JP2020103440A - Ophthalmologic apparatus, and control method and program of ophthalmologic apparatus - Google Patents

Abstract

To provide a new technology to determine occurrence of a blink of an eye to be examined, fixation displacement, etc. by simple processing.SOLUTION: An ophthalmologic apparatus includes an acquisition unit and a determination unit. The acquisition unit acquires data on an eye to be examined by performing optical coherence tomography to the eye to be examined. The determination unit determines presence or absence of occurrence of a blink of the eye to be examined or fixation displacement based on the data acquired by the acquisition unit.SELECTED DRAWING: Figure 1

Description

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

2. Description of the Related Art In recent years, optical coherence tomography (OCT), which measures or images the shape of an object to be measured using a light beam from a laser light source or the like, has been attracting attention. OCT has no invasiveness to the human body unlike X-ray CT (Computed Tomography), and is therefore expected to be applied particularly in the medical field and biological field. For example, in the field of ophthalmology, a device for forming an image of a fundus, a cornea or the like has been put into practical use. Such a device using OCT (OCT device) is applicable to observation of various parts of the eye to be inspected (fundus or anterior segment). Further, since it is possible to obtain a high-definition image, it is applied to the diagnosis of various eye diseases.

In the measurement using such an OCT apparatus, if the measurement time is long or the skill of the operator of the apparatus is unskilled, there is a high possibility that the eye to be inspected will blink, or the fixation disparity will occur. In these cases, it becomes necessary to perform remeasurement, and work efficiency falls.

When detecting the occurrence of blinking of the eye to be inspected, it is considered to use an anterior segment observation system for observing the anterior segment of the eye. However, this complicates the configuration of the optical system of the apparatus. Therefore, it is desirable to determine the presence or absence of blinking of the subject's eye without using the anterior segment observation system.

For example, Patent Document 1 discloses an apparatus capable of determining continuity of volume data of a tomographic image of an eye to be inspected and performing reimaging according to an instruction from an operator referring to the determination result displayed on the display unit. It is disclosed.

JP, 2010-110656, A

However, in the conventional method, since the continuity of the volume data of the tomographic image is determined by detecting the blood vessel, the processing load becomes heavy, and the occurrence of blinking of the eye to be examined is detected (determined) by a simpler process. Is required.

The present invention has been made in view of such circumstances, and an object thereof is to provide a new technique for determining the occurrence of blinking, fixation disparity, and the like by a simple process.

A first aspect according to some embodiments is an acquisition unit that acquires data of the eye to be inspected by performing optical coherence tomography on the eye to be inspected, and a target based on the data acquired by the acquisition unit. An ophthalmologic apparatus, comprising: a determination unit that determines the occurrence of blinking or fixation disparity of the optometry.

In a second aspect according to some embodiments, in the first aspect, the acquisition unit includes an optical scanner, divides light from a light source into reference light and measurement light, and deflects the light by the optical scanner. Irradiating the eye to be measured with the measurement light, including an interference optical system for detecting the interference light between the reference light and the return light of the measurement light, the determination unit, by the measurement light based on the detection result of the interference light The presence or absence of blinking or fixation disparity of the eye to be inspected is determined based on the brightness profile in the scanning direction.

A third aspect according to some embodiments is the second aspect, including a profile data generation unit that generates an integrated profile by integrating the luminance profile in an integration direction intersecting the scan direction, and the determination unit is The presence or absence of blinking or fixation disparity of the eye to be inspected is determined based on the integrated profile.

A fourth aspect according to some embodiments is the third aspect, including a gradient calculation unit that calculates a gradient of the integrated profile generated by the profile data generation unit, the determination unit, by the gradient calculation unit. The presence or absence of blink or fixation disparity of the eye to be inspected is determined based on the calculated gradient.

A fifth aspect according to some embodiments is the fourth aspect, wherein the gradient calculation unit calculates a gradient at each of a plurality of positions in the scan direction, and the determination unit is calculated by the gradient calculation unit. The presence or absence of blinking or fixation disparity of the subject eye is determined based on the statistical values of the plurality of gradients.

A sixth aspect according to some embodiments is, in any one of the first to fifth aspects, when the determination unit determines that there is blinking or fixation disparity of the eye to be inspected, the acquisition unit. And a control unit that executes reacquisition of the data of the eye to be inspected.

A seventh aspect according to some embodiments is an acquisition step of acquiring data of the eye by performing optical coherence tomography on the eye, and the data based on the data acquired in the acquisition step. And a determination step of determining the presence or absence of blinking or fixation disparity of the eye to be inspected.

In an eighth aspect according to some embodiments, in the seventh aspect, in the obtaining step, the light from the light source is divided into reference light and measurement light, and the measurement light deflected by an optical scanner is used for the eye to be inspected. To obtain the data of the eye to be examined by detecting the interference light between the reference light and the return light of the measurement light, the determination step, the scanning by the measurement light based on the detection result of the interference light The presence or absence of blinking or fixation disparity of the eye to be inspected is determined based on the directional brightness profile.

A ninth aspect according to some embodiments is the eighth aspect, further including a profile data generation step of generating an integrated profile by integrating the luminance profile in an integration direction intersecting the scan direction, and the determination step includes The presence or absence of blinking or fixation disparity of the eye to be inspected is determined based on the integrated profile.

A tenth aspect according to some embodiments includes, in the ninth aspect, a gradient calculation step of calculating a gradient of the integrated profile generated in the profile data generation step, and the determination step is performed in the gradient calculation step. The presence or absence of blink or fixation disparity of the eye to be inspected is determined based on the calculated gradient.

In an eleventh aspect according to some embodiments, in the tenth aspect, the gradient calculation step calculates a gradient at each of a plurality of positions in the scan direction, and the determination step is calculated in the gradient calculation step. The presence or absence of blinking or fixation disparity of the subject eye is determined based on the statistical values of the plurality of gradients.

A twelfth aspect according to some embodiments is, in any one of the seventh aspect to the eleventh aspect, when it is determined in the determination step that there is blinking or fixation disparity of the eye to be inspected. And re-execution of optical coherence tomography to obtain new data of the eye to be examined.

A thirteenth aspect according to some embodiments is a program that causes a computer to execute each step of the method for controlling an ophthalmologic apparatus according to any of the seventh to twelfth aspects.

It is possible to arbitrarily combine the configurations according to the plurality of aspects described above.

According to the present invention, it is possible to provide a new technique for determining occurrence of blinking, fixation disparity, and the like by a simple process.

It is a schematic diagram showing an example of composition of an ophthalmologic apparatus concerning an embodiment. It is a schematic diagram showing an example of composition of an ophthalmologic apparatus concerning an embodiment. It is a schematic diagram showing an example of composition of an ophthalmologic apparatus concerning an 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. 6 is a flowchart illustrating an operation example of the ophthalmologic imaging apparatus according to the embodiment.

Exemplary embodiments of an ophthalmologic apparatus, a method for controlling an ophthalmologic apparatus, and a program according to the present invention will be described in detail with reference to the drawings. It should be noted that the contents of the documents cited in this specification and any known techniques can be applied to the following embodiments.

The ophthalmologic apparatus according to the embodiment acquires data of the eye to be inspected (OCT data) by performing optical coherence tomography (OCT) on the eye to be inspected, and when the data is acquired based on the acquired data. The presence or absence of blinking or fixation disparity of the eye to be examined is determined. This makes it possible to determine whether or not re-imaging (re-measurement) is necessary by determining the suitability of analysis (diagnosis) for the obtained data immediately after performing the OCT and obtaining the data of the eye to be inspected. Therefore, it becomes possible to efficiently acquire the data (image) suitable for the analysis.

The control method of the ophthalmologic apparatus according to the embodiment includes one or more steps for realizing processing executed by a processor (computer) in the ophthalmologic apparatus according to the embodiment. The program according to the embodiment causes a processor to execute each step of the method for controlling the ophthalmologic apparatus according to the embodiment.

In the present specification, the “processor” includes, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an ASIC (Application Specific Integrated Circuit), and a programmable logic device (eg, SPLD (Simple Dimension), programmable logic device (eg, SPLD). It means a circuit such as Programmable Logic Device, FPGA (Field Programmable Gate Array), or the like. The processor implements the functions according to the embodiments by reading and executing a program stored in a storage circuit or a storage device, for example.

The ophthalmologic apparatus according to the embodiment includes an ophthalmologic photographing apparatus and an ophthalmologic measuring apparatus. Examples of the ophthalmologic imaging device include an optical coherence tomography device, a fundus camera, a scanning laser ophthalmoscope (SLO), and a slit lamp. Further, as the ophthalmologic measuring device, there are an eye refraction test device, a tonometer, a specular microscope, a wavefront analyzer, and the like. In the following embodiments, a case where the present invention is applied to an optical coherence tomography will be described, but the present invention can be applied to an ophthalmologic apparatus that combines the functions of an optical coherence tomography and any other apparatus. Is.

In this specification, images acquired by OCT may be collectively referred to as OCT images. Further, the measurement operation for forming the OCT image may be referred to as OCT measurement.

In addition, in the following embodiments, an optical coherence tomography device using a Swept Source type OCT will be described. However, the present invention is applied to an optical coherence tomography using a method other than a swept source, for example, a so-called spectral domain (Spectral Domain) type, an en-face type OCT equipped with a low coherence light source and a spectroscope. It is also possible to apply. In addition, the spectral domain OCT is to divide the light from the low coherence light source into the measurement light and the reference light, and cause the return light of the measurement light from the test object to interfere with the reference light to generate interference light. In this method, the spectral distribution of light is detected by a spectroscope, and the detected spectral distribution is subjected to Fourier transform or the like to form an image. In addition, the en-face type OCT irradiates light having a predetermined beam diameter on an object to be measured, and analyzes the component of interference light obtained by superimposing the reflected light and the reference light, This is a method of forming an image of the object to be measured in a cross section orthogonal to the traveling direction of, and is also called a full-field type.

The ophthalmologic apparatus according to the embodiment can switch the application from fundus measurement to anterior segment measurement by inserting an optical element such as a front lens at a predetermined position of the optical system. The measurement target site is not limited to the fundus and anterior segment, and may be any site of the eye to be inspected, such as the vitreous body or the crystalline lens. Further, it is also possible to prepare optical elements corresponding to the measurement target parts and selectively apply them to the ophthalmologic apparatus. It is also possible to automatically select whether or not an optical element such as a front lens is used and/or to select an applied optical element. These selection processes are performed, for example, on the basis of the imaging details, the name of injury or disease, etc. that have been performed in the past.

In the following, the optical axis direction of the device optical system is the z direction (front-back direction), the horizontal direction orthogonal to the optical axis of the device optical system is the x direction (horizontal direction), and the vertical direction orthogonal to the optical axis of the device optical system. Is the y direction (vertical direction).

[Constitution]
1 and 2 show a configuration example of the ophthalmologic apparatus according to the embodiment. The ophthalmologic apparatus 1 according to the embodiment measures a function of acquiring data of the eye E by performing OCT on the eye E, that is, a function of photographing the eye E and/or a characteristic of the eye E. It has a function.

The ophthalmologic apparatus 1 includes an optical system 10, a processor 50, a face support unit 70, a first drive mechanism 80A, a second drive mechanism 80B, and a user interface (User Interface: UI) unit 90. The configuration may be such that only one of the first drive mechanism 80A and the second drive mechanism 80B is provided.

The optical system 10 is provided with an interference optical system 20, an optical scanner 30, a focusing lens 31, an objective lens 40, and a front lens 41. The focusing lens 31 is configured to be movable in the optical axis direction of the interference optical system 20. In some embodiments, the interference optics 20 includes an optical scanner 30 and a focusing lens 31. The front lens 41 is configured to be insertable/removable between the eye E to be inspected and the objective lens 40.

(Optical system 10)
In addition to the configuration shown in FIG. 1, the optical system 10 may be provided with an optical system (observation optical system, photographing optical system, etc.) for taking an image of the eye E from the front, and an alignment optical system. Further, a configuration for focusing the interference optical system 20 may be provided. Further, the optical system 10 may include a light source for illuminating the anterior segment of the eye E (anterior segment illumination light source).

(Interference optical system 20)
The interference optical system 20 is provided with an optical system for acquiring an OCT image of the fundus Ef of the eye E or the anterior segment of the eye E. This optical system has a configuration similar to that of a conventional swept source type OCT apparatus. That is, as shown in FIG. 2, this optical system splits the light from the wavelength swept light source into the reference light LR and the measurement light LS, and refers to the measurement light LS passing through the fundus or anterior segment and the reference light path. It is configured to interfere with the light LR to generate the interference light LC and detect the spectral intensity distribution of the interference light LC. The detection result (detection signal) is sent to the processor 50.

The light source unit 101 is configured to include a wavelength sweep type (wavelength scanning type) light source capable of sweeping (scanning) the wavelength of emitted light, similarly to a general swept source type ophthalmic apparatus. The wavelength-swept light source includes a laser light source including a resonator. The light source unit 101 temporally changes the output wavelength in the near-infrared wavelength band that cannot be visually recognized by the human eye.

The light L0 output from the light source unit 101 is guided to the polarization controller 103 by the optical fiber 102 and its polarization state is adjusted. The polarization controller 103 adjusts the polarization state of the light L0 guided in the optical fiber 102 by externally applying a stress to the looped optical fiber 102.

The light L0 whose polarization state has been adjusted by the polarization controller 103 is guided to the fiber coupler 105 by the optical fiber 104 and split into the measurement light LS and the reference light LR.

The reference light LR is guided to the collimator 111 by the optical fiber 110, converted into a parallel light flux, and guided to the optical path length changing unit 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 compensating member 113 acts to match the dispersion characteristics between the reference light LR and the measurement light LS. The optical path length changing unit 114 includes, for example, a corner cube and a moving mechanism that moves the corner cube, and the corner cube can be moved by the moving mechanism in the incident direction of the reference light LR. Thereby, the optical path length of the reference light LR is changed.

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

On the other hand, the measurement light LS generated by the fiber coupler 105 is guided by the optical fiber 127, converted into a parallel light flux by the collimator lens unit 128, and passes through the optical scanner 30 and the focusing lens 31. The measurement light LS that has passed through the focusing lens 31 is refracted by the objective lens 40 (front lens 41) and enters the subject's eye E. The measurement light LS is scattered/reflected at various depth positions of the eye E to be inspected. The return light of the measurement light LS from the subject's eye E travels in the same path as the outward path in the opposite direction, is guided to the fiber coupler 105, and reaches the fiber coupler 122 via the optical fiber 129.

The fiber coupler 122 synthesizes (interferes) the measurement light LS incident via the optical fiber 129 and the reference light LR incident via the optical fiber 121 to generate interference light. The fiber coupler 122 splits the interference light at a predetermined splitting ratio (for example, 1:1) to generate a pair of interference light LC. The pair of interference lights LC are guided to the detector 125 through the optical fibers 123 and 124, respectively.

The detector 125 is, for example, a balanced photodiode (Balanced Photo Diode) that has a pair of photo detectors that detect a pair of interference lights LC and that outputs the difference between the detection results of these detectors. The detector 125 sends the detection result (interference signal) to a DAQ (Data Acquisition System) 130. The 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 (scanned) within a predetermined wavelength range by the wavelength swept light source. The light source unit 101 optically delays one of the two branched lights obtained by branching the light L0 of each output wavelength, and then determines the clock KC based on the result of detecting the combined light. To generate. The DAQ 130 samples the detection result of the detector 125 based on the clock KC. The DAQ 130 sends the sampled detector 125 detection results to the processor 50. The processor 50 forms a reflection intensity profile in each A line by performing Fourier transform or the like on the spectral distribution based on the detection result obtained by the detector 125, for example, for each series of wavelength scanning (for each A line). .. Further, the processor 50 forms image data by imaging the reflection intensity profile of each A line.

When this optical system has the same configuration as the spectral domain type OCT device, a light source that outputs a low coherence light source is provided instead of the wavelength swept light source, and an optical member that spectrally decomposes interference light is provided. To be In general, with respect to the configuration of the interference optical system 20, a known technique according to the type of OCT can be arbitrarily applied.

The optical system 10 may include a configuration for providing a function associated with the inspection. For example, a fixation optical system for projecting a target (fixation target) for fixing the eye E to be examined onto the fundus of the eye E may be provided.

(Optical scanner 30)
The optical scanner 30 changes the traveling direction of the measurement light LS. The optical scanner 30 is controlled by the processor 50 (control unit 51) and deflects the measurement light in a direction orthogonal to the traveling direction of the measurement light LS (crosswise in a broad sense) according to a predetermined scan pattern. Thereby, a desired part of the fundus Ef or the anterior segment of the eye can be scanned with the measurement light LS according to the scan pattern. The optical scanner 30 is configured to include, for example, a galvanometer mirror that scans the measurement light in the x direction, a galvanometer mirror that scans the measurement light in the y direction, and a mechanism that drives these independently. This allows the measurement light to scan in any direction on the xy plane.

(Front lens 41)
The front lens 41 is an optical member for changing the focal length of the objective lens 40. The front lens 41 is configured so that it can be inserted/retracted from the optical path toward the subject's eye E. The anterior lens 41 is retracted from the optical path when performing OCT measurement of the fundus, and is disposed in the optical path when performing OCT measurement of the anterior segment. In this embodiment, the front lens 41 is inserted/removed between the eye E to be inspected and the objective lens 40, but may be arranged between the objective lens 40 and the focusing lens 31 (or the optical scanner 30). Good. When the front lens 41 is retracted from between the eye E to be inspected and the objective lens 40, the conjugate position of the optical scanner 30 is arranged in the vicinity of the pupil of the eye E, and the ophthalmologic apparatus 1 can scan the fundus. .. When the front lens 41 is disposed between the eye E to be inspected and the objective lens 40, the conjugate position of the optical scanner 30 is moved to a position different from the anterior segment of the eye E to be examined, and the ophthalmologic apparatus 1 operates the anterior eye. Parts can be scanned.

(Processor 50)
The processor 50 executes various types of information processing. The processor 50 realizes the function according to the embodiment by reading and executing a program stored in a storage circuit or a storage device, for example. At least a part of a memory circuit or a memory device may be included in the processor 50. Further, at least a part of the memory circuit or the memory device may be provided outside the processor 50.

The processor 50 includes a control unit 51, a storage unit 52, an image forming unit 53, and a data processing unit 54. In some embodiments, the processor 50 includes one or more processors that implement the functions of the control unit 51, the image forming unit 53, and the data processing unit 54. For example, the processor 50 includes a control processor that implements the function of the control unit 51, an image forming processor that implements the function of the image forming unit 53, and a data processor that implements the function of the data processing unit 54.

(Control unit 51)
The control unit 51 executes control of each unit of the ophthalmologic apparatus 1. In particular, the control unit 51 controls the optical system 10, the first drive mechanism 80A, and the second drive mechanism 80B.

The control for the optical system 10 includes the control for executing the OCT measurement by the interference optical system 20. In order to execute the OCT measurement, the control unit 51 can control the optical scanner 30 to move the projection position of the measurement light LS on the eye E to be examined according to a predetermined scan pattern. Scan patterns include three-dimensional scan, radial scan, line scan, and circle scan.

Further, the control unit 51 can control the alignment (alignment) of the optical system 10 with respect to the eye E to be inspected. In the case of manual alignment, the control unit 51 receives an operation on the user interface unit 90 by the user and controls at least one of the first drive mechanism 80A and the second drive mechanism 80B, so that the optical system 10 and the eye E to be inspected. Move relative. In the case of automatic alignment, the control unit 51 controls at least one of the first drive mechanism 80A and the second drive mechanism 80B based on the relative position of the optical system 10 and the eye E to be inspected, so that the optical system 10 and the eye E to be inspected. Move E relative to each other. For example, based on a relative position between an image formed by projecting alignment light onto the eye E by an alignment optical system (not shown) and returning light from the eye E and a characteristic position of the eye E, the control unit 51 Can relatively move the optical system 10 and the eye E to be inspected.

(Storage unit 52)
The storage unit 52 stores various data. The data stored in the storage unit 52 includes data acquired by the interference optical system 20 (measurement data, detection result of interference light, etc.), information regarding a subject and an eye to be examined, and the like. The storage unit 52 may store various computer programs and data for operating the ophthalmologic apparatus 1. The storage unit 52 stores various data used and referred to in the processing described later. The storage unit 52 includes the storage circuit and the storage device described above.

(Image forming unit 53)
The image forming unit 53 forms image data of a tomographic image of the subject's eye based on the detection result of the interference light LC obtained by the interference optical system 20. Specifically, the image forming unit 53 forms an OCT image (image data) of the eye E to be inspected, based on the sampling data obtained by sampling the detection signal from the detector 125 with the DAQ 130. The OCT image formed by the image forming unit 53 includes an A scan image, a B scan image (tomographic image), a C scan image, and the like. This processing includes processing such as noise removal (noise reduction), filter processing, dispersion compensation, and FFT (Fast Fourier Transform), as in the conventional swept source type OCT. In the case of another type of OCT device, the image forming unit 53 executes a known process according to the type.

(Data processing unit 54)
The data processing unit 54 executes various types of data processing. For example, the data processing unit 54 performs various types of image processing and analysis processing on the image formed by the image forming unit 53. For example, the data processing unit 54 executes various correction processes such as image brightness correction. Specifically, the data processing unit 54 analyzes the detection result of the interference light obtained by the interference optical system 20 and the image of the eye to be inspected formed by the image forming unit 53.

The data processing unit 54 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 anterior segment. The image data of the three-dimensional image means image data in which the pixel position is defined by the 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 the volume data, the data processing unit 54 performs a rendering process (volume rendering, MIP (Maximum Intensity Projection), etc.) on the volume data, and views it from a specific line-of-sight direction. Image data of a pseudo three-dimensional image at the time of being formed is formed. For example, the pseudo three-dimensional image is displayed on the UI unit 90 including the display device.

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

The data processing unit 54 performs various renderings on the acquired three-dimensional data set (volume data, stack data, etc.) to obtain a B-mode image (longitudinal cross-sectional image, axial cross-sectional image) at an arbitrary cross section and an arbitrary cross section. It is possible to form a C-mode image (transverse sectional image, horizontal sectional image), projection image, shadowgram and the like. An image of an arbitrary cross section such as a B mode image or a C mode image is formed by selecting pixels (pixels, voxels) on a specified cross section from a three-dimensional data set. The projection image is formed by projecting the three-dimensional data set in a predetermined direction (z direction, depth direction, axial direction). The shadowgram is formed by projecting a part of the three-dimensional data set (for example, partial data corresponding to a specific layer) in a predetermined direction. Images such as C-mode images, projection images, and shadowgrams whose viewpoint is the front side of the subject's eye are called front images (en-face images).

The data processing unit 54, based on the data collected in time series by OCT (for example, B scan image data), a B-mode image and a front image (vascular emphasis image, angiogram) in which retinal blood vessels and choroidal blood vessels are emphasized. Can be built. For example, time-sequential OCT data can be collected by repeatedly scanning substantially the same region of the eye E to be inspected.

In some embodiments, the data processing unit 54 compares the time-series B-scan images obtained by the B-scan for substantially the same region, and sets the pixel value of the changing portion of the signal intensity to the pixel value corresponding to the changing portion. By performing the conversion, the emphasized image in which the changed portion is emphasized is constructed. Further, the data processing unit 54 forms an OCTA image by extracting information of a predetermined thickness in a desired portion from the constructed plurality of emphasized images and constructing it as an en-face image.

Images (for example, three-dimensional images, B-mode images, C-mode images, projection images, shadowgrams, OCTA images) generated by the data processing unit 54 are also included in the OCT images.

Further, the data processing unit 54 analyzes the detection result of the interference light LC obtained by the OCT measurement and determines the focus state of the measurement light in the focus fine adjustment control. For example, the control unit 51 performs repetitive OCT measurement while controlling the focusing drive unit that moves the focusing lens 31 in the optical axis direction according to a predetermined algorithm. The data processing unit 54 analyzes the detection result of the interference light repeatedly acquired by the OCT measurement to calculate a predetermined evaluation value regarding the image quality of the OCT image. The data processing unit 54 determines whether the calculated evaluation value is less than or equal to the threshold value. In some embodiments, the focus fine adjustment is continued until the calculated evaluation value is equal to or less than the threshold value. That is, when the evaluation value is equal to or less than the threshold value, the focus state of the measurement light is determined to be appropriate, and the focus fine adjustment is continued until it is determined that the focus state of the measurement light is appropriate.

In some embodiments, the control unit 51 monitors the intensity (interference intensity, interference sensitivity) of the sequentially acquired interference signals while performing the above-described repetitive OCT measurement to acquire the interference signals. .. Further, the position of the focusing lens 31 that maximizes the interference intensity is searched for by moving the focusing lens while performing this monitoring process. With such focus fine adjustment, the focusing lens 31 can be guided to a position where the interference intensity is optimized.

Further, the data processing unit 54 analyzes the detection result of the interference light LC obtained by the OCT measurement and determines the polarization state of at least one of the measurement light and the reference light. For example, the control unit 51 performs repetitive OCT measurement while controlling at least one of the polarization controllers 103 and 118 according to a predetermined algorithm. In some embodiments, the control unit 51 controls the attenuator 120 to change the attenuation amount of the reference light LR. The data processing unit 54 analyzes the detection result of the interference light LC repeatedly acquired by the OCT measurement to calculate a predetermined evaluation value regarding the image quality of the OCT image. The data processing unit 54 determines whether the calculated evaluation value is less than or equal to the threshold value. This threshold is set in advance. The polarization adjustment is continued until the calculated evaluation value becomes equal to or less than the threshold value. That is, when the evaluation value is equal to or less than the threshold value, it is determined that the polarization state of the measurement light LS is proper, and the polarization adjustment is continued until it is determined that the polarization state of the measurement light LS is proper.

In some embodiments, the control unit 51 can monitor the interference intensity even in polarization adjustment.

The data processing unit 54 is provided with an analysis unit 300 for analyzing the acquired detection result of the interference light LC and the image.

(Analysis unit 300)
The analysis unit 300 can perform at least an analysis process for determining the presence or absence of blinking or fixation disparity of the eye E to be inspected. As an example of a configuration for performing such analysis processing, the analysis unit 300 is provided with a blink determination unit 310. The blink determination unit 310 determines whether or not there is blinking or fixation disparity of the eye E based on the acquired detection result of the interference light LC.

FIG. 3 shows a block diagram of a configuration example of the analysis unit 300 according to the embodiment.

The analysis unit 300 includes a blink determination unit 310. The blink determination unit 310 determines the presence or absence of blinking or fixation disparity of the eye E to be inspected based on the brightness profile in the scan direction of the measurement light based on the acquired detection result of the interference light LC.

(Blink determination unit 310)
The blink determination unit 310 includes a profile data generation unit 311, a gradient calculation unit 312, and a gradient determination unit 313.

(Profile data generation unit 311)
4 and 5 show operation explanatory diagrams of the blink determination unit 310 according to the embodiment. FIG. 4 shows a projection image IMG of the fundus oculi Ef of the eye E for convenience, in order to explain the integration direction DR described later.

The profile data generation unit 311 generates integrated profile data in which the brightness profile in the B scan direction is integrated in the integration direction DR intersecting (orthogonal to) the B scan direction.

In some embodiments, the profile data generation unit 311 specifies the brightness profile in the B-scan direction from the image data of the projection image generated by the data processing unit 54, as shown in FIG. Integration profile data is generated by integrating the brightness profile in the B-scan direction in the integration direction DR. For example, the profile data generation unit 311 integrates the x-direction luminance profile of the projection image IMG of FIG. 4 in the integration direction DR corresponding to the y-direction of the projection image IMG to obtain integrated profile data as shown in FIG. 7. To generate.

In some embodiments, the profile data generation unit 311 changes from the reflection intensity profile of each A line acquired by performing Fourier transform or the like to the spectral distribution based on the detection result obtained by the detector 125 in the B scan direction. Generate a brightness profile. For example, the brightness value at the A scan position is obtained by integrating the reflection intensity values corresponding to a predetermined layer region (or the entire layer region in the z direction) in the reflection intensity profile, and a data set is formed in the B scan direction. Then, a brightness profile in the B-scan direction is generated. The profile data generation unit 311 generates integrated profile data by integrating the generated plurality of brightness profiles in the B scan direction in the integration direction DR.

(Slope calculation unit 312)
The gradient calculation unit 312 calculates the gradient of the integrated profile at one or more positions (pixel position, scan position) in the x direction. As illustrated in FIG. 5, when the horizontal axis represents the position in the x direction and the vertical axis represents the integrated value, the integrated profile represents the integrated value at each position in the x direction.

In some embodiments, the gradient calculation unit 312 calculates the gradient of the integrated profile at all positions in the x direction (B scan direction). In some embodiments, the gradient calculator 312 calculates the gradient of the integrated profile at two or more positions in the B-scan direction at predetermined intervals.

(Slope determination unit 313)
The gradient determining unit 313 determines whether or not blinking occurs from the gradient calculated by the gradient calculating unit 312, paying attention to the fact that the gradient of the integrated profile becomes steep at the position where the artifact caused by the blinking is drawn. To do. For example, the gradient determining unit 313 identifies the representative value of the gradient at the two or more positions calculated by the gradient calculating unit 312. The gradient determination unit 313 determines that the image has blinks when the identified representative value is equal to or greater than the predetermined first threshold value, and the blinks occur when the identified representative value is less than the predetermined first threshold value. It is determined that the image has not been processed. The representative value includes the maximum value of the absolute value of the gradient, the average value of the absolute value of the gradient, the median value of the absolute value of the gradient, and the mode of the absolute value of the gradient.

Further, the gradient determination unit 313 determines whether or not there is fixation disparity from the gradient calculated by the gradient calculation unit 312, focusing on the fact that the steeper the gradient of the integrated profile, the higher the possibility of fixation disparity. Is possible. Also in this case, the gradient determining unit 313 determines that the image has fixation disparity when the representative value of the gradient at the two or more positions calculated by the gradient calculating unit 312 is equal to or more than the predetermined second threshold, When the specified representative value is less than the predetermined second threshold value, it is determined that the image has no fixation disparity. The second threshold may be a value different from the first threshold. Further, the second threshold may be the same value as the first threshold.

(Face support 70)
The face supporting unit 70 includes a member for supporting the face of the subject. For example, the face support unit 70 includes a forehead support on which the subject's forehead is in contact, and a chin rest on which the subject's chin is placed. The face support portion 70 may include only one of the forehead support and the chin rest, or may include members other than these.

(First drive mechanism 80A, second drive mechanism 80B)
The first drive mechanism 80A moves the optical system 10 under the control of the control unit 51. The first drive mechanism 80A can move the optical system 10 three-dimensionally. The first drive mechanism 80A includes, for example, a mechanism for moving the optical system 10 in the x direction, a mechanism for moving the optical system 10 in the y direction, and a mechanism for moving the optical system 10 in the z direction, as in the conventional case. The first drive mechanism 80A includes a plurality of stepping motors and the like (driving means) that drives a mechanism for moving in the x direction, the y direction, and the z direction. For example, the control unit 51 can move the optical system 10 by a movement amount corresponding to the number of pulses by supplying a driving signal of a predetermined number of pulses to the stepping motor.

The second drive mechanism 80B moves the face support 70 under the control of the controller 51. The second drive mechanism 80B can move the face support portion 70 three-dimensionally. The second drive mechanism 80B includes, for example, a mechanism similar to the first drive mechanism 80A. Note that, as described above, generally, at least one of the first drive mechanism 80A and the second drive mechanism 80B is provided. Further, the first drive mechanism 80A may move the optical system 10 three-dimensionally, and the second drive mechanism 80B may move the face support portion 70 only in the vertical direction.

(User interface unit 90)
The user interface unit 90 provides functions for exchanging information between the ophthalmologic apparatus 1 and its user, such as displaying information, inputting information, and inputting operation instructions. The user interface unit 90 provides an output function and an input function. Examples of configurations that provide an output function include a display device such as a flat panel display, an audio output device, a print output device, and a data writer that writes to a recording medium. Examples of configurations that provide an input function include operating levers, buttons, keys, pointing devices, microphones, and data writers. The user interface unit 90 may include a device such as a touch panel display in which an output function and an input function are integrated. The user interface unit 90 may also include a graphical user interface (GUI) for inputting/outputting information.

The optical system 10 (and the image forming unit 53 and the data processing unit 54) is an example of the “acquisition unit” according to the embodiment. The blink determination unit 310 is an example of a “determination unit” according to the embodiment.

[motion]
The operation of the ophthalmologic apparatus 1 according to the embodiment will be described.

FIG. 6 shows an operation example of the ophthalmologic apparatus 1 according to the embodiment. FIG. 6 shows a flowchart of an operation example of the ophthalmologic apparatus 1 according to the embodiment. The storage unit 52 stores a computer program for implementing the processing shown in FIG. The control unit 51 executes the processing shown in FIG. 6 by operating according to this computer program.

(S1: alignment)
The control unit 51 executes alignment.

That is, the control unit 51 receives an operation on the user interface unit 90 by the user and controls at least one of the first drive mechanism 80A and the second drive mechanism 80B to move the optical system 10 and the eye E relative to each other. (Manual alignment). When performing automatic alignment, the control unit 51 controls an alignment optical system (not shown) to project an alignment index on the eye E to be inspected. At this time, a fixation target by a fixation optical system (not shown) is also projected onto the eye E to be examined. The control unit 51 controls at least one of the first drive mechanism 80A and the second drive mechanism 80B based on the relative position between the image formed based on the return light from the eye E and the characteristic position of the eye E. By doing so, the optical system 10 and the subject's eye E are moved relative to each other. The control unit 51 repeatedly executes this processing.

(S2: Acquisition of a tomographic image for adjustment)
For example, the control unit 51 controls the OCT unit 100 to execute the OCT provisional measurement in a state where the eye E to be inspected is fixed at a desired fixation position by a fixation optical system (not shown), and the depth direction measurement An adjustment tomographic image for adjusting the reference position of the range is acquired.

Specifically, the control unit 51 controls the optical scanner 30 to deflect the measurement light LS generated based on the light L0 emitted from the light source unit 101, and the deflected measurement light LS causes the eye to be inspected. A predetermined region of E (for example, fundus Ef) is scanned. The detection result of the interference light obtained by the scanning of the measurement light LS is sampled in synchronization with the clock KC and then sent to the image forming unit 53. The image forming unit 53 forms a tomographic image (OCT image) of the eye E from the obtained interference signal.

(S3: Adjust the reference position in the depth direction)
Subsequently, the control unit 51 adjusts the reference position of the measurement range in the depth direction (z direction).

For example, the control unit 51 causes the data processing unit 54 to specify a predetermined site (for example, the sclera) in the tomographic image obtained in step S2, and a predetermined position in the depth direction with respect to the position of the specified predetermined site. The position separated by the distance of is set as the reference position of the measurement range. Further, a predetermined position that is determined in advance so that the optical path lengths of the measurement light LS and the reference light LR are substantially the same may be set as the reference position of the measurement range.

(S4: Focus adjustment, polarization adjustment)
Next, the control unit 51 executes focus adjustment control and polarization adjustment control.

For example, the control unit 51 controls the focusing drive unit that moves the focusing lens 31 to move the focusing lens 31 by a predetermined distance, and then controls the OCT unit 100 to execute the OCT measurement. As described above, the control unit 51 causes the data processing unit 54 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 54, the control unit 51 controls the focus drive unit again and determines that the focus state is appropriate. Repeat until

Further, for example, the control unit 51 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. Then, the OCT measurement is executed and the OCT image based on the acquired detection result of the interference light is formed in the image forming unit 53. As described above, the control unit 51 causes the data processing unit 54 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 54, the control unit 51 controls the polarization controllers 103 and 118 again, and the polarization state is appropriate. Repeat until it is determined that there is.

(S5: OCT measurement)
Subsequently, the control unit 51 controls the OCT unit 100 to execute the OCT measurement. The detection result of the interference light obtained by the OCT measurement is sampled by the DAQ 130 and stored in the storage unit 52 or the like as an interference signal.

In some embodiments, in step S5, the control unit 51 controls the image forming unit 53 to form an image of the eye E to be inspected based on the detection result of the interference light acquired by the OCT measurement.

(S6: determination process)
Next, the control unit 51 controls the blink determination unit 310 to execute the determination process on the detection result or the image of the interference light acquired in step S5. As described above, the blink determination unit 310 determines the presence or absence of blink or fixation disparity based on the detection result or image of the interference light acquired in step S5.

(S7: Remeasurement?)
The control unit 51 determines whether to perform remeasurement based on the determination result of the determination process in step S5.

When the blink determination unit 310 determines in step S6 that there is blinking or fixation disparity (S7:Y), the operation of the ophthalmologic apparatus 1 proceeds to step S5. When the blink determination unit 310 determines in step S6 that there is no blink or fixation disparity (S7:N), the operation of the ophthalmologic apparatus 1 proceeds to step S8.

In some embodiments, when transitioning from step S7 to step S5, the control unit 51 informs the user to perform remeasurement. The notification of the user includes displaying information indicating that the UI unit 90 performs remeasurement and outputting a sound indicating that remeasurement is performed. In some embodiments, in the OCT remeasurement at the time of shifting from step S7 to step S5, the imaging condition is changed so as to suppress the occurrence of blinking or fixation disparity (for example, changing the imaging rate or the imaging timing). .. In some embodiments, the information indicating the remeasurement is added to the measurement result (image) obtained by the OCT remeasurement at the time of shifting from step S7 to step S5.

(S8: Next?)
Subsequently, the control unit 51 determines whether to continue the OCT measurement. The control unit 51 determines whether or not to continue the OCT measurement according to the operation content of the user on the UI unit 90 or the content of the operation mode set in advance.

When it is determined to continue the OCT measurement (S8:Y), the operation of the ophthalmologic apparatus 1 proceeds to step S9. When it is determined that the OCT measurement is not continued (S8:N), the operation of the ophthalmologic apparatus 1 ends (end).

(S9: Alignment?)
When it is determined in step S8 that the OCT measurement is to be continued (S8:Y), the control unit 51 determines whether or not to execute alignment again before the OCT measurement. The control unit 51 executes the realignment according to the operation content of the user on the UI unit 90, the content of the preset operation mode, or the positional relationship between the eye E to be inspected and the optical system detected by the detection unit (not shown). Or not.

When it is determined to re-execute the alignment (S9:Y), the operation of the ophthalmologic apparatus 1 shifts to step S1. When it is determined that the alignment is not re-executed (S9:N), the operation of the ophthalmologic apparatus 1 proceeds to step S5.

As described above, the presence or absence of blinking or fixation disparity of the eye E to be inspected is determined based on the luminance profile (integrated profile) obtained from the detection result of the interference light LC obtained by the OCT measurement. Therefore, it is possible to determine whether or not a blink has occurred by a simple process. Thereby, immediately after acquiring the data of the eye to be inspected by performing the OCT, it is possible to easily judge the necessity of reimaging (remeasurement) by judging the suitability of the analysis (diagnosis) for the acquired data. Therefore, it becomes possible to efficiently acquire the data (image) suitable for the analysis.

[effect]
The ophthalmologic apparatus, the control method of the ophthalmologic apparatus, and the program according to the embodiment will be described.

The ophthalmologic apparatus (1) according to some embodiments includes an acquisition unit (the optical system 10 (and the image forming unit 53, the data processing unit 54)) and a determination unit (blink determination unit 310). The acquisition unit acquires optical data (OCT data) of the eye to be inspected (E) by performing optical coherence tomography. The determination unit determines the presence or absence of blinking or fixation disparity of the eye to be inspected based on the data acquired by the acquisition unit.

According to such a configuration, it is possible to easily determine the presence or absence of blinking of the eye to be inspected by a simple process without providing an anterior segment observation system for observing the anterior segment of the eye to be inspected. Become.

In the ophthalmologic apparatus according to some embodiments, the acquisition unit includes an optical scanner (30) and splits the light (L0) from the light source (light source unit 101) into reference light (LR) and measurement light (LS). Then, the determination unit includes an interference optical system (20) for irradiating the eye to be inspected with the measurement light deflected by the optical scanner and detecting the interference light (LC) between the reference light and the return light of the measurement light. The presence or absence of blinking or fixation disparity of the eye to be inspected is determined based on the brightness profile in the scan direction (B scan direction) by the measurement light based on the detection result of 1.

According to such a configuration, it is possible to determine the occurrence of blinking or fixation disparity of the eye to be examined based on the brightness profile obtained by performing the OCT on the eye to be examined, It is possible to simplify the configuration of the ophthalmologic apparatus that can determine the occurrence of blinking and the like.

An ophthalmologic apparatus according to some embodiments includes a profile data generation unit (311) that generates a cumulative profile by integrating luminance profiles in a cumulative direction (DR) that intersects the scan direction, and the determination unit is a cumulative profile. The presence or absence of blinking or fixation disparity of the eye to be inspected is determined based on.

According to such a configuration, the integrated profile is generated from the brightness profile, and the presence or absence of blinking or fixation disparity of the eye to be inspected is determined from the generated profile, so that simple processing can be performed with high accuracy. It is possible to easily determine whether or not the blink of the optometry has occurred.

The ophthalmologic apparatus according to some embodiments includes a gradient calculation unit (312) that calculates the gradient of the integrated profile generated by the profile data generation unit, and the determination unit is based on the gradient calculated by the gradient calculation unit. The presence or absence of blinking or fixation disparity of the eye to be inspected is determined.

According to such a configuration, the gradient of the integrated profile is calculated, and the presence or absence of blinking or fixation disparity of the eye to be inspected is determined from the calculated gradient, so that the eye to be inspected with high accuracy with simple processing. It becomes possible to easily determine the presence or absence of the occurrence of the blink.

In the ophthalmologic apparatus according to some embodiments, the gradient calculation unit calculates the gradient at each of the plurality of positions in the scanning direction, the determination unit, based on the statistical value of the plurality of gradients calculated by the gradient calculation unit. The presence or absence of blinking or fixation disparity of the eye to be inspected is determined.

According to such a configuration, the statistical value of the gradient of the integrated profile is calculated, and the presence or absence of blinking or fixation disparity of the eye to be inspected is determined from the calculated statistical value of the gradient, so that a simple process is performed. Thus, it becomes possible to easily determine with high accuracy whether or not a blink of the eye to be examined has occurred.

Ophthalmologic apparatus according to some embodiments, when it is determined by the determination unit that there is blinking or fixation disparity of the eye to be inspected, the acquisition unit is controlled to control re-acquisition of data of the eye to be inspected. Including part (51).

According to such a configuration, the presence or absence of blinking or fixation disparity of the eye to be inspected is determined by a simple process, and the re-acquisition of the data of the eye to be inspected is performed based on the determination result. Immediately after acquiring the data of the optometry, it becomes possible to easily judge the necessity of re-acquisition by judging the suitability of analysis (diagnosis) for the acquired data. Thereby, it becomes possible to efficiently acquire the data suitable for the analysis.

The control method of the ophthalmologic apparatus (1) according to some embodiments includes an acquisition step and a determination step. In the acquisition step, the data of the eye (E) to be inspected is acquired by executing optical coherence tomography on the eye (E) to be inspected. The determination step determines the presence or absence of blinking or fixation disparity of the eye to be inspected based on the data acquired in the acquisition step.

According to such a method, it is possible to easily determine the presence or absence of blinking of the eye to be inspected by a simple process without providing an anterior segment observation system for observing the anterior segment of the eye to be inspected. Become.

In the control method of the ophthalmologic apparatus according to some embodiments, in the acquisition step, the light (L0) from the light source (light source unit 101) is divided into reference light (LR) and measurement light (LS), and an optical scanner ( 30) The measurement light deflected by 30) is applied to the eye to be inspected, and the interference light (LC) between the reference light and the return light of the measurement light is detected to obtain the data of the eye to be inspected. The presence or absence of blinking or fixation disparity of the eye to be inspected is determined based on the brightness profile in the scanning direction by the measurement light based on the detection result.

According to such a method, it is possible to determine the presence or absence of blinking or fixation disparity of the eye to be inspected based on the brightness profile obtained by performing the OCT on the eye to be inspected. It is possible to simplify the configuration of the ophthalmologic apparatus that can determine the occurrence of blinking and the like.

A method of controlling an ophthalmologic apparatus according to some embodiments includes a profile data generation step of generating an integrated profile by integrating a brightness profile in an integrated direction (DR) intersecting a scan direction, and the determination step includes an integrated profile. The presence or absence of blinking or fixation disparity of the eye to be inspected is determined based on.

According to such a method, the integrated profile is generated from the luminance profile, and the presence or absence of blinking or fixation disparity of the eye to be inspected is determined from the generated profile. It is possible to easily determine whether or not the blink of the optometry has occurred.

The control method of the ophthalmologic apparatus according to some embodiments includes a gradient calculation step of calculating a gradient of the integrated profile generated in the profile data generation step, and the determination step is based on the gradient calculated in the gradient calculation step. The presence or absence of blinking or fixation disparity of the eye to be inspected is determined.

According to such a method, the gradient of the integrated profile is calculated, and the presence or absence of blinking or fixation disparity of the eye to be inspected is determined from the calculated gradient, so that the eye to be inspected with high accuracy with simple processing. It becomes possible to easily determine the presence or absence of the occurrence of the blink.

In the control method of the ophthalmologic apparatus according to some embodiments, the gradient calculation step calculates a gradient at each of a plurality of positions in the scanning direction, and the determination step, a statistical value of the plurality of gradients calculated in the gradient calculation step. The presence or absence of blinking or fixation disparity of the eye to be inspected is determined based on.

According to such a method, the statistical value of the gradient of the integrated profile is calculated, and the presence or absence of blinking or fixation disparity of the eye to be inspected is determined from the statistical value of the calculated gradient, so that a simple process is performed. Thus, it becomes possible to easily determine with high accuracy whether or not a blink of the eye to be examined has occurred.

The control method of the ophthalmologic apparatus according to some embodiments, when it is determined that there is blinking or fixation disparity of the eye to be inspected in the determination step, the eye to be inspected by re-executing optical coherence tomography. Including a control step for acquiring new data of.

According to such a method, the presence or absence of blinking or fixation disparity of the eye to be examined is determined by a simple process, and the re-acquisition of the data of the eye to be examined is performed based on the determination result. Immediately after acquiring the data of the optometry, it becomes possible to easily judge the necessity of re-acquisition by judging the suitability of analysis (diagnosis) for the acquired data. Thereby, it becomes possible to efficiently acquire the data suitable for the analysis.

A program according to some embodiments causes a computer to execute each step of the method for controlling an ophthalmologic apparatus described in any of the above.

According to such a program, it is possible to easily determine the presence or absence of blinking of the eye to be inspected by a simple process without providing an anterior segment observation system for observing the anterior segment of the eye to be inspected. Become.

<Other>
In the above embodiment, a case has been mainly described in which the presence or absence of blinking is determined based on the data (image) obtained by performing the OCT on the fundus Ef of the eye E to be examined. The configuration according to is not limited to this. The above embodiment can be applied to the case where OCT is performed on an arbitrary part of the eye E to be inspected such as the anterior segment.

The embodiments described above are merely examples for implementing the present invention. A person who intends to carry out the present invention can make arbitrary modifications, omissions, additions, etc. within the scope of the present invention.

In some embodiments, a program for causing a computer to execute the above method for controlling an ophthalmologic apparatus is provided. Such a program can be stored in any computer-readable recording medium. As the recording medium, for example, a semiconductor memory, an optical disk, a magneto-optical disk (CD-ROM/DVD-RAM/DVD-ROM/MO, etc.), a magnetic storage medium (hard disk/floppy (registered trademark) disk/ZIP, etc.), etc. Can be used. It is also possible to send and receive this program through a network such as the Internet or LAN.

1 Ophthalmologic apparatus 10 Optical system 20 Interference optical system 30 Optical scanner 31 Focusing lens 40 Objective lens 41 Front lens 50 Processor 51 Control section 52 Storage section 53 Image forming section 54 Data processing section 300 Analysis section 310 Blink determination section 311 Profile data Generation unit 312 Gradient calculation unit 313 Gradient determination unit E Eye to be examined

Claims (13)

An acquisition unit that acquires data of the eye to be inspected by performing optical coherence tomography on the eye to be inspected,
A determination unit that determines the presence or absence of blinking or fixation disparity of the eye to be inspected based on the data acquired by the acquisition unit,
Including an ophthalmic device. The acquisition unit is
An optical scanner is included, the light from the light source is divided into reference light and measurement light, the measurement light deflected by the light scanner is irradiated to the eye to be examined, and the reference light and return light of the measurement light Including an interference optical system that detects the interference light,
The determination unit determines the presence or absence of blinking or fixation disparity of the eye to be inspected based on a brightness profile in the scanning direction by the measurement light based on the detection result of the interference light. The described ophthalmic device. A profile data generation unit that generates an integrated profile by integrating the brightness profiles in an integration direction intersecting the scanning direction,
The ophthalmologic apparatus according to claim 2, wherein the determination unit determines the presence or absence of blinking or fixation disparity of the eye to be inspected based on the integrated profile. A gradient calculator that calculates a gradient of the integrated profile generated by the profile data generator,
The ophthalmologic apparatus according to claim 3, wherein the determination unit determines the presence or absence of blinking or fixation disparity of the eye to be inspected based on the gradient calculated by the gradient calculation unit. The gradient calculator calculates a gradient at each of a plurality of positions in the scan direction,
The ophthalmology according to claim 4, wherein the determination unit determines the presence or absence of blinking or fixation disparity of the eye to be inspected based on statistical values of a plurality of gradients calculated by the gradient calculation unit. apparatus. When the determination unit determines that there is blinking or fixation disparity of the eye to be inspected, the control unit controls the acquisition unit to reacquire data of the eye to be inspected. The ophthalmologic apparatus according to any one of claims 1 to 5. An acquisition step of acquiring data of the eye to be examined by performing optical coherence tomography on the eye to be examined;
A determination step of determining the presence or absence of blink occurrence or fixation disparity of the eye to be inspected based on the data acquired in the acquisition step,
A method for controlling an ophthalmologic apparatus, comprising: The acquisition step divides the light from the light source into reference light and measurement light, irradiates the measurement light deflected by an optical scanner to the eye to be inspected, and interferes with the reference light and return light of the measurement light. Obtaining the data of the eye to be examined by detecting light,
The determining step determines the presence or absence of blinking or fixation disparity of the eye to be inspected based on a brightness profile in a scanning direction by the measurement light based on the detection result of the interference light. A method for controlling the described ophthalmologic apparatus. A profile data generating step of generating an integrated profile by integrating the luminance profiles in an integration direction intersecting the scanning direction,
The control method of the ophthalmologic apparatus according to claim 8, wherein the determining step determines whether or not blinking or fixation disparity is present in the eye to be inspected based on the integrated profile. A gradient calculation step of calculating a gradient of the integrated profile generated in the profile data generation step,
The control method of the ophthalmologic apparatus according to claim 9, wherein the determination step determines presence or absence of blinking or fixation disparity of the eye to be inspected based on the gradient calculated in the gradient calculation step. .. The gradient calculation step calculates a gradient at each of a plurality of positions in the scan direction,
The ophthalmology according to claim 10, wherein the determination step determines presence/absence of blinking or fixation disparity of the eye to be inspected based on statistical values of a plurality of gradients calculated in the gradient calculation step. Device control method. When it is determined that there is a blink occurrence or fixation disparity of the eye to be examined in the determination step, a control step to obtain new data of the eye to be examined by re-executing optical coherence tomography on the eye to be examined. The method for controlling an ophthalmologic apparatus according to any one of claims 7 to 11, comprising: A program for causing a computer to execute each step of the method for controlling an ophthalmologic apparatus according to any one of claims 7 to 12.

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