disease are not remarkable, and to continuously and in detail observe morphological changes as areas of interest in the future. can enable early detection and early treatment of

An ophthalmologic information processing method according to an embodiment includes one or more steps executed by the ophthalmologic information processing apparatus described above. A program according to an embodiment causes a computer (processor) to execute each step of an ophthalmologic information processing method according to an embodiment. A recording medium according to the embodiment is a non-temporary recording medium (storage medium) in which the program according to the embodiment is recorded.

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

Hereinafter, mainly, the case of determining the risk of CSC from the amount of change in the thickness of the choroid and facilitating the identification of the characteristic position of the amount of change in the thickness of the choroid will be described, but the configuration according to the embodiment is this. is not limited to CSC is a disease in which serous retinal detachment occurs in the macula, causing symptoms such as decreased visual acuity and central darkening.

Moreover, the following embodiments are also applicable to the amount of change in the thickness of layer regions other than the choroid. Moreover, the following embodiments are also applicable to eye diseases other than CSC.

In the following embodiments, an ophthalmologic apparatus including the functions of the ophthalmologic information processing apparatus according to the embodiment will be described as an example. An ophthalmologic apparatus according to an embodiment includes an ophthalmologic imaging apparatus. The ophthalmic imaging device included in the ophthalmic device of some embodiments is, for example, any one or more of a fundus camera, a scanning optical ophthalmoscope, a slit lamp ophthalmoscope, a surgical microscope, or the like. An ophthalmic device according to some embodiments includes any one or more of an ophthalmic measurement device and an ophthalmic treatment device in addition to an ophthalmic imaging device. The ophthalmic measurement device included in the ophthalmic device of some embodiments is, for example, any one or more of an eye refractor, a tonometer, a specular microscope, a wavefront analyzer, a perimeter, a microperimeter, etc. . The ophthalmic treatment device included in the ophthalmic device of some embodiments is, for example, any one or more of a laser treatment device, a surgical device, a surgical microscope, and the like.

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

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

<Configuration>
〔Optical system〕
As shown in FIG. 1 , the ophthalmologic apparatus 1 includes a fundus camera unit 2 , an OCT unit 100 and an arithmetic control unit 200 . The retinal camera unit 2 is provided with an optical system and a mechanism for acquiring a front image of the eye E to be examined. The OCT unit 100 is provided with a part of an optical system and a mechanism for performing OCT. Another part of the optical system and mechanism for performing OCT is provided in the fundus camera unit 2 . The arithmetic control unit 200 includes one or more processors that perform various arithmetic operations and controls. In addition to these, arbitrary elements such as a member for supporting the subject's face (chin rest, forehead rest, etc.) and a lens unit for switching the target part of OCT (for example, attachment for anterior segment OCT) or unit may be provided in the ophthalmologic apparatus 1 . Furthermore, the ophthalmologic apparatus 1 includes a pair of anterior eye cameras 5A and 5B.

In some embodiments, ophthalmic device 1 includes display device 3 . The display device 3 displays processing results (for example, OCT images, etc.) by the arithmetic control unit 200, images obtained by the retinal camera unit 2, operation guidance information for operating the ophthalmologic apparatus 1, and the like.

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

The 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 illumination light from the eye E to be examined. The measurement light from the OCT unit 100 is guided to the subject's eye E through the optical path in the retinal camera unit 2, and its return light is guided to the OCT unit 100 through the same optical path.

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

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

An image (observation image) based on the fundus reflected light detected by the image sensor 35 is displayed on the display device 3 . Note that when the imaging optical system 30 is focused on the anterior segment, an observation image of the anterior segment of the subject's eye E is displayed. The display device 3 also displays an image (captured image, spectral fundus image) based on the fundus reflected light detected by the image sensor 38 . The display device 3 that displays the observed image and the display device 3 that displays the captured image may be the same or different. When the subject's eye E is illuminated with infrared light and photographed in the same manner, an infrared photographed image is displayed.

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

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

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

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

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

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

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

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

[Anterior segment cameras 5A and 5B]
The anterior eye cameras 5A and 5B are used to determine the relative position between the optical system of the ophthalmologic apparatus 1 and the subject's eye E, for example, in the same manner as the method described in Japanese Patent Application Laid-Open No. 2013-248376. The anterior eye cameras 5A and 5B are provided on the face of the subject's eye E side of a housing (fundus camera unit 2, etc.) housing an optical system. The ophthalmologic apparatus 1 analyzes two anterior segment images obtained substantially simultaneously from different directions by the anterior segment cameras 5A and 5B, thereby determining the three-dimensional relative relationship between the optical system and the subject's eye E. find the position. The analysis of the two anterior segment images may be similar to the analysis disclosed in Japanese Patent Application Laid-Open No. 2013-248376. Also, the number of anterior segment cameras may be any number of two or more.

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

[OCT unit 100]
As illustrated in FIG. 2, the OCT unit 100 is provided with an optical system for performing swept-source OCT. This optical system includes an interference optical system. This interference optical system has a function of dividing light from a wavelength tunable light source (wavelength swept light source) into measurement light and reference light, return light of the measurement light from the subject's eye E, and reference light passing through the reference light path. and a function of generating interference light and a function of detecting this interference light. A detection result (detection signal) of the interference light obtained by the interference optical system is a signal indicating the spectrum of the interference light, and is sent to the arithmetic control unit 200 .

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

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

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

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

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

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

A clock KC is supplied from the light source unit 101 to the DAQ 130 . The clock KC is generated in the light source unit 101 in synchronization with the output timing of each wavelength swept within a predetermined wavelength range by the wavelength tunable light source. The light source unit 101, for example, optically delays one of the two branched lights obtained by branching the light L0 of each output wavelength, and then outputs the clock KC based on the result of detecting these combined lights. Generate. The DAQ 130 samples the detection signal input from the detector 125 based on the clock KC. DAQ 130 sends the sampling result of the detection signal from detector 125 to arithmetic control unit 200 .

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

[Processing system]
3 to 6 show configuration examples of the processing system of the ophthalmologic apparatus 1. FIG. 3 to 6, some of the components included in the ophthalmologic apparatus 1 are omitted. In FIG. 3, the same parts as those in FIGS. 1 and 2 are denoted by the same reference numerals, and description thereof will be omitted as appropriate. 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 executes various controls. Control unit 210 includes main control unit 211 and storage unit 212 .

<Main control unit 211>
The main controller 211 includes a processor (eg, control processor) and controls each part of the ophthalmologic apparatus 1 (including each element shown in FIGS. 1 to 6). For example, the main control unit 211 controls each part of the optical system of the retinal camera unit 2 shown in FIGS. It controls mechanism 150 , image forming section 220 , data processing section 230 and user interface (UI) 240 .

The control over the retinal camera unit 2 includes control over the focus driving units 31A and 43A, control over the image sensors 35 and 38, control over the LCD 39, control over the optical path length changing unit 41, and control over the optical scanner 42.

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

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

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

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

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

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

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

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

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

Control of the detector 125 includes control of the light receiving sensitivity of the detection element, control of the frame rate (light receiving timing), control of the light receiving area (position, size, size), control of readout of the light receiving result of the detection element, and the like.

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

Control of the anterior eye cameras 5A and 5B includes control of the light receiving sensitivity of each camera, frame rate (light receiving timing) control, synchronization control of the anterior eye cameras 5A and 5B, and the like.

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

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

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

In the case of auto-alignment, the main control unit 211 controls the movement mechanism 150 so that the displacement of the eye E to be inspected with respect to the optical system is canceled so that the optical system is relatively moved with respect to the eye E to be inspected. Specifically, as described in JP-A-2013-248376, arithmetic processing using trigonometry based on the positional relationship between the pair of anterior eye cameras 5A and 5B and the subject's eye E is performed, and the main control unit A reference numeral 211 controls the moving mechanism 150 so that the eye to be examined E has a predetermined positional relationship with respect to the optical system. In some embodiments, the main controller 211 outputs a control signal such that the optical axis of the optical system substantially coincides with the axis of the eye E to be examined and the distance of the optical system from the eye E to be examined is a predetermined working distance. to the moving mechanism 150 to control the moving mechanism 150 to move the optical system relative to the eye E to be examined. Here, the working distance is a default value also called a working distance of the objective lens 22, and corresponds to the distance between the subject's eye E and the optical system at the time of measurement (at the time of photographing) using the optical system.

The main controller 211 also includes a display controller 211A. The display control unit 211A can display various information on the display unit 240A. For example, the display control unit 211A controls the fundus image or the anterior segment image acquired using the retinal camera unit 2, the tomographic image or front image (OCT image) acquired using the OCT unit 100, or the data processing described later. The data processing result (analysis processing result) obtained by the unit 230 is displayed on the display unit 240A. Examples of data processing results include a layer thickness change amount profile indicating the amount of change in the layer thickness of the choroid, information indicating characteristic positions in the layer thickness change amount profile, and a layer thickness change amount at the characteristic positions in the layer thickness change amount profile. There is information indicating In some embodiments, the display control unit 211A causes the display unit 240A to display the data processing result in association with at least one of the fundus image (or the anterior segment image) and the OCT image.

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

The storage unit 212 also stores risk determination information 212A. The risk determination information 212A is information for determining the risk of CSC (disease). Examples of CSC risk include whether or not to have CSC (disease) (presence or absence of disease) and the probability of having CSC (likelihood of disease). As an example of the risk determination information 212A, standard data (reference data, statistical data) in which CSC risk information is associated in advance with the amount of change in the feature position of the choroid layer thickness change amount profile for a plurality of eyes to be examined (Normative Data) There is

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

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

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

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

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

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

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

As shown in FIG. 4 , data processing section 230 includes alignment processing section 250 and risk determination processing section 260 . The alignment processing unit 250 performs processing for aligning the optical system of the ophthalmologic apparatus 1 with respect to the eye E to be examined. The risk determination processing unit 260 executes processing for determining the risk of CSC.

<Alignment processing unit 250>
As shown in FIG. 5 , the alignment processing section 250 includes a characteristic part identifying section 251 and a three-dimensional position calculating section 252 . The alignment processing unit 250 obtains the three-dimensional position of the subject's eye E based on the positions of the anterior eye cameras 5A and 5B and the positions of the characteristic regions. The main control unit 211 moves the optical system relative to the eye E to be examined by controlling the moving mechanism 150 based on the obtained three-dimensional position, and aligns the optical system with the eye E to be examined.

<Characteristic part identification unit 251>
The characteristic site identification unit 251 analyzes each captured image obtained by the anterior segment cameras 5A and 5B to identify a position (referred to as a characteristic position) in the captured image corresponding to the characteristic site of the anterior segment Ea. Identify. For example, the pupil region of the subject eye E, the pupil center position of the subject eye E, the pupil center position, the corneal center position, the corneal vertex position, the subject eye center position, or the iris are used as the characteristic site. A specific example of processing for specifying the pupil center position of the eye E to be examined will be described below.

First, the characteristic site identification unit 251 identifies an image region (pupil region) corresponding to the pupil of the subject's eye E based on the distribution of pixel values (such as luminance values) of the captured image. Since the pupil is generally drawn with lower luminance than other parts, the pupil region can be identified by searching for the low-luminance image region. At this time, the pupil region may be specified in consideration of the shape of the pupil. In other words, the pupil region can be identified by searching for a substantially circular low-brightness image region.

Next, the characteristic part identifying section 251 identifies the central position of the identified pupil region. Since the pupil is substantially circular as described above, it is possible to specify the outline of the pupil region, specify the center position of this outline (the approximate circle or approximate ellipse), and set this as the pupil center position. Alternatively, the center of gravity of the pupil region may be obtained and the position of the center of gravity may be specified as the position of the center of gravity of the pupil.

It should be noted that even when specifying a characteristic position corresponding to another characteristic part, it is possible to specify the characteristic position based on the distribution of pixel values of the captured image in the same manner as described above.

The characteristic part identifying unit 251 can sequentially identify characteristic positions corresponding to the characteristic parts in the captured images sequentially obtained by the anterior eye cameras 5A and 5B. Further, the characteristic part identification unit 251 may identify the characteristic position every one or more frames of the captured images sequentially obtained by the anterior eye cameras 5A and 5B.

<Three-dimensional position calculator 252>
The three-dimensional position calculation unit 252 calculates the three-dimensional positions of the characteristic regions of the subject's eye E based on the positions of the anterior eye cameras 5A and 5B and the characteristic positions corresponding to the characteristic regions identified by the characteristic region identification unit 251. Identify as a three-dimensional position. The three-dimensional position calculation unit 252, as disclosed in Japanese Unexamined Patent Application Publication No. 2013-248376, calculates the positions of the two anterior eye cameras 5A and 5B (which are known) and the characteristic regions in the two captured images. The three-dimensional position of the subject's eye E is calculated by applying a known trigonometric method to the position where the eye E is to be examined. The three-dimensional position calculated by the three-dimensional position calculator 252 is sent to the main controller 211 . Based on the three-dimensional position, the main control unit 211 determines that the x- and y-direction positions of the optical axis of the optical system match the x- and y-direction positions of the three-dimensional position, and that the z-direction distance is The moving mechanism 150 is controlled so as to achieve a predetermined working distance.

<Risk determination processing unit 260>
As shown in FIG. 6, the risk determination processing unit 260 includes a layer area specifying unit 261, a layer thickness specifying unit 262, a characteristic position specifying unit 263, a layer thickness change amount profile generating unit 264, and a risk determining unit 265. including. The feature position specifying section 263 includes a moving average processing section 2631 and a maximum value specifying section 2632 .

<Layer area specifying unit 261>
The layer region identifying unit 261 identifies a predetermined layer region based on OCT data obtained by performing OCT on the eye E to be examined. Examples of layer regions include the inner limiting membrane, nerve fiber layer, ganglion cell layer, inner plexiform layer, inner nuclear layer, outer plexiform layer, outer nuclear layer, outer limiting membrane, photoreceptor layer, retinal pigment epithelium layer, and Bruch's membrane. , choroid, and sclera.

In some embodiments, the layer area identifying section 261 identifies a predetermined layer area based on the intensity of the interference signal obtained by detecting the interference light. For example, the layer area identifying unit 261 identifies a position indicating an extreme value (maximum value) of the intensity of the interference signal as a position corresponding to the boundary position of the layer area, and uses the position indicating the maximum value of the intensity of the interference signal as a reference. Identify the above layer regions.

In some embodiments, the layer region identifying section 261 identifies a predetermined layer region based on the tomographic image of the fundus oculi Ef formed by the image forming section 220 . For example, the layer region identifying unit 261 identifies the boundary candidate position of the layer region in the fundus oculi Ef from the intensity difference (luminance value difference, pixel value difference) of two or more adjacent pixels in the tomographic image. At this time, the layer region specifying unit 261 binarizes the first boundary candidate position obtained by binarizing the intensity difference with the first threshold and the intensity difference with the second threshold higher than the first threshold. A second boundary candidate position obtained by the above is identified. The first boundary candidate position is a boundary candidate position identified in a state containing many noise components. The second boundary candidate position is a boundary candidate position where there is a possibility that part of the part required as the boundary position of the layer region is lost. Note that the layer region identifying unit 261 removes a portion unrelated to the boundary based on the intensity gradient (brightness gradient) from the plurality of boundary candidate positions of the layer region identified from the intensity difference, and then removes the first boundary candidate position and the first boundary candidate position. It is possible to identify two boundary candidate locations. The layer region identifying unit 261 identifies those of the first boundary candidate positions that are connected to the second boundary candidate positions as boundary positions of the layer region. The layer area identifying unit 261 identifies the area between the two identified boundary positions as a layer area.

In this embodiment, the layer region identifying unit 261 identifies the boundary position corresponding to Bruch's membrane and the boundary position corresponding to the Chorio-Scleral Interface (CSI) interface, and the identified 2 Identify the choroid from one boundary location.

<Layer thickness specifying unit 262>
The layer thickness specifying unit 262 specifies the layer thickness in the A scan direction of the layer region specified by the layer region specifying unit 261 . For example, the layer thickness identifying unit 262 identifies the distance in the A-scan direction between the two identified boundary positions as the layer thickness of the layer region between the two boundary positions.

In this embodiment, the layer thickness specifying unit 262 specifies the distance in the A-scan direction between the boundary position corresponding to Bruch's membrane and the boundary position corresponding to CSI as the layer thickness (film thickness) of the choroid.

The layer thickness specifying unit 262 can sequentially specify the layer thickness of the choroid at the A-scan measurement positions (A-line positions) arranged in the B-scan direction. The A-scan measurement position is the A-line scan angle (A It is identified from the scan angle of the scan). The layer thickness specifying unit 262 can sequentially calculate the difference in layer thickness of A lines adjacent in the B scanning direction for each scanning angle of the A lines.

<Characteristic position specifying unit 263>
The feature position specifying unit 263 specifies the feature position of the amount of change in the layer thickness of the choroid in the B scan direction that intersects with the A scan direction.

As described above, the layer thickness specifying unit 262 specifies the layer thickness for each A-line scan angle.
Therefore, the characteristic position specifying unit 263 determines the amount of change in layer thickness based on the difference in the layer thickness of the A lines adjacent in the B scanning direction and the scan angle for each A line centered on the scan center position of the OCT scan. It is possible to identify the feature position of

Examples of characteristic positions include the position indicating the maximum value of the amount of change, the position indicating the minimum value of the amount of change, one or more positions indicating the maximum value of the amount of change, one or more positions indicating the minimum value of the amount of change, and the amount of change. Alternatively, there are one or more positions where the extreme value of the amount of change is greater than or equal to the threshold, one or more positions where the amount of change or the extreme value of the amount of change is less than or equal to the threshold. The one or more positions indicating the maximum value of the amount of change may be a plurality of high-ranking positions when arranging the maximum values in descending order. The one or more positions indicating the minimum value of the amount of change may be a plurality of lower positions when the minimum values are arranged in descending order.

<Moving average processing unit 2631>
The moving average processing unit 2631 smoothes the layer thicknesses (layer thickness data) of a plurality of A lines adjacent in the B scanning direction (intersecting direction of the A scanning direction) in the B scanning direction. As a result, it is possible to smooth the layer thickness profile data that is stepped in pixel units, and to calculate the extreme value described later with good reproducibility from the layer thickness profile data smoothed in the B scan direction (i.e. , can identify feature locations with high reproducibility).

Specifically, the moving average processing unit 2631 sequentially obtains a moving average of layer thicknesses of a plurality of A lines within a predetermined scanning angle range adjacent to the B scanning direction, thereby obtaining a layer thickness profile after smoothing. Generate. For example, the moving average processing unit 2631 calculates the average value of N (N is an integer equal to or greater than 2) layer thickness data adjacent to the B scan direction in the scan angle range of 0 degrees to 10 degrees, and the scan angle is Calculate the average value of N pieces of layer thickness data adjacent to the B scan direction in the range of 1 degree to 11 degrees, . . . A layer thickness profile is generated by calculating the average value of individual layer thickness data.

Smoothing of layer thickness data according to the embodiment is not limited to moving average processing. For example, the layer thickness data may be smoothed in the B-scan direction by spline interpolation or polynomial approximation.

<Maximum value specifying unit 2632>
The maximum value specifying unit 2632 specifies the position indicating the maximum value of the change amount of the choroidal layer thickness as the characteristic position indicating the maximum value of the choroidal change. In some embodiments, the maximum value specifying unit 2632 sequentially analyzes the layer thickness variation of each A line in the B scan direction to determine the position of the A line showing the maximum layer thickness variation. Identify as feature locations.

In some embodiments, the maximum value specifying unit 2632 specifies the maximum value of the change amount for each of a plurality of A-line ranges arranged in the B scan direction, and determines the change amount from the specified maximum values. The position of the A line showing the maximum value is identified as the feature position.

In some embodiments, maximum value identifier 2632 identifies the maximum value of layer thickness variation in the B-scan direction within a given A-line. The predetermined A-line range may be a predetermined range, a range specified by the data processing unit 230, or a range specified using the operation unit 240B described later. Examples of the range specified by the data processing unit 230 include a range determined based on the characteristic site (eg, the macula) of the eye E to be examined (eg, a range including the characteristic site, a predetermined distance away from the characteristic site). range).

<Layer thickness change amount profile generator 264>
Based on the layer thickness specified by the layer thickness specifying unit 262, the layer thickness change amount profile generation unit 264 creates a layer thickness change amount representing the amount of change in the layer thickness along the B scan direction (intersecting direction of the A scan direction). Generate a profile. That is, the layer thickness change amount profile generation unit 264 generates the layer thickness change amount profile by sequentially calculating the difference in the layer thicknesses of the A lines adjacent in the B scanning direction for each scanning angle of the A line.

In some embodiments, the feature locations of the layer thickness variation are identified based on the layer thickness variation profile generated by the layer thickness variation profile generator 264 .

7 and 8 show an example of the layer thickness variation profile according to the embodiment. FIG. 7 schematically represents a layer thickness change amount profile in a normal eye. FIG. 8 schematically represents a layer thickness variation profile in a CSC eye.

FIG. 7 schematically shows an example in which the layer thickness change amount profile is displayed on the display unit 240A in association with the tomographic image IMG1 of the normal eye. That is, the position of the A line in the tomographic image IMG1 is displayed so as to coincide with the position of the A line in the layer thickness variation profile in the vertical direction. In FIG. 7, the horizontal axis of the characteristic graph showing the layer thickness change amount profile etc. represents the pixel position (A line position, A scan position) of the tomographic image corresponding to the scan angle (imaging angle of view). The vertical axis represents thickness, and the right vertical axis represents layer thickness variation.

When OCT is performed on the eye to be examined, which is a normal eye, and OCT data is acquired, the layer region specifying unit 261 specifies the choroid as described above using the acquired OCT data. The layer thickness specifying unit 262 specifies the layer thickness of the choroid in the A-scan direction specified by the layer area specifying unit 261 as described above. By specifying the layer thickness for each pixel position, a layer thickness profile T1 of the choroid as shown in FIG. 7 is obtained.

The moving average processing unit 2631 sequentially obtains the moving average of the layer thickness of a plurality of A lines within a scanning angle range of 10 degrees adjacent to the B scanning direction for the layer thickness profile T1. to generate a layer thickness profile T2 of

The maximum value identifying unit 2632 analyzes the layer thickness profile T2 over the entire range from pixel position 0 to pixel position 2047 to identify the maximum value of the amount of change in layer thickness. The characteristic position identifying section 263 identifies the position indicating the maximum value identified by the maximum value identifying section 2632 as the characteristic position P1 indicating the maximum choroidal change value.

The layer thickness change amount profile generation unit 264 generates a layer thickness change amount profile T3 by obtaining a difference in layer thickness between adjacent A lines with respect to the layer thickness profile T2 after the moving average process.

As shown in FIG. 7, the display control unit 211A causes the display unit 240A to display a triangular mark (information) indicating the position corresponding to the characteristic position P1 in the layer thickness change amount profile T3. Further, the display control unit 211A displays information indicating the amount of change at the characteristic position P1 in the layer thickness change amount profile T3 (for example, information indicating a solid line segment, a dashed line segment, and a range) on the display unit 240A. Let In some embodiments, the display control unit 211A causes the display unit 240A to display information indicating the layer thickness at the feature position P1 in the layer thickness change amount profile T3.

FIG. 8 schematically shows an example in which the layer thickness change amount profile is displayed on the display unit 240A in association with the tomographic image IMG2 of the CSC eye (eye with CSC). That is, the position of the A line in the tomographic image IMG2 is displayed so as to coincide with the position of the A line in the layer thickness variation profile in the vertical direction. In FIG. 8, the horizontal axis of the characteristic graph showing the layer thickness change amount profile etc. represents the pixel position of the tomographic image corresponding to the scan angle, the left vertical axis represents the thickness, and the right vertical axis represents the layer thickness change. represent quantity.

When OCT is performed on the subject's eye, which is a CSC eye, and OCT data is obtained, the layer region identification unit 261 identifies the choroid as described above using the obtained OCT data. The layer thickness specifying unit 262 specifies the layer thickness of the choroid in the A-scan direction specified by the layer area specifying unit 261 as described above. By specifying the layer thickness for each pixel position, a choroid layer thickness profile T11 as shown in FIG. 8 is acquired.

The moving average processing unit 2631 sequentially obtains the moving average of the layer thickness of a plurality of A lines within a scanning angle range of 10 degrees adjacent to the B scanning direction for the layer thickness profile T11. to generate a layer thickness profile T12 of

The maximum value identifying unit 2632 analyzes the layer thickness profile T12 over the entire range from pixel position 0 to pixel position 2047 to identify the maximum value of the amount of change in layer thickness. The characteristic position identifying section 263 identifies the position indicating the maximum value identified by the maximum value identifying section 2632 as the characteristic position P2 indicating the maximum choroidal change value.

The layer thickness change amount profile generation unit 264 generates a layer thickness change amount profile T13 by obtaining a difference in layer thickness between adjacent A lines in the layer thickness profile T12 after the moving average process.

As shown in FIG. 8, the display control unit 211A causes the display unit 240A to display a triangular mark indicating the position corresponding to the characteristic position P2 in the layer thickness change amount profile T13. Further, the display control unit 211A displays information indicating the amount of change at the characteristic position P2 in the layer thickness change amount profile T13 (for example, information indicating a solid line segment, a broken line segment, and a range) on the display unit 240A. Let In some embodiments, the display control unit 211A causes the display unit 240A to display information indicating the layer thickness at the feature position P2 in the layer thickness change amount profile T13.

As shown in FIGS. 7 and 8, the feature positions are different between the normal eye and the CSC eye. This feature position difference can be a significant parameter (information) for identifying a CSC eye. Therefore, based on the feature positions, it is possible to identify areas of continuous interest and to determine the risk of CSC.

<Risk determination unit 265>
The risk determination unit 265 determines the risk of CSC (disease) based on the amount of change in layer thickness at characteristic positions of the layer thickness change amount profile. The risk determination unit 265 can refer to the risk determination information 212A to determine the risk of CSC.

FIG. 9 shows an overview of the configuration of risk determination information 212A according to the embodiment.

The risk determination information 212A is standard data (reference data, statistical data) in which risk information representing the risk of CSC is associated in advance with the layer thickness change amount at the characteristic position of the layer thickness change amount profile for a plurality of eyes to be examined. ). Specifically, in the risk determination information 212A, risk information RK1, RK2, . . . Associated table information. Each of the risk information RK1, RK2, . . . , RKn includes at least one of whether or not it is CSC (disease) (presence or absence of disease) and probability of being CSC (possibility of disease).

In some embodiments, risk determination information 212A is statistical data for multiple normal eyes. In some embodiments, risk determination information 212A is statistical data for multiple CSC eyes.

The risk determination unit 265 refers to the risk determination information 212A based on the layer thickness change amount (the maximum value of the layer thickness change amount specified by the maximum value specifying unit 2632) at the feature position specified by the feature position specifying unit 263. , to identify the risk information corresponding to the layer thickness variation. The risk determination unit 265 can generate a risk determination result including at least one of whether or not the subject's eye is CSC and the probability that the subject's eye is CSC from the specified risk information.

In some embodiments, the risk determination unit 265 refers to the risk determination information 212A based on the layer thickness change amount, and obtains two or more pieces of risk information corresponding to two or more layer thickness change amounts close to the layer thickness change amount. is specified, and one piece of risk information corresponding to the layer thickness change amount is generated from the specified two or more pieces of risk information.

In some embodiments, the risk determination unit 265, based on the amount of change in layer thickness of the choroid of the subject eye E at the feature position of the amount of change in layer thickness of the choroid, the statistical data for the plurality of normal eyes and the statistical data for the plurality of CSC eyes Based on the two pieces of risk information obtained by referring to each statistical data, the risk of CSC in the subject's eye E is determined.

In some embodiments, the risk determination information 212A includes a plurality of pieces of risk determination information corresponding to a plurality of distances to the feature location with reference to the feature site (eg, macula) in the fundus. In this case, the risk determination unit 265 identifies risk determination information corresponding to the distance between the characteristic site and the characteristic position from a plurality of pieces of risk determination information, and uses the identified risk determination information to correspond to the layer thickness change amount. It is possible to identify the risk information that

In some embodiments, the risk determination information 212A includes multiple pieces of risk determination information corresponding to multiple shooting angles of view. In this case, the risk determination unit 265 identifies risk determination information corresponding to the shooting angle of view from a plurality of pieces of risk determination information, and uses the identified risk determination information to identify risk information corresponding to the layer thickness change amount. is possible.

In some embodiments, the display control unit 211A causes the display unit 240A to display information corresponding to the risk information identified by the risk determination unit 265 as described above.

7 and 8, a case has been described in which the maximum value of the layer thickness change amount is used as the maximum value of the choroidal change to specify the feature position, but the embodiment is not limited to this. The feature position specifying unit 263 may specify the maximum value of the layer thickness change amount as the choroidal change maximum value for each of the plurality of pixel position ranges, and specify a plurality of feature positions indicating the specified choroidal change maximum value. .

FIG. 10 shows another example of the layer thickness profile according to the embodiment.

Similar to FIGS. 7 and 8, FIG. 10 schematically illustrates an example in which the layer thickness profile is displayed on the display unit 240A in association with the tomographic image IMG3 of the subject's eye. That is, the position of the A line in the tomographic image IMG3 is displayed so as to coincide with the position of the A line in the layer thickness profile in the vertical direction. In FIG. 10, the horizontal axis of the characteristic graph showing the layer thickness profile etc. represents the pixel position of the tomographic image corresponding to the scan angle, and the vertical axis represents the thickness.

When OCT is performed on the eye to be inspected and OCT data is acquired, the layer region specifying unit 261 specifies the choroid as described above using the acquired OCT data. The layer thickness specifying unit 262 specifies the layer thickness of the choroid in the A-scan direction specified by the layer area specifying unit 261 as described above. By specifying the layer thickness for each pixel position, a choroid layer thickness profile T31 as shown in FIG. 10 is acquired.

The moving average processing unit 2631 sequentially obtains the moving average of the layer thickness of a plurality of A lines within a scanning angle range of 10 degrees adjacent to the B scanning direction for the layer thickness profile T31. to generate a layer thickness profile T32 of

The feature position specifying unit 263 (maximum value specifying unit 2632) specifies the maximum value of the layer thickness variation in the B scan direction for each of three predetermined ranges from pixel position 0 to pixel position 2047. . The characteristic position identifying unit 263 identifies the positions indicating the maximum values identified by the maximum value identifying unit 2632 as characteristic positions P21, P31, and P41 indicating the maximum choroidal change values.

At least one of the three ranges may be specified by analyzing tomographic image IMG3 by data processing unit 230, or specified by the user using operation unit 240B.

The layer thickness change amount profile generation unit 264 generates a layer thickness change amount profile (not shown) by obtaining the difference in layer thickness between adjacent A lines in the layer thickness profile T32 after the moving average process. Is possible.

The display control unit 211A causes the display unit 240A to display information indicating positions corresponding to the characteristic positions P21, P31, and P41 in the layer thickness profiles T31 and T32.

In some embodiments, the display control unit 211A displays information (indices) representing layer thickness variation amounts at the characteristic positions P21, P31, and P41 of the layer thickness profiles T31 and T32 (for example, vertical line segments at the characteristic positions). is displayed on the display unit 240A. In this case, the display control unit 211A provides information (inclination of the tangent line at the characteristic position of the layer thickness profile) Q21 representing the gradient corresponding to the amount of change in the layer thickness at the characteristic positions P21, P31, and P41 of the layer thickness profiles T31 and T32, Q31 and Q41 are displayed on the display section 240A. In some embodiments, the information Q21, Q31, Q41 representing the tilt is displayed in a manner (color) according to the magnitude of the tilt. The greater the slope, the greater the amount of change in layer thickness. For example, the information Q21, Q31, and Q41 representing the tilt are displayed in such a manner that the greater the tilt, the more the user's attention is drawn to it. For example, the degree of suspicion of a CSC eye from a normal eye can be represented by the tilt angle and the color of the information representing the tilt.

In the above-described embodiment, the case where the maximum value of the choroidal layer thickness change amount is mainly specified as the choroidal change maximum value and the position indicating the choroidal change maximum value is specified has been described. is not limited to For example, the shape of the eyeball can be detected by determining whether the maximum choroidal change value and the position where the amount of change in the choroidal layer thickness is the second largest are located point-symmetrically with respect to the macula. , the presence or absence of a disease (or the probability of disease) caused by the shape of the eyeball can be estimated.

<User Interface 240>
As shown in FIG. 3, the user interface 240 includes a display section 240A and an operation section 240B. Display unit 240A includes display device 3 . The operation unit 240B includes various operation devices and input devices.

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

<Communication unit 280>
The communication unit 280 has a function for communicating with an external device (not shown). The communication unit 280 has a communication interface according to a connection form with an external device. Examples of external devices include server devices, OCT devices, scanning optical ophthalmoscopes, slit lamp ophthalmoscopes, ophthalmic measurement devices, and ophthalmic treatment devices. Examples of ophthalmic measurement devices include eye refractometers, tonometers, specular microscopes, wavefront analyzers, perimeters, microperimeters, and the like. Examples of ophthalmic treatment devices include laser treatment devices, surgical devices, surgical microscopes, and the like. The external device may be a device (reader) that reads information from a recording medium, or a device (writer) that writes information to a recording medium. Furthermore, the external device may be a hospital information system (HIS) server, a DICOM (Digital Imaging and Communication in Medicine) server, a doctor terminal, a mobile terminal, a personal terminal, a cloud server, or the like.

The arithmetic control unit 200 (the control section 210, the image forming section 220, and the data processing section 230) is an example of the "ophthalmic information processing apparatus" according to the embodiment. CSC is an example of a "disease" according to embodiments. The display unit 240A (display device 3) is an example of the "display unit" according to the embodiment. The moving average processing unit 2631 is an example of the "smoothing unit" according to the embodiment. The optical system from the OCT unit 100 to the objective lens 22 is an example of the "OCT optical system" according to the embodiment.

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

11 to 14 show operation examples of the ophthalmologic apparatus 1 according to the embodiment. FIG. 11 shows a flow diagram of an operation example of the ophthalmologic apparatus 1 that performs risk determination. FIG. 12 shows a flowchart of an operation example of the ophthalmologic apparatus 1 that performs the process of step S4 in FIG. FIG. 13 shows a flowchart of an operation example of the ophthalmologic apparatus 1 that performs the process of step S14 of FIG. FIG. 14 shows a flowchart of another operation example of the ophthalmologic apparatus 1 that performs the process of step S4 in FIG.

The storage unit 212 stores computer programs for realizing the processes shown in FIGS. The main control unit 211 executes the processes shown in FIGS. 11 to 14 by operating according to this computer program.

First, an operation example shown in FIG. 11 will be described.

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

For example, the main control unit 211 controls the LCD 39 to present the eye E to be examined with a fixation target for alignment. The main control unit 211 controls the anterior eye cameras 5A and 5B to photograph the anterior eye Ea of the subject's eye E substantially simultaneously. The characteristic site identification unit 251 receives control from the main control unit 211, analyzes a pair of anterior segment images obtained substantially simultaneously by the anterior segment cameras 5A and 5B, and determines the pupil of the subject's eye E as a characteristic site. Identify the center position. The three-dimensional position calculator 252 obtains the three-dimensional position of the eye E to be examined. This processing includes arithmetic processing using trigonometry based on the positional relationship between the pair of anterior eye cameras 5A and 5B and the subject's eye E, as described in Japanese Patent Application Laid-Open No. 2013-248376, for example.

The main control unit 211 moves based on the three-dimensional position of the subject's eye E obtained by the three-dimensional position calculator 252 so that the optical system (for example, the fundus camera unit 2) and the subject's eye E have a predetermined positional relationship. Control mechanism 150 . Here, the predetermined positional relationship is a positional relationship that enables imaging and examination of the subject's eye E using an optical system. As a typical example, when the three-dimensional position (x-coordinate, y-coordinate, z-coordinate) of the eye E to be examined is obtained by the three-dimensional position calculator 252, the x-coordinate and y-coordinate of the optical axis of the objective lens 22 are the eye E and the difference between the z-coordinate of the objective lens 22 (front lens surface) and the z-coordinate of the eye to be examined E (corneal surface) is equal to a predetermined distance (working distance) , is set as the destination of the optical system.

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

For example, the main controller 211 controls the focus optical system 60 to project the split index on the eye E to be examined. Under the control of the main control unit 211, the data processing unit 230 extracts a pair of split index images by analyzing the observed image of the fundus oculi Ef on which the split indices are projected, and extracts a pair of split index images. Calculate the deviation. The main control unit 211 controls the focus driving unit 31A and the focus driving unit 43A based on the calculated deviation (direction of deviation, amount of deviation).

(S3: OCT measurement)
Next, the main controller 211 causes OCT measurement to be performed.

For example, the main control unit 211 causes the LCD 39 to display a fixation target for OCT measurement at a predetermined position. The main control unit 211 can display the fixation target at the display position of the LCD 39 corresponding to the position of the optical axis of the optical system on the fundus oculi Ef.

Subsequently, the main control unit 211 controls the OCT unit 100 to perform OCT provisional measurement and acquire an adjustment tomographic image for adjusting the reference position of the measurement range in the depth direction. Specifically, the main control unit 211 controls the optical scanner 42 to deflect the measuring light LS generated based on the light L0 emitted from the light source unit 101, and the deflected measuring light LS A predetermined site (for example, the fundus) of the eye E to be examined is scanned. A detection result of the interference light obtained by scanning the measurement light LS is sampled in synchronization with the clock KC and then sent to the image forming section 220 . The image forming unit 220 forms a tomographic image (OCT image) of the subject's eye E from the obtained interference signal.

Subsequently, the main control unit 211 adjusts the reference position of the measurement range in the depth direction (z direction).

For example, the main control unit 211 causes the data processing unit 230 to identify a predetermined site (for example, the sclera) in the acquired tomographic image, and a predetermined distance in the depth direction from the position of the identified predetermined site. A position that is separated by The main control section 211 controls at least one of the optical path length changing section 41 and the reference driving section 114A in accordance with the reference position. Also, a predetermined position determined in advance so that the optical path lengths of the measurement light LS and the reference light LR substantially match may be set as the reference position of the measurement range.

Next, the main controller 211 executes focus adjustment control and polarization adjustment control.

For example, the main control unit 211 controls the focus drive unit 43A to move the OCT focus lens 43 by a predetermined distance, and then controls the OCT unit 100 to perform OCT measurement. The main control unit 211 causes the data processing unit 230 to determine the focus state of the measurement light LS based on the detection result of the interference light obtained by the OCT measurement. When it is determined that the focus state of the measurement light LS is not appropriate based on the determination result by the data processing unit 230, the main control unit 211 controls the focus driving unit 43A again to determine that the focus state is appropriate. Repeat until determined.

Further, for example, the main control unit 211 controls at least one of the polarization controllers 103 and 118 to change the polarization state of at least one of the light L0 and the measurement light LS by a predetermined amount, and then controls the OCT unit 100. to perform OCT measurement, and the image forming unit 220 to form an OCT image based on the obtained detection result of the interference light. The main control unit 211 causes the data processing unit 230 to determine the image quality of the OCT image obtained by the OCT measurement. When it is determined that the polarization state of the measurement light LS is not appropriate based on the determination result by the data processing unit 230, the main control unit 211 controls the polarization controllers 103 and 118 again so that the polarization state is appropriate. Repeat until it is determined that

Subsequently, the main controller 211 controls the OCT unit 100 to perform OCT measurement. A detection result of interference light obtained by the OCT measurement is sampled by the DAQ 130 and stored as an interference signal in the storage unit 212 or the like.

For example, the main control unit 211 causes the image forming unit 220 to form a data set group of A-scan image data of the subject's eye E based on the acquired interference signal. The image forming unit 220 forms a tomographic image by arranging the formed A-scan images in the B-scan direction.

(S4: risk determination processing)
Next, the main control unit 211 controls the risk determination processing unit 260 in the data processing unit 230 to execute CSC risk determination processing based on the OCT data or the tomographic image acquired in step S3.

Details of step S4 will be described later.

With this, the operation of the ophthalmologic apparatus 1 is completed (end).

The process of step S4 in FIG. 11 is executed as shown in FIG.

(S11: Identify BM and CSI)
The main control unit 211 controls the layer region specifying unit 261 to specify the Bruch membrane (BM) and CSI based on the OCT data acquired in step S3 of FIG. 11 as described above. As a result, the layer region identifying unit 261 can identify the choroid.

(S12: Identify layer thickness between BM and CSI)
Next, the main control unit 211 controls the layer thickness specifying unit 262 to specify the layer thickness between the BM and the CSI specified in step S11 for each A line as described above. As a result, the layer thickness specifying unit 262 can generate a layer thickness profile of the choroid.

(S13: moving average processing)
Next, the main control unit 211 controls the moving average processing unit 2631 to sequentially calculate moving averages in the B scan direction within a scanning angle range of 10 degrees for the choroid layer thickness data specified in step S12. . As a result, the moving average processing unit 2631 can generate layer thickness data of the choroid after moving average processing.

(S14: Specify the characteristic position of the layer thickness change amount)
Next, the main control unit 211 controls the characteristic position specifying unit 263 to calculate the layer thickness difference of the adjacent A lines ( layer thickness variation) is calculated. The main control unit 211 controls the characteristic position specifying unit 263 to specify the characteristic position of the layer thickness change amount from the calculated difference in layer thickness.

For example, the layer thickness change amount profile generator 264 generates a layer thickness change amount profile from the layer thickness change amounts sequentially specified in step S14. In some embodiments, characteristic positions of the layer thickness variation are identified from the layer thickness variation profile generated by the layer thickness variation profile generator 264 .

The details of step S14 will be described later.

(See S15: risk determination information)
Subsequently, the main control section 211 controls the risk determination section 265 to refer to the risk determination information 212A based on the layer thickness change amount at the characteristic position specified in step S14. The risk determination unit 265 identifies risk information corresponding to the layer thickness change amount identified in step S14 from the risk determination information 212A.

(S16: risk determination)
Subsequently, the main control unit 211 controls the risk determination unit 265 to determine the risk of CSC with respect to the subject's eye E based on the risk information specified in step S15. The risk determination unit 265 generates a risk determination result including at least one of whether or not the subject eye E is CSC and the probability that the subject eye is CSC from the specified risk information.

(S17: display)
Subsequently, the display control unit 211A causes the display unit 240A to display the feature position identified in step S14, the layer thickness change amount at the feature position, and the risk determination result obtained in step S16.

In some embodiments, the display control unit 211A causes the display unit 240A to display information representing the slope corresponding to the amount of change in layer thickness at the characteristic position, as shown in FIG.

With this, the process of step S4 in FIG. 11 is completed (end).

The process of step S14 in FIG. 12 is executed as shown in FIG. FIG. 13 shows a processing example in which a position indicating the maximum value of the layer thickness variation is specified as a feature position of the layer thickness variation profile. It is assumed that the maximum value of the layer thickness change amount is initialized (for example, the maximum value is initialized to “0” or a negative value) before executing the process of FIG. 13 .

(S21: Calculate scan angle for one A line)
First, the characteristic position specifying unit 263 calculates a scan angle for one A line centered on the scan center position of the OCT scan. The imaging angle of view is a known design value unique to the ophthalmologic apparatus 1 due to the arrangement of the optical system of the ophthalmologic apparatus 1 and the like. The range of A-scan measurement positions (A-line positions) arranged in the B-scan direction corresponds to the number of pixels in the tomographic image in the B-scan direction. The number of pixels in the B-scan direction in the tomographic image is also predetermined. Therefore, the feature position specifying unit 263 obtains the scan angle for each A line by dividing the known imaging angle of view unique to the ophthalmologic apparatus 1 by the known number of pixels in the B scan direction in the tomographic image.

(S22: Find the difference in layer thickness between adjacent A lines)
Next, the maximum value specifying unit 2632 in the characteristic position specifying unit 263 obtains, for example, the difference in layer thickness between adjacent A lines separated by the scan angle calculated in step S21 in the tomographic image of the eye E to be examined.

(S23: Identify slope of layer thickness)
Next, the maximum value specifying unit 2632 divides the difference in layer thickness calculated in step S22 by the scan angle for one A line calculated in step S21 to obtain the layer thickness as the amount of change in layer thickness. identify the slope of

(S24: slope > maximum value?)
Subsequently, the maximum value identifying unit 2632 determines whether or not the slope of the layer thickness calculated in step S23 exceeds the maximum value.

When it is determined in step S24 that the calculated slope of the layer thickness exceeds the maximum value (step S24: Y), the process of step S14 in FIG. 12 proceeds to step S25. When it is determined in step S24 that the calculated slope of the layer thickness does not exceed the maximum value (S24: N), the process of step S14 in FIG. 12 proceeds to step S26.

(S25: update the maximum value of the slope)
When it is determined in step S24 that the slope of the calculated layer thickness exceeds the maximum value (step S24: Y), the maximum value specifying unit 2632 updates the slope calculated in step S23 as the maximum value. .

(S26: Next A line?)
Following step S25 or when it is determined in step S24 that the slope of the calculated layer thickness does not exceed the maximum value (S24: N), the maximum value specifying unit 2632 determines the layer thickness for the next A line. It is determined whether or not to continue the calculation of the slope of .

The maximum value specifying unit 2632 determines whether or not steps S22 to S25 have been repeated for a predetermined number of A lines, thereby determining whether or not to continue calculating the layer thickness gradient for the next A line. can be discriminated.

When it is determined in step S26 to continue the calculation of the layer thickness gradient for the next A line (step S26: Y), the process of step S14 in FIG. 12 proceeds to step S22. When it is determined in step S26 not to continue calculating the layer thickness gradient for the next A line (step S26: N), the process of step S14 in FIG. 12 proceeds to step S27.

(S27: Generate layer thickness variation profile)
In step S26, when it is determined not to continue calculating the slope of the layer thickness for the next A line (step S26: N), the main control unit 211 controls the layer thickness change amount profile generation unit 264 to perform step Using the layer thickness gradient obtained by repeatedly executing S23 as the layer thickness change amount, a layer thickness change amount profile indicating the layer thickness change amount along the B scan direction is generated.

With this, the process of step S14 in FIG. 12 is completed (end).

Also, the process of step S4 in FIG. 11 is not limited to the process shown in FIG. For example, the process of step S4 in FIG. 11 may be performed as shown in FIG.

(S31: Identify BM and CSI)
As in step S11, the main control unit 211 controls the layer region specifying unit 261 to specify Bruch's membrane (BM) and CSI based on the OCT data acquired in step S3 of FIG. 11 as described above. Let As a result, the layer region identifying unit 261 can identify the choroid.

(S32: Identify layer thickness between BM and CSI)
Next, the main control unit 211 controls the layer thickness specifying unit 262 to specify the layer thickness between the BM and CSI specified in step S31 for each A line, as in step S12. As a result, the layer thickness specifying unit 262 can generate a layer thickness profile of the choroid.

(S33: moving average processing)
Next, as in step S13, the main control unit 211 controls the moving average processing unit 2631 to move the choroid layer thickness data identified in step S32 in the B scan direction within a scan angle range of 10 degrees. Let the averages be calculated sequentially. As a result, the moving average processing unit 2631 can generate layer thickness data of the choroid after moving average processing.

(S34: Specify the characteristic position of the layer thickness change amount)
Next, the main control unit 211 controls the characteristic position specifying unit 263 in the same manner as in step S14 to obtain the choroidal layer thickness data after the moving average processing obtained in step S33. The difference in layer thickness (amount of change in layer thickness) is calculated. The main control unit 211 controls the characteristic position specifying unit 263 to specify the characteristic position of the layer thickness change amount from the calculated difference in layer thickness.

Further, in step S34, the main control unit 211 controls the layer thickness variation profile generation unit 264 to determine the layer thickness variation along the B scan direction based on the layer thickness variation identified in step S34. to generate a layer thickness variation profile representing

(See S35: risk determination information)
Subsequently, the main control section 211 controls the risk determination section 265 to refer to the risk determination information 212A based on the layer thickness change amount at the characteristic position identified in step S14, as in step S15. The risk determination unit 265 identifies risk information corresponding to the layer thickness change amount identified in step S14 from the risk determination information 212A.

(S36: risk determination)
Subsequently, the main control section 211 controls the risk determination section 265 to determine the risk of CSC with respect to the subject's eye E based on the risk information specified in step S15, as in step S16. The risk determination unit 265 generates a risk determination result including at least one of whether or not the subject eye E is CSC and the probability that the subject eye is CSC from the specified risk information.

(S37: display tomographic image and layer thickness variation profile)
Next, the display control unit 211A causes the display unit 240A to display the tomographic image formed in step S3 of FIG. 11 and the layer thickness variation profile generated in step S34. For example, the display control unit 211A causes the display unit 240A to display the tomographic image and the layer thickness variation profile as shown in FIG. 7 or 8 .

In step S37, the display control unit 211A displays the layer thickness profile or the layer thickness profile after moving average processing in addition to the tomographic image and the layer thickness change amount profile, as shown in FIG. 7, FIG. 8, or FIG. It is possible to display it on the part 240A.

(S38: Display additional information)
Subsequently, the display control unit 211A causes the display unit 240A to display various supplementary information so as to be superimposed on the tomographic image and layer thickness variation profile. Examples of additional information include triangular marks (information) indicating positions corresponding to characteristic positions in the layer thickness variation profile, information indicating the amount of variation at characteristic positions in the layer thickness variation profile, layer There is information indicating the thickness and information indicating the slope at the characteristic position of the layer thickness profile.

With this, the process of step S4 in FIG. 11 is completed (end).

[Modification]
In the above embodiment, the display control unit 211A may cause the display unit 240A to display a tomographic image that has undergone actual shape correction so as to match the actual shape of the eyeball. In this case, the data processing unit performs actual shape correction on the OCT data or tomographic image of the subject's eye. The display control unit 211A causes the display unit 240A to display a corrected tomographic image formed based on OCT data subjected to actual shape correction or a tomographic image subjected to actual shape correction.

Modifications of the embodiment will be described below, focusing on differences from the embodiment.

The configuration of the optical system of the ophthalmologic apparatus according to the modified example of the embodiment is the same as the configuration of the optical system of the ophthalmologic apparatus 1 according to the embodiment. The configuration of the processing system of the ophthalmologic apparatus according to the modification of the embodiment differs from the configuration of the processing system of the ophthalmologic apparatus 1 according to the embodiment in that a data processing section 230a is provided instead of the data processing section 230. be.

FIG. 15 shows a block diagram of a configuration example of the data processing unit 230a according to the modification of the embodiment. In FIG. 15, the same parts as those in FIG. 4 are denoted by the same reference numerals, and description thereof will be omitted as appropriate.

The configuration of the data processing section 230a differs from that of the data processing section 230 in that an actual shape correction section 300 is added to the data processing section 230a.

(Actual shape correction unit 300)
The actual shape correction unit 300 performs actual shape correction on the OCT data of the eye E to be examined or the OCT image (tomographic image) formed by the image forming unit 220 based on the OCT data of the eye E to be examined. The actual shape correction unit 300 scans the inside of the eye with the measurement light LS using the optical scanner 42 arranged substantially optically conjugate with the pupil (predetermined portion) of the eye E to be inspected. Correct the dimensional OCT data (scan data) or the OCT image. OCT images are two-dimensional or three-dimensional images. OCT images include a tomographic image of the fundus, a three-dimensional image of the fundus, and the like.

The real shape correction unit 300 corresponds to the pixel position in the OCT image or the scan position in the two-dimensional or three-dimensional scan data, and converts the converted position along the A scan direction (the traveling direction of the measurement light passing through the scan center position). identify. The actual shape correction unit 300 converts the pixel position or the scan position into the conversion position specified based on the pixel position or the like. A transformed position is a position in a predetermined coordinate system. The predetermined coordinate system is defined by two or more coordinate axes including at least one coordinate axis in the same axial direction as the scanning direction of the A-scan.

In some embodiments, the actual shape correction unit 300 identifies the transformation position based on parameters representing the optical characteristics of the eye E to be inspected (eg, axial length). In some embodiments, the actual shape correction unit 300 performs conversion in a predetermined coordinate system based on the scan radius in the A-scan direction, the scan angle, the depth range where OCT measurement is possible, and the pixel position or scan position. At least one of a component of position along a first axis and a component of a second axis that intersects the first axis is identified.

FIG. 16 shows an explanatory diagram of a comparative example of the embodiment. FIG. 16 schematically shows the path of measurement light incident on the eye E to be examined.

For example, the measurement light deflected by the optical scanner 42 is incident on the pupil of the subject's eye E as the scan center position at various angles of incidence, as shown in FIG. The measurement light incident on the subject's eye E is projected toward each part in the eye around a scan center position Cs set, for example, at the center of the pupil.

An A-scan image was formed from the interference data obtained using the measurement light LS1 in FIG. 16, an A-scan image was formed from the interference data obtained using the measurement light LS2, and an A-scan image was formed using the measurement light LS3. An A-scan image is formed from the interferometric data. A tomographic image of the fundus oculi Ef is formed by arranging a plurality of A-scan images thus formed.

In this manner, the A-scan direction changes within the scan angle range centered on the scan center position Cs, and the shape of the site is deformed in a tomographic image in which a plurality of obtained A-scan images are arranged in the horizontal direction. This is because the wider the angle of view, the greater the difference from the actual shape.

Morphological information representing the morphology of the subject's eye E can be obtained from the position of an arbitrary pixel in the tomographic image. Such morphological information includes the thickness of a layer region, the distance between regions, the area of a region, the volume of a region, the perimeter of a region, the direction of a region with respect to a reference position, the angle of a region with respect to the reference direction, the radius of curvature of a region. etc.

For example, the thickness of a layer region (or the distance between parts) as morphological information can be obtained by measuring the distance between any two points in the tomographic image. In this case, the distance between two points is specified by the number of pixels in the tomographic image, and is measured by multiplying the specified number of pixels by the device-specific pixel size. At this time, the same pixel size is adopted for all pixels in the tomographic image. However, as described above, since the scanning direction differs around the scanning center position Cs, the horizontal pixel size of the tomographic image differs depending on the depth position in the scanning direction. For example, when the depth range is 2.5 [mm], when the same pixel size is adopted for all pixels in the tomographic image, the scan length of the B scan between the top and bottom of the tomographic image is about 13%. When the depth range is 10 [mm], the difference is about 50%.

Therefore, the actual shape correction unit 300 performs coordinate transformation of pixel positions in the acquired OCT image or scanning positions in the scan data.

A case where the actual shape correction unit 300 performs actual shape correction on a tomographic image formed based on the OCT data of the eye E will be mainly described below. When the actual shape correction unit 300 performs actual shape correction on OCT data (scan data), the “pixel position” in the tomographic image should be read as the “scan position” in the OCT data.

FIG. 17 shows a block diagram of a configuration example of the actual shape correction unit 300 of FIG.

Actual shape correction section 300 includes a position specifying section 310 , a position conversion section 320 and an interpolation section 330 .

(Position specifying unit 310)
The position specifying unit 310 specifies a conversion position along the traveling direction of the measurement light passing through the scan center position Cs, corresponding to the pixel position in the acquired tomographic image. In some embodiments, the position identifying unit 310 uses the eyeball parameters (such as axial length) of the subject's eye E or the eyeball parameters of the model eye for the conversion position identifying process.

FIG. 18 shows an operation explanatory diagram of the position specifying unit 310 according to the modified example of the embodiment. In FIG. 18, the same parts as in FIG. 16 are denoted by the same reference numerals, and description thereof will be omitted as appropriate.

Here, the scan angle is φ, the scan radius is r, the depth range in which OCT measurement is possible is d, the length of the tomographic image in the depth direction is h, and the length of the tomographic image in the horizontal direction is w. and The scan angle φ corresponds to the deflection angle of the measurement light LS around the scan center position Cs. The scan radius r corresponds to the distance from the scan center position Cs to the optical path length zero position where the measurement optical path length and the reference optical path length are substantially equal. The depth range d is a device-specific value (known) that is uniquely determined by the optical design of the device or the like.

The position specifying unit 310 specifies the transformed position (X, Z) in the second coordinate system from the pixel position (x, z) in the first coordinate system. The first coordinate system has an origin at the upper left coordinate position in a tomographic image (OCT image, B scan image), an x coordinate axis with the B scan direction as the x direction, and an A scan direction orthogonal to the x coordinate axis with the z direction. and the z coordinate axis. A pixel position (x, z) in the tomographic image is defined in the first coordinate system. The second coordinate system is a Z coordinate axis (eg, second axis) whose Z direction is the traveling direction of the measurement light LS whose scan angle is 0 degrees with respect to the measurement optical axis that passes through a predetermined portion (eg, the fovea centralis) of the fundus oculi Ef. and an X-coordinate axis (for example, a first axis) whose X direction is the B-scanning direction orthogonal to the Z-coordinate axis at the predetermined site. In the second coordinate system, a predetermined Z position is set as the origin of the Z coordinate axis so that the position of the scan radius r is the deepest part in the measurement optical axis passing through a predetermined portion (for example, the fovea centralis). Also, a predetermined X position on the measurement optical axis passing through a predetermined portion (for example, the fovea) is set as the origin of the X coordinate axis so as to have a predetermined length d in the depth direction as described below. A transformed position (X, Z) is defined in a second coordinate system. The conversion position (X, Z) corresponds to the pixel position (x, z) and is a position along the traveling direction (A scan direction) of the measurement light LS passing through the scan center position Cs.

The position specifying unit 310 calculates a transformed position (X, Z). The position specifying unit 310 can specify at least one of the X component (component in the first axis direction) and Z component (component in the second axis direction) of the transformed position.

For an OCT image (tomographic image) having N (N is a natural number) A-scan lines, the transformation position (X, Z) corresponding to the pixel position (x, z) in the n-th (n is a natural number) A-scan line is specified as shown in equations (1) and (2).

Here, the length h in the depth direction, the length w in the horizontal direction, and the x component of the pixel position of the OCT image are represented by equations (3) to (5).

In equations (1) and (2), the x-coordinate of the pixel position is represented by equation (5). Therefore, the position specifying unit 310 can specify the transformation position (X, Z) from the pixel position (x, z) based on the scan radius r, scan angle φ, and depth range d.

In some embodiments, the position specifying unit 310, in the same manner as described above, for the scan data, scan radius r in the A scan direction, scan angle φ, OCT measurable depth range d, and scan position , it is possible to identify the transformation position (X, Z).

In some embodiments, the scan radius r is determined by analyzing the detection results of interfering light LC obtained using OCT unit 100 . Thereby, it is possible to specify the transformation position (X, Z) that more accurately reflects the eyeball optical characteristics of the eye E to be examined.

In some embodiments, the position specifying unit 310 specifies the scan angle φ by performing ray tracing processing on the measurement light LS based on the corneal shape information of the eye E to be examined. The corneal shape information includes corneal curvature radius (corneal anterior curvature radius, corneal posterior curvature radius), corneal thickness, and the like. Thereby, it is possible to specify the transformation position (X, Z) that more accurately reflects the eyeball optical characteristics of the eye E to be examined.

(Position converter 320)
The position conversion unit 320 converts the pixel position (x, z) of the tomographic image into the conversion position (X, Z) specified by the position specifying unit 310 . In some embodiments, for each pixel location of the tomographic image, the location identification unit 310 identifies a transformation location, and the location transformation unit 320 transforms the pixel location to the transformation location.

Thereby, as shown in FIG. 19, it is possible to arrange the A-scan images acquired by the A-scan in the A-scan direction. Therefore, even when the angle of view is wide, it is possible to acquire a tomographic image in which the shape of the predetermined portion is similar to the actual shape.

(Interpolation unit 330)
The interpolator 330 interpolates pixels between the conversion positions. For example, as described above, according to the distance from the scan center position Cs, the pixel position is converted to the conversion position, and the interval between adjacent A-scan images changes. The interpolation unit 330 interpolates pixels between the A-scan images using the pixels of the A-scan images adjacent to each other according to the depth position of the A-scan images. For pixel interpolation processing by the interpolator 330, known methods such as the nearest neighbor method, bilinear interpolation method, and bicubic interpolation method can be employed. In some embodiments, the interpolator 330 interpolates pixels between adjacent A-scan images according to the distance from the scan center position Cs. For example, the interpolator 330 interpolates pixels between adjacent A-scan images by changing the interpolation processing method according to the distance from the scan center position Cs.

In some embodiments, scan data is interpolated in the same manner as above for scan positions in the scan data.

FIG. 20 shows an example of the flow of actual shape correction processing according to the modification of the embodiment. The storage unit 212 stores a computer program for realizing the processing shown in FIG. The main control unit 211 executes the processing shown in FIG. 20 by operating according to this computer program.

(S41: Calculate conversion position)
First, the main control unit 211 causes the position specifying unit 310 to specify the conversion positions corresponding to the pixel positions of the tomographic image. The position specifying unit 310 specifies the conversion positions corresponding to the pixel positions of the tomographic image as described above.

(S42: Convert pixel position)
Subsequently, the main control unit 211 controls the position conversion unit 320 to convert the pixel positions of the tomographic image to the conversion positions calculated in step S41.

(S43: End?)
The main control unit 211 determines whether or not to end the pixel position conversion.

When it is determined that there is a pixel position to be converted next (S43: N), the operation of the ophthalmologic apparatus according to this modification proceeds to step S41. When it is determined that there is no pixel position to be converted next (S43: Y), the operation of the ophthalmologic apparatus 1 according to this modification proceeds to step S44.

Through steps S41 to S43, a conversion position is specified and conversion to the specified conversion position is performed for each pixel position of the tomographic image.

(S44: interpolation)
When it is determined in step S43 that there is no pixel position to be converted next (S43: Y), the main control unit 211 converts the pixels between the mutually adjacent A-scan images converted to the conversion positions in step S42 into The interpolator 330 interpolates.

With the above, the actual shape correction processing according to the present modification is finished (end).

As shown in FIG. 7, FIG. 8, or FIG. 10, the display control unit 211A can display the layer thickness profile on the display unit 240A in association with the tomographic image on which the actual shape correction has been performed.

FIG. 21 schematically shows an example in which a tomographic image after actual shape correction and a layer thickness profile are associated with each other and displayed on the display unit 240A according to the modified example of the embodiment. In FIG. 21, the horizontal axis of the characteristic graph showing the layer thickness profile etc. represents the pixel position of the tomographic image corresponding to the scan angle, and the vertical axis represents the thickness.

When OCT is performed on the eye to be inspected and OCT data is acquired, the layer region specifying unit 261 specifies the choroid as described above using the acquired OCT data. The layer thickness specifying unit 262 specifies the layer thickness of the choroid in the A-scan direction specified by the layer area specifying unit 261 as described above. By specifying the layer thickness for each pixel position, a choroid layer thickness profile T41 as shown in FIG. 21 is obtained.

The moving average processing unit 2631 sequentially obtains the moving average of the layer thickness of a plurality of A lines within a scanning angle range of 10 degrees adjacent to the B scanning direction for the layer thickness profile T41. to generate a layer thickness profile T42 of

For example, the characteristic position specifying unit 263 (maximum value specifying unit 2632) specifies the maximum value of the layer thickness variation from the layer thickness profile T42. The characteristic position identifying section 263 identifies the position indicating the maximum value identified by the maximum value identifying section 2632 as a characteristic position P51 indicating the maximum choroidal change value.

The layer thickness change amount profile generation unit 264 generates a layer thickness change amount profile (not shown) by obtaining a difference in layer thickness between adjacent A lines in the layer thickness profile T42 after the moving average process. Is possible.

Further, as described above, the actual shape correction unit 300 performs actual shape correction on the tomographic image formed by the image forming unit 220 based on the acquired OCT data. As shown in FIG. 21, the display control unit 211A can cause the display unit 240A to display the layer thickness profiles T41 and T42 in association with the tomographic image after actual shape correction (corrected tomographic image). In the tomographic image after real shape correction, A-scan images are arranged along A-scan lines (A-lines) that advance in a direction corresponding to the scan angle centering on the scan center position. This enables, for example, a physician to visually explain to a patient a site suspected of CSC as a characteristic location, or to facilitate the physician's consideration of a therapeutic strategy or surgical strategy.

Further, the display control section 211A may cause the display section 240A to display information indicating the position corresponding to the characteristic position P51 in the layer thickness profiles T41 and T42. In some embodiments, the display control unit 211A causes the display unit 240A to display the layer thickness change amount profile in association with the tomographic image after the actual shape correction.

In FIG. 21, the pixel position (angle of view) is represented as the 100% position at the center position of the B scan line (for example, pixel position “1023” or “1024”) and the 0% position at pixel position “0”. , the position of pixel position '2047' is represented as the 0% position. In the tomographic image IMG4 as a corrected tomographic image, a line segment corresponding to the A scan line corresponding to the pixel position and percentage numerical information representing the pixel position are depicted. In FIG. 21, the pixel position corresponding to the feature position P51 is represented by a line segment representing the A scan line corresponding to the feature position P51 and information representing a numerical value of Pc (0≤Pc≤100)%. This makes it possible to easily specify the positions corresponding to the characteristic positions in the fundus having a curved shape.

In some embodiments, as shown in FIG. 10, the display control unit 211A displays information (index) representing the layer thickness change amount at the characteristic position of the layer thickness profile (for example, a vertical line segment at the characteristic position). Displayed on the display unit 240A. In this case, the display control unit 211A displays, on the display unit 240A, information representing the slope corresponding to the amount of change in layer thickness at the feature position P51 of the layer thickness profiles T41 and T42 (the slope of the tangent line at the feature position of the layer thickness profile). Let For example, the information representing the tilt is displayed in such a manner that the greater the tilt, the more the user's attention is drawn to it. For example, the degree of suspicion of a CSC eye from a normal eye can be represented by the tilt angle and the color of the information representing the tilt.

[Another modification]
In this modified example, the case of correcting the actual shape of a two-dimensional OCT image (or two-dimensional scan data) has been described, but the configuration according to the embodiment is not limited to this. The ophthalmologic apparatus according to the embodiment can correct a three-dimensional OCT image (or three-dimensional scan data), as in the above modification.

FIG. 22 shows an operation explanatory diagram of the position specifying unit according to another modification of the embodiment. In FIG. 22, the same parts as in FIG. 18 are given the same reference numerals, and the description thereof will be omitted as appropriate.

In FIG. 22, a Y plane is defined in addition to the X and Z planes in FIG. In addition to the parameters shown in FIG. 18, let θ be the central angle in the C-scan direction, and lc be the length in the C-scan direction.

The position specifying unit 310 specifies the transformation position (X, Y, Z) in the fourth coordinate system from the pixel position (x, y, z) in the third coordinate system. The third coordinate system has the coordinate position of the upper left corner in the three-dimensional OCT image as the origin, the x coordinate axis with the B scan direction as the x direction, the y coordinate axis orthogonal to the x coordinate axis with the C scan direction as the y direction, It is defined by a z-coordinate axis that is orthogonal to both the x-coordinate axis and the y-coordinate axis and has the A-scan direction as the z-direction. A pixel position (x, y, z) in the OCT image is defined in a third coordinate system. The fourth coordinate system has a Z coordinate axis in which the Z direction is the traveling direction of the measurement light LS having a scan angle of 0 degrees with respect to the measurement optical axis passing through a predetermined portion (for example, the fovea) of the fundus oculi Ef, and a Z coordinate axis in the predetermined portion. It is defined by an X-coordinate axis whose X direction is the B-scanning direction perpendicular to the coordinate axis, and a Y-coordinate axis whose Y-direction is the C-scanning direction perpendicular to the Z-coordinate axis at the predetermined site. In the fourth coordinate system, a predetermined Z position is set as the origin of the Z coordinate axis so that the position of the scan radius r in the measurement optical axis passing through a predetermined portion (for example, the fovea) is the deepest part. Also, the predetermined X position and Y position on the measurement optical axis passing through a predetermined site (for example, the fovea) are set as the origin of the X coordinate axis and the Y coordinate axis so that the length d in the depth direction is predetermined as follows. do. A transform position (X, Y, Z) is defined in a fourth coordinate system. The conversion position (X, Y, Z) corresponds to the pixel position (x, y, z) and is a position along the travel direction (A scan direction) of the measurement light LS passing through the scan center position Cs.

The position identifying unit 310 can identify at least one of the X, Y and Z components of the transformed position.

For an OCT image (tomographic image) where the number of A-scan lines is N (N is a natural number) and the number of B-scan lines is M (M is a natural number), the m-th (m is a natural number) B-scan n (n is a natural number) )th A scan line, the transform position (X, Y, Z) corresponding to the pixel position (x, y, z) is specified as shown in equations (6) to (8).

Here, from the length h in the depth direction, the length w in the B scanning direction, and the length lc in the C scanning direction of the three-dimensional OCT image, the x component and the y component of the pixel position are expressed by equations (9) to It is expressed as in Equation (13).

In equations (6) to (8), x-coordinates and y-coordinates of pixel positions are expressed as in equations (12) and (13). Therefore, the position specifying unit 310 can specify the transformation position (X, Y, Z) from the pixel position (x, y, z) based on the scan radius r, the scan angle φ, and the depth range d. It is possible.

In some embodiments, the position specifying unit 310 can specify the transformation position (X, Y, Z) for three-dimensional scan data (OCT data) in the same manner as described above.

The position transforming unit 320 transforms the pixel position (x, y, z) of the OCT image into the transforming position (X, Y, Z) specified by the position specifying unit 310 . In some embodiments, for each pixel location of the OCT image, the location identifier 310 identifies a transform location, and the location transform unit 320 transforms the pixel location to the transform location. The interpolation section 330 interpolates pixels between the conversion positions converted by the position conversion section 320 .

In some embodiments, the display control unit 211A causes the display unit 240A to display a three-dimensional OCT image in association with the layer thickness profile instead of the tomographic image in FIG. In this case, the display control unit 211A may identifiably display positions corresponding to characteristic positions in the layer thickness profile in the three-dimensional OCT image.

In some embodiments, the display control unit 211A outputs three-dimensional OCT data, a three-dimensional OCT image, three-dimensional OCT data after real shape correction (scan data), or a three-dimensional image after real shape correction (three-dimensional OCT The position corresponding to the characteristic position in the layer thickness profile in the front image (C-scan image, projection image, or en-face image) formed from the actual shape corrected image) is identifiably displayed on the display unit 240A. In this case, the display control unit 211A may cause the display unit 240A to identifiably display the positions corresponding to the characteristic positions together with the OCT scan regions in the front image.

In a modification of the above embodiment or another modification of the embodiment, feature positions identified from OCT data before actual shape correction can be identified in an OCT image (such as a tomographic image) after actual shape correction. Although the case of displaying is described, the configuration according to the embodiment is not limited to this. For example, first, the OCT data is subjected to the actual shape correction as described above, and the characteristic position of the film thickness variation in the A-scan direction of the predetermined layer region is specified based on the OCT data subjected to the actual shape correction. You may make it In this case, the actual shape correction unit 300 performs actual shape correction on the OCT data of the eye E to be examined, and the layer thickness specifying unit 262 performs the actual shape correction based on the OCT data subjected to the actual shape correction by the actual shape correction unit 300. A layer thickness in the A-scan direction of a predetermined layer region (for example, choroid) is specified.

<Action>
An ophthalmologic information processing apparatus, an ophthalmologic apparatus, an ophthalmologic information processing method, and a program according to embodiments will be described.

An ophthalmologic information processing apparatus (arithmetic control unit 200 (control unit 210, image forming unit 220, and data processing unit 230)) according to a first aspect of some embodiments includes a layer thickness specifying unit (262), a feature position and a specifying part (263). The layer thickness specifying unit specifies the layer thickness in the A-scan direction of a predetermined layer region in the measurement site based on the OCT data of the eye to be examined (E). The feature position specifying unit specifies the feature position of the amount of change in layer thickness in the direction intersecting the A scan direction (B scan direction) based on the layer thickness specified by the layer thickness specification unit.

According to this aspect, since the characteristic position of the amount of change in layer thickness at the measurement site of the eye to be examined is specified, it is possible to specify the change in the morphology of the tissue of the eye to be inspected with high accuracy. In addition, regardless of the measurement range such as the imaging angle of view, changes in the morphology of the tissue of the subject's eye can be observed in detail over a wide range.

An ophthalmologic information processing apparatus according to a second aspect of some embodiments, in the first aspect, includes a risk determination unit (265) that determines the risk of disease based on the amount of change in layer thickness at the characteristic position.

According to this aspect, since the risk of disease is determined based on the amount of change in layer thickness at the identified feature position, the risk of disease can be determined even when the change in morphology peculiar to the disease is not remarkable. it becomes possible to Thereby, it becomes possible to contribute to early detection and early treatment of diseases.

In the second aspect of the ophthalmologic information processing apparatus according to the third aspect of some embodiments, the risk determination unit obtains risk determination information (212A ) to determine the risk of disease.

According to this aspect, the risk of disease can be determined according to the relationship between the predetermined amount of change and the information representing the risk of the disease. It is also possible to determine the risk of disease with high accuracy.

In the ophthalmic information processing apparatus according to the fourth aspect of some embodiments, in the second aspect or the third aspect, the disease includes central serous chorioretinopathy (CSC).

According to such an aspect, it is possible to determine the risk of CSC even when the morphological change peculiar to CSC is not remarkable. Thereby, it becomes possible to contribute to early detection and early treatment of CSC.

An ophthalmologic information processing apparatus according to a fifth aspect of some embodiments, in any one of the first to fourth aspects, displays a layer thickness change amount profile representing the amount of change in layer thickness along the cross direction. A display control section (211A) for displaying on means (display section 240A) is included, and the display control section causes the display means to display information indicating positions corresponding to characteristic positions in the layer thickness change amount profile.

According to this aspect, since the information indicating the position corresponding to the characteristic position in the layer thickness change amount profile is displayed on the display means, the morphological change is continuously observed in detail as a part to be noted in the future. be able to

In the fifth aspect of the ophthalmologic information processing apparatus according to the sixth aspect of some embodiments, the display control unit causes the display means to display information indicating the amount of change at the characteristic position in the layer thickness variation profile.

According to this aspect, since it is possible to visually recognize the amount of change in the characteristic position in the layer thickness change amount profile, it becomes possible to continuously observe in detail the change in the form as a part to be noted in the future. .

In the ophthalmologic information processing apparatus according to the seventh aspect of some embodiments, in the fifth aspect or the sixth aspect, the display control unit displays information representing the tilt corresponding to the amount of change in the layer thickness at the feature position on the display means. display.

According to such an aspect, it becomes possible to easily grasp the amount of change in the layer thickness.

In the ophthalmologic information processing apparatus according to the eighth aspect of some embodiments, in any one of the fifth to seventh aspects, the display control unit displays a tomographic image formed based on the layer thickness variation profile and the OCT data. are displayed on the display means, and information indicating positions corresponding to the characteristic positions in the tomographic image is displayed on the display means.

According to such an aspect, it becomes possible to continuously and in detail observe changes in the shape of the part to be noted in the future.

An ophthalmologic information processing apparatus according to a ninth aspect of some embodiments, in the eighth aspect, includes a real shape correction unit (300) that performs real shape correction on OCT data or a tomographic image. The display control unit displays a corrected tomographic image (tomographic image IMG4) formed based on OCT data subjected to actual shape correction by the actual shape correction unit, or a tomographic image subjected to actual shape correction by the actual shape correction unit. display on the display means.

According to this aspect, for example, a doctor can visually explain to a patient a site suspected of having a disease as a characteristic position, and the doctor can easily consider a treatment strategy or a surgical strategy. .

An ophthalmologic information processing apparatus according to a tenth aspect of some embodiments includes a real shape correction unit (300) that performs real shape correction on OCT data in any one of the first to eighth aspects. The layer thickness specifying unit specifies the layer thickness of the predetermined layer region in the A-scan direction based on the OCT data subjected to the actual shape correction by the actual shape correcting unit.

In this aspect, the OCT data may be two-dimensional OCT data or three-dimensional OCT data. According to such an aspect, it is possible to specify the feature position by performing the layer thickness analysis on the layer region on which the actual shape correction has been performed. As a result, it is possible to accurately identify the characteristic positions according to the shape of the eyeball of the subject's eye.

In the ophthalmologic information processing apparatus according to the eleventh aspect of some embodiments, in any one of the first to tenth aspects, the characteristic position specifying unit determines the layer thickness difference between the A lines adjacent in the cross direction and , and the scan angle for each A line centered on the scan center position of the OCT scan of the eye to be inspected.

According to such an aspect, it is possible to specify the characteristic position of the amount of change in layer thickness with high accuracy.

In the ophthalmologic information processing apparatus according to the twelfth aspect of some embodiments, in the eleventh aspect, the feature position specifying unit performs smoothing for smoothing the layer thicknesses of the plurality of A-lines adjacent in the intersecting direction in the intersecting direction. A smoothing unit (moving average processing unit 2631) is included, and the characteristic position of the amount of change in layer thickness is specified based on the layer thicknesses of the multiple A lines smoothed by the smoothing unit.

According to this aspect, the stepped layer thickness profile data is smoothed, and the feature position can be specified with good reproducibility from the layer thickness profile data smoothed in the cross direction. .

In the ophthalmologic information processing apparatus according to the thirteenth aspect of some embodiments, in the twelfth aspect, the smoothing unit moves the layer thickness of a plurality of A-lines within a predetermined scan angle range adjacent to the cross direction. Calculate the averages sequentially.

According to this aspect, the stepwise layer thickness profile data is smoothed by a simple moving average process, and the feature position is specified with good reproducibility from the layer thickness profile data smoothed in the cross direction. be able to

In any one of the first to thirteenth aspects of the ophthalmologic information processing apparatus according to the fourteenth aspect of the embodiments, the characteristic position is a position showing the maximum value or the local maximum value of the layer thickness variation.

According to this aspect, since the position and characteristic position showing the maximum value or maximum value of the layer thickness change amount in the measurement site of the eye to be examined are specified, the change in the morphology of the tissue of the eye to be examined can be detected with high accuracy. can be specified. In addition, regardless of the measurement range such as the imaging angle of view, changes in the morphology of the tissue of the subject's eye can be observed in detail over a wide range.

According to some embodiments of the ophthalmologic information processing apparatus according to the fifteenth aspect, in any one of the first to fourteenth aspects, the predetermined layer region is the choroid.

According to this aspect, since the characteristic position of the amount of change in the layer thickness of the choroid is specified, it is possible to specify the change in the morphology of the choroid with high accuracy. In addition, regardless of the measurement range such as the imaging angle of view, it becomes possible to observe changes in the morphology of the choroid in detail over a wide range.

An ophthalmologic apparatus according to a sixteenth aspect of some embodiments includes an optical scanner (42), an OCT optical system that obtains OCT data by projecting measurement light (LS) deflected by the optical scanner onto an eye to be examined. (an optical system from the OCT unit 100 to the objective lens 22) and the ophthalmologic information processing apparatus according to any one of the first to fifteenth aspects.

According to this aspect, it is possible to provide an ophthalmologic apparatus capable of identifying a change in the tissue morphology of an eye to be examined with high accuracy. In addition, it is possible to provide an ophthalmologic apparatus capable of observing changes in the morphology of the tissue of the subject's eye in detail over a wide range regardless of the measurement range such as the imaging angle of view.

An ophthalmologic information processing method according to a seventeenth aspect of some embodiments includes a layer thickness identifying step and a feature position identifying step. The layer thickness specifying step specifies the layer thickness in the A-scan direction of a predetermined layer region in the measurement site based on the OCT data of the eye (E) to be examined. The characteristic position identifying step identifies the characteristic position of the amount of change in layer thickness in a direction intersecting the A scanning direction (B scanning direction) based on the layer thickness identified in the layer thickness identifying step.

According to this aspect, since the characteristic position of the amount of change in layer thickness at the measurement site of the eye to be examined is specified, it is possible to specify the change in the morphology of the tissue of the eye to be inspected with high accuracy. In addition, regardless of the measurement range such as the imaging angle of view, changes in the morphology of the tissue of the subject's eye can be observed in detail over a wide range.

A program according to the eighteenth aspect of some embodiments causes a computer to execute each step of the ophthalmologic information processing method of the seventeenth aspect.

According to this aspect, it is possible to provide a program capable of specifying a change in the morphology of the tissue of the eye to be examined with high accuracy. In addition, it is possible to provide a program that enables detailed observation of changes in the morphology of the tissue of the subject's eye over a wide range, regardless of the measurement range such as the imaging angle of view.

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

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

1 ophthalmologic apparatus 2 retinal camera unit 100 OCT unit 210 control unit 211 main control unit 211A display control unit 212 storage unit 212A risk determination information 220 image forming units 230 and 230a data processing unit 250 alignment processing unit 260 risk determination processing unit 261 layer region Identification unit 262 Layer thickness identification unit 263 Characteristic position identification unit 2631 Moving average processing unit 2632 Maximum value identification unit 264 Layer thickness change amount profile generation unit 265 Risk determination unit 300 Actual shape correction unit 310 Position identification unit 320 Position conversion unit 330 Interpolation unit E Eye to be examined Ef Fundus LS Measurement light

Claims (18)

a layer thickness specifying unit that specifies the layer thickness in the A-scan direction of a predetermined layer region in the measurement site based on the OCT data of the eye to be examined;
a feature position specifying unit that specifies a feature position of the amount of change in the layer thickness in the direction intersecting the A-scan direction based on the layer thickness specified by the layer thickness specifying unit;
An ophthalmic information processing device, comprising: The ophthalmologic information processing apparatus according to claim 1, further comprising a risk determination unit that determines a risk of disease based on the amount of change in the characteristic position. 3. The risk determination unit according to claim 2, wherein the risk determination unit determines the risk of the disease based on risk determination information in which information representing the risk of the disease is pre-associated with each of a plurality of variations. Ophthalmic information processing device. 4. The ophthalmologic information processing apparatus according to claim 2, wherein the disease includes central serous chorioretinopathy. a display control unit that causes a display unit to display a layer thickness variation profile representing the variation of the layer thickness along the cross direction;
The display controller according to any one of claims 1 to 4, wherein the display control unit causes the display means to display information indicating a position corresponding to the characteristic position in the layer thickness variation profile. Ophthalmic information processing device. 6. The ophthalmologic information processing apparatus according to claim 5, wherein the display control unit causes the display unit to display information indicating the amount of change at the characteristic position in the layer thickness change amount profile. 7. The ophthalmologic information processing apparatus according to claim 5, wherein the display control unit causes the display unit to display information representing an inclination corresponding to the amount of change in the layer thickness at the feature position. The display control unit causes the display means to display the layer thickness variation profile and the tomographic image formed based on the OCT data, and displays information indicating a position corresponding to the characteristic position in the tomographic image. 8. The ophthalmologic information processing apparatus according to any one of claims 5 to 7, wherein the information is displayed on means. A real shape correction unit that performs real shape correction on the OCT data or the tomographic image,
The display control unit displays a corrected tomographic image formed based on the OCT data subjected to actual shape correction by the actual shape correction unit, or the tomographic image subjected to actual shape correction by the actual shape correction unit. The ophthalmologic information processing apparatus according to claim 8, wherein the information is displayed on the display means. An actual shape correction unit that performs actual shape correction on the OCT data,
The layer thickness specifying unit specifies the layer thickness of the predetermined layer region in the A-scan direction based on the OCT data subjected to the actual shape correction by the actual shape correcting unit. The ophthalmologic information processing apparatus according to claim 8 . The feature position specifying unit determines the feature based on the difference in the layer thickness of the A-lines adjacent in the cross direction and the scan angle for each A-line centered on the scan center position of the OCT scan of the eye to be examined. The ophthalmologic information processing apparatus according to any one of claims 1 to 10, characterized by specifying a position. The feature location specifying unit includes:
A smoothing unit that smoothes the layer thickness of the plurality of A lines adjacent in the cross direction in the cross direction,
12. The ophthalmologic information processing apparatus according to claim 11, wherein a characteristic position of the amount of change in the layer thickness is specified based on the layer thicknesses of the plurality of A-lines smoothed by the smoothing unit. 13. The ophthalmologic information processing apparatus according to claim 12, wherein the smoothing unit sequentially obtains a moving average of the layer thicknesses of a plurality of A-lines within a predetermined scan angle range adjacent in the cross direction. The ophthalmologic information processing apparatus according to any one of claims 1 to 13, wherein the characteristic position is a position indicating a maximum value or a local maximum value of the amount of change. The ophthalmologic information processing apparatus according to any one of claims 1 to 14, wherein the predetermined layer region is a choroid. an OCT optical system that includes an optical scanner and obtains the OCT data by projecting measurement light deflected by the optical scanner onto the eye to be examined;
The ophthalmologic information processing apparatus according to any one of claims 1 to 15,
An ophthalmic device, comprising: a layer thickness specifying step of specifying the layer thickness in the A-scan direction of a predetermined layer region in the measurement site based on the OCT data of the eye to be examined;
a feature position specifying step of specifying a feature position of the amount of change in the layer thickness in the direction intersecting the A-scan direction based on the layer thickness specified in the layer thickness specifying step;
An ophthalmic information processing method, comprising: A program that causes a computer to execute each step of the ophthalmologic information processing method according to claim 17.

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