JP2022031533A - Ophthalmology imaging apparatus - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an ophthalmology imaging apparatus capable of acquiring a highly accurate OCT image even at the occurrence of the movement of a subject eye.

SOLUTION: The ophthalmology imaging apparatus according to embodiment executes a series of scanning (unit scanning) on a plurality of paths. The unit scanning successively executes a predetermined number of times of scanning on the plurality of paths and thereby collects a predetermined number of data sets corresponding to the respective paths. The ophthalmology imaging apparatus executes processing of obtaining characteristic information of the respective data sets, processing of calculating errors of each of a plurality of pairs made of a predetermined number of combinations having different characteristic information with respect to the respective paths, and processing of identifying the maximum value and the minimum value in the plurality of calculated errors. In a case where a difference between the maximum value and the minimum value among a plurality of maximum values and a plurality of minimum values identified with respect to the respective paths exceeds a threshold, the apparatus determines that displacement of a subject eye has occurred during the unit scanning.

SELECTED DRAWING: Figure 5

COPYRIGHT: (C)2022,JPO&INPIT

Description

The present invention relates to an ophthalmologic imaging apparatus that images an eye to be inspected using optical coherence tomography (OCT).

Diagnostic imaging occupies an important position in the field of ophthalmology. In recent years, the use of OCT has been advancing. OCT has come to be used not only for acquiring B-mode images and three-dimensional images of the eye to be inspected, but also for acquiring front images (en-face images) such as C-mode images and shadowgrams. In addition, it is also performed to acquire an image emphasizing a specific part of the eye to be inspected and to acquire functional information. For example, based on the time series data collected by OCT, it is possible to construct an image (angiogram) in which retinal blood vessels and choroidal blood vessels are emphasized. Further, it is also possible to obtain blood flow information (blood flow velocity, blood flow volume, etc.) from the phase information in the time series data collected by OCT. Such an imaging technique is disclosed in, for example, Patent Document 1-3. Further, there is also known a technique of repeatedly scanning the same cross section to acquire a plurality of images and adding and averaging them to create a low noise image (see, for example, Patent Document 4).

In the above imaging technology, three-dimensional scanning and repeated scanning are applied. Three-dimensional scanning and repeated scanning take several seconds to ten seconds, and in some cases even longer. Therefore, the position of the eye to be inspected may shift or blink may occur during scanning. In view of these problems, tracking and rescanning are used. Tracking is a technique for monitoring the movement of the eye to be inspected during scanning with a video camera and controlling the optical scanner in real time according to the movement (see, for example, Patent Document 5). Rescan is a technique for monitoring the eye to be inspected with a video camera during scanning and rescanning the scanned position at the timing when the eye to be inspected moves significantly or when blinking occurs (see, for example, Patent Document 6). ..

Japanese Unexamined Patent Publication No. 2014-200680 Japanese Patent Publication No. 2015-515894 Special Table 2010-523286 Gazette Japanese Unexamined Patent Publication No. 2011-120655 Japanese Patent Publication No. 2014-512245 Japanese Unexamined Patent Publication No. 2015-83248

In conventional tracking and rescanning, the image taken by the video camera is analyzed to detect the movement or blinking of the eye to be inspected. On the other hand, due to recent advances in OCT technology, the repetition rate of OCT scans (for example, the repetition rate of B scans) is considerably higher than the frame rate of video cameras. For example, the typical B-scan repetition interval is about 2 to 3 ms, while the frame rate of the video camera is about 20 to 50 FPS (frame interval is about 20 to 50 ms). Therefore, the movement of the eye to be inspected, which cannot be detected by the video camera, may affect the OCT image. Further, there are problems that the scan affected by the movement of the eye to be inspected cannot be identified and that it takes time to identify the scan. Although it is possible to shorten the interval for detecting the movement of the eye to be inspected, it is not realistic because a very expensive imaging device is required.

An object of the present invention is to provide an ophthalmologic imaging apparatus capable of acquiring a highly accurate OCT image even when the eye to be examined moves.

The ophthalmologic imaging apparatus of the embodiment is preset with a data collection unit that collects data by scanning the eye to be inspected using optical coherence stromography, and an imaging unit that photographs the eye to be inspected to acquire a front image. A control unit that controls the data collection unit to perform a unit scan consisting of a series of scans for the route group, a series of data collected by the series of scans, and the photographing unit corresponding to the series of scans. The route group includes a plurality of routes having different positions from each other, and includes an abnormality detection unit for detecting an abnormality based on two or more front images including one or more front images acquired by the above-mentioned data collection. The unit performs B scans sequentially at the first rate for the plurality of routes, and the photographing unit acquires two or more front images at a second rate slower than the first rate, and the above-mentioned The abnormality detection unit includes a first abnormality detection unit that detects the occurrence of displacement of the eye to be inspected based on all of a series of data collected from the plurality of paths at the first rate by the data collection unit, and the above-mentioned abnormality detection unit. The series of scans includes the plurality of scans including a second abnormality detecting unit that detects the amount of the displacement of the eye to be inspected based on the two or more front images acquired by the photographing unit at the second rate. The series of data includes a predetermined number of data sets corresponding to the respective routes of the plurality of routes, and the first abnormality detection unit includes scans executed sequentially and a predetermined number of times for the routes. A plurality of data sets calculated by obtaining the characteristic information of each of the predetermined number of data sets and calculating the error of each of a plurality of pairs consisting of different combinations of the predetermined number of characteristic information for each route of the plurality of routes. When the maximum value and the minimum value of the errors of the above are specified, and the difference between the maximum value and the minimum value of the plurality of maximum values and the plurality of minimum values specified for the plurality of routes exceeds the threshold value, the series is described. It is determined that the displacement of the subject eye has occurred during the scan.

According to the ophthalmologic imaging apparatus according to the embodiment, it is possible to acquire a highly accurate OCT image even when the eye to be inspected moves.

The schematic diagram which shows the example of the structure of the ophthalmologic imaging apparatus which concerns on embodiment. The schematic diagram which shows the example of the structure of the ophthalmologic imaging apparatus which concerns on embodiment. The schematic diagram which shows the example of the structure of the ophthalmologic imaging apparatus which concerns on embodiment. The schematic diagram which shows the example of the operation of the ophthalmologic imaging apparatus which concerns on embodiment. The schematic diagram which shows the example of the operation of the ophthalmologic imaging apparatus which concerns on embodiment. The flow chart which shows the example of the operation of the ophthalmologic imaging apparatus which concerns on embodiment. The schematic diagram for demonstrating the operation example of the ophthalmologic imaging apparatus which concerns on embodiment.

Some embodiments of the present invention will be described in detail with reference to the drawings. An embodiment is an ophthalmologic imaging apparatus having a function as an optical coherence tomography (OCT) and a function of acquiring a frontal image of an eye to be inspected. The latter function can be realized by, for example, a fundus camera, a scanning laser ophthalmoscope (SLO), a slit lamp microscope, an ophthalmic surgery microscope, an anterior ocular segment photographing camera and the like. Hereinafter, an example in which a swept source OCT and a fundus camera are combined will be described, but the embodiment is not limited to this.

<Constitution>
As shown in FIG. 1, the ophthalmologic photographing apparatus 1 includes a fundus camera unit 2, an OCT unit 100, and an arithmetic control unit 200. The fundus camera unit 2 is provided with an optical system and a mechanism for acquiring a front image of the eye to be inspected. The OCT unit 100 is provided with an optical system and a mechanism for executing OCT. The arithmetic control unit 200 includes a processor that executes various arithmetic operations and controls. In addition to these, even if a member for supporting the subject's face (chin rest, forehead pad, etc.) and a lens unit for switching the target part of OCT (for example, an attachment for anterior ocular segment OCT) are provided. good.

In the present 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, a SPLD (Simple It means a circuit such as Programmable Logic Device), FPGA (Field Programgable Gate Array)). The processor realizes the function according to the embodiment by reading and executing a program stored in a storage circuit or a storage device, for example.

<Fundus camera unit 2>
The fundus camera unit 2 is provided with an optical system for photographing the fundus Ef of the eye to be inspected E. The acquired image of the fundus Ef (called a fundus image, a fundus photograph, etc.) is a front image such as an observation image, a photographed image, or the like. The observed image is obtained by taking a moving image using near-infrared light. The captured image is a still image using flash light.

The fundus camera unit 2 includes an illumination optical system 10 and a photographing optical system 30. The illumination optical system 10 irradiates the eye E to be inspected with illumination light. The photographing optical system 30 detects the return light of the illumination light from the eye E to be inspected. The measurement light from the OCT unit 100 is guided to the eye E to be inspected through the optical path in the fundus camera unit 2, and the return light is guided to the OCT unit 100 through the same optical path.

The light output from the observation light source 11 of the illumination optical system 10 (observation illumination light) is reflected by the reflection mirror 12 having a curved reflecting surface, passes through the condenser lens 13, and passes through the visible cut filter 14. It becomes near-infrared light. Further, the observation illumination light is once focused in the vicinity of the photographing light source 15, reflected by the mirror 16, and passes through the relay lenses 17, 18, the diaphragm 19, and the relay lens 20. Then, the observation illumination light is reflected at the peripheral portion of the perforated mirror 21 (the region around the perforated portion), passes through the dichroic mirror 46, is refracted by the objective lens 22, and is the eye to be inspected E (fundibular Ef or anterior eye). Department) is illuminated. The return light of the observation illumination light from the eye E to be inspected is refracted by the objective lens 22, passes through the dichroic mirror 46, passes through the hole formed in the central region of the perforated mirror 21, and passes through the dichroic mirror 55. , It is reflected by the mirror 32 via the photographing focusing lens 31. 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 34. The image sensor 35 detects the return light at a predetermined frame rate. The focus of the photographing optical system 30 is adjusted with respect to the fundus Ef or the anterior eye portion.

The light output from the photographing light source 15 (photographing illumination light) is applied to the fundus Ef through the same path as the observation illumination light. The return light of the photographing illumination light from the eye E to be examined 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, and is reflected by the condenser lens 37. An image is formed on the light receiving surface of the image sensor 38.

The LCD 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 33A, reflected by the mirror 32, passes through the photographing focusing lens 31 and the dichroic mirror 55, and passes through the hole portion of the perforated mirror 21. The involuntary luminous flux that has passed through the hole of the perforated mirror 21 passes through the dichroic mirror 46, is refracted by the objective lens 22, and is projected onto the fundus Ef.

The alignment optical system 50 generates an alignment index used for alignment of the optical system with respect to the eye E to be inspected. The alignment light output from the LED 51 passes through the diaphragms 52 and 53 and the relay lens 54, is reflected by the dichroic mirror 55, and passes through the hole portion of the perforated mirror 21. The light that has passed through the hole of the perforated mirror 21 passes through the dichroic mirror 46 and is projected onto the eye E to be inspected by the objective lens 22. The corneal reflected light of the alignment light is guided to the image sensor 35 through the same path as the return light of the observation illumination light. Manual alignment and auto alignment can be executed based on the received light image (alignment index image).

The focus optical system 60 generates a split index used for focus adjustment with respect to the eye E to be inspected. 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 photographing focusing lens 31 along the optical path (optical path) of the photographing optical system 30. The reflective rod 67 is removable with respect to the illumination optical path. When adjusting the focus, the reflecting surface of the reflecting rod 67 is inclined and arranged in the illumination optical path. The focus light output from the LED 61 passes through the relay lens 62, is separated into two light beams by the split index plate 63, passes through the two-hole diaphragm 64, is reflected by the mirror 65, and is reflected by the condenser lens 66. It is once imaged on the reflecting surface of the lens and reflected. Further, the focus 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 Ef. The fundus reflected light of the focus light is guided to the image sensor 35 through the same path as the corneal reflected light of the alignment light. Manual alignment and auto alignment can be executed based on the received light image (split index image).

The diopter correction lenses 70 and 71 can be selectively inserted into the photographing optical path between the perforated mirror 21 and the dichroic mirror 55. The diopter correction lens 70 is a plus lens (convex lens) for correcting high-intensity hyperopia. The diopter correction lens 71 is a minus lens (concave lens) for correcting high-intensity myopia.

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

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

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

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

<OCT unit 100>
As illustrated in FIG. 2, the OCT unit 100 is provided with an optical system for performing a swept source OCT. This optical system divides the light from the wavelength variable light source (wavelength sweep type light source) into the measurement light and the reference light, and causes the return light of the measurement light from the subject E to interfere with the reference light passing through the reference optical path. It includes an interfering optical system that generates interfering light and detects this interfering light. The detection result (detection signal) obtained by the interference optical system is a signal showing 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 wavelength 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 its polarization state is adjusted. Further, the optical L0 is guided by the optical fiber 104 to the fiber coupler 105 and divided into the measurement optical LS and the reference optical LR.

The reference optical LR is guided to the collimator 111 by the optical fiber 110 and converted into a parallel light flux, and is 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 with the optical path length of the measured light LS. The dispersion compensating 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 optical LR via the corner cube 114 is converted from a parallel luminous flux to a focused luminous flux by the collimator 116 via the dispersion compensating member 113 and the optical path length correction member 112, and is incident on the optical fiber 117. The reference optical LR incident on the optical fiber 117 is guided by the polarization controller 118 to adjust its polarization state, is guided to the attenuator 120 by the optical fiber 119 to adjust the amount of light, and is guided to the fiber coupler 122 by the optical fiber 121. Be taken.

On the other hand, the measurement optical 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 is 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. The light is reflected by the dichroic mirror 46 via the relay lens 45, refracted by the objective lens 22, and incident on the eye E to be inspected. The measurement light LS is scattered and reflected at various depth positions of the eye E to be inspected. The return light of the measurement light LS from the eye E to be inspected travels in the same direction 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 128.

The fiber coupler 122 combines (interferes with) the measured light LS incident via the optical fiber 128 and the reference light LR incident via the optical fiber 121 to generate interference light. The fiber coupler 122 generates a pair of interference light LCs by branching the interference light at a predetermined branching ratio (for example, 1: 1). The pair of interference light LCs are guided to the detector 125 through the optical fibers 123 and 124, respectively.

The detector 125 is, for example, a balanced photodiode. The balanced photodiode has a pair of photodetectors that detect each pair of interference light LCs, and outputs the difference between the detection results by these. The detector 125 sends this output (detection signal) to the DAT (Data Acquisition System) 130.

A clock KC is supplied to the DAQ 130 from the light source unit 101. 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 tunable 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 sets the clock KC based on the result of detecting these combined lights. Generate. The DAQ 130 samples the detection signal input from the detector 125 based on the clock KC. The DAQ 130 sends the sampling result of the detection signal from the detector 125 to the arithmetic control unit 200.

In this example, in order to change the length of the 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 the optical path (reference optical path, reference arm) of the reference light LR. Although both corner cubes 114 are provided, only one of the optical path length changing portion 41 and the corner cube 114 may be provided. Further, it is also possible to change the difference between the measured optical path length and the reference optical path length by using an optical member other than these.

<Control system>
FIG. 3 shows a configuration example of the control system of the ophthalmologic imaging apparatus 1. The control unit 210, the image forming unit 220, and the data processing unit 230 are provided in the arithmetic control unit 200.

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

<Main control unit 211>
The main control unit 211 controls each unit (including the elements shown in FIGS. 1 to 3) of the ophthalmologic imaging apparatus 1. The photographing focusing drive unit 31A shown in FIG. 3 moves the photographing focusing lens 31, the OCT focusing drive unit 43A moves the OCT focusing lens 43, and the reference driving unit 114A moves the corner cube 114. The moving mechanism 150 moves the fundus camera unit 2 three-dimensionally.

<Memory unit 212>
The storage unit 212 stores various data. The data stored in the storage unit 212 includes an OCT image, a fundus image, and eye information to be inspected. The eye test information includes subject information such as patient ID and name, left eye / right eye identification information, electronic medical record information, and the like.

<Image forming unit 220>
The image forming unit 220 forms an image based on the output from the DAQ 130 (sampling result of the detection signal). For example, 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 as in the conventional swept source OCT. And arrange along the scan line. The signal processing includes noise removal (noise reduction), filter processing, FFT (Fast Fourier Transform) and the like.

<Data processing unit 230>
The data processing unit 230 performs image processing and analysis processing on the image formed by the image forming unit 220. For example, the data processing unit 230 creates 3D image data (stack data, volume data, etc.) based on raster scan data, renders 3D image data, corrects images, and performs image analysis based on an analysis application. The data processing unit 230 includes an OCT data analysis unit 231 and a photographing data analysis unit 232.

<OCT data analysis unit 231>
The OCT data analysis unit 231 detects the occurrence of an abnormality by analyzing a series of data collected by a series of OCT scans (unit scans described later) along a plurality of scan lines. The types of anomalies that can be detected include at least one of displacement of the eye E to be inspected (displacement of fixation, etc.) and occurrence of blinking. The displacement of the eye E to be inspected includes at least one of a small displacement and a large displacement. The contents of the processing executed by the OCT data analysis unit 231 will be described later.

<Shooting data analysis unit 232>
The photographing data analysis unit 232 detects an abnormality by analyzing two or more fundus images including one or more fundus images acquired by the fundus camera unit 2 in response to the unit scan. The target of detection is, for example, the amount of abnormality detected by the OCT data analysis unit 231. It is also possible to detect the occurrence of an abnormality. The contents of the processing executed by the shooting data analysis unit 232 will be described later.

<User interface 240>
The user interface 240 includes a display unit 241 and an operation unit 242. The display unit 241 includes a display device 3. The operation unit 242 includes various operation devices and input devices. The user interface 240 may include a device such as a touch panel in which a display function and an operation function are integrated. It is also possible to build embodiments that do not include at least a portion of the user interface 240. For example, the display device may be an external device connected to the ophthalmologic imaging device.

<Scan mode and abnormality detection>
The OCT scan mode applied in the present embodiment and the processing executed by the OCT data analysis unit 231 and the photographing data analysis unit 232 will be described.

In this example, a three-dimensional scan (raster scan) is applied. A three-dimensional scan is a scan along a plurality of scan lines parallel to each other. The 3D scan of this example is shown in FIGS. 4A and 4B.

As shown in FIG. 4B, the three-dimensional scan of this example is performed on 320 scan lines L1 to L320. One scan along one scan line Li (i = 1 to 320) is called a B scan. One B scan consists of 320 A scans (see FIG. 4A). A scan is a scan for one A line. That is, the A scan is a scan for the A line along the incident direction (z direction, depth direction) of the measurement light LS. The B scan consists of 320 A-line scans arranged along the scan lines Li on the xy plane orthogonal to the z direction.

In the three-dimensional scan, B scans for the scan lines L1 to L320 are executed four times according to the arrangement order. Four B scans for each scan line Li are called repetition scans. The scan lines L1 to L320 are classified into a set of 5 lines according to the arrangement order. The set of 64 obtained by this classification is called a unit, and the scan for each unit is called a unit scan. The unit scan consists of 4 B scans (that is, a total of 20 B scans) for each of the 5 scan lines.

The abnormality detection process of this example is executed for each unit. If no abnormality is detected during the three-dimensional scan, 320 × 4 × 5 × 64 A scans are executed in the temporal order shown in FIG. 4A, and 4 × 5 × 64 B scan images are acquired. When an abnormality is detected, the scan for the unit at the time of the abnormality is executed again as described later.

The embodiment detects, for example, any of the following.
(1) Blinking (2) Relatively large fixation deviation (large displacement of the eye E to be inspected)
(3) Relatively small displacement of fixation (small displacement of eye E to be inspected)
(4) It is not possible to determine the presence or absence of displacement of the eye E to be inspected (5) Amount of displacement of the eye E to be inspected (including the displacement direction)

(1) to (3) are detected based on OCT data, and (4) and (5) are detected based on a frontal image (fundus image). This embodiment has the following advantages by combining OCT and fundus photography. First, in the conventional technique of detecting an abnormality using an infrared fundus observation image, there is a considerable possibility that detection omission occurs due to the slow update speed (frame rate), but in the present embodiment, the update speed (update speed () Since OCT with a high B scan repetition rate) is used, there is almost no possibility of detection omission. Secondly, although the displacement amount of the eye to be inspected cannot be obtained only by OCT, in the present embodiment, the displacement amount can be obtained by the analysis of the front image and the scan position can be corrected (tracked). Thirdly, even when the OCT data and the front image are acquired at a certain timing at the same time, the analysis result of one cannot be used for the confirmation of the other because a slight time difference actually intervenes, but in the present embodiment. The abnormality generated during one unit scan can be detected by OCT, and the displacement amount can be detected from the front image obtained after the unit scan is started.

<Process executed by OCT data analysis unit 231>
An example of the process executed by the OCT data analysis unit 231 will be described. As described above, the OCT data analysis unit 231 detects the occurrence of an abnormality by analyzing a series of data (interference signals) collected by one unit scan. The OCT data analysis unit 231 analyzes each A scan data (interference signal) included in each B scan data, and obtains a feature value representing the feature of the signal waveform. This feature value is, for example, the number of predetermined feature points in the signal waveform. This feature point is, for example, a turning point (a point where an extreme value is taken, for example, an upwardly convex peak point) in a signal waveform, or a point where the amplitude is zero (zero cross point). The OCT data analysis unit 231 identifies the feature points in the A scan data and counts the number thereof. The above processing is executed for each of the 320 A scan data included in the B scan data. As a result, 320 feature values related to the B scan can be obtained. The set of these 320 feature values is called the characteristic information of the B scan. Such processing is executed for each of the 20 B scan data obtained by the unit scan. As a result, 20 characteristic information regarding the unit scan can be obtained. Further, the OCT data analysis unit 231 calculates an error between the two characteristic information and detects the presence or absence of an abnormality based on this error. The error calculated here is, for example, a correlation coefficient or an average squared error.

(1) Blink detection For each scan line included in one unit scan, the OCT data analysis unit 231 determines the correlation coefficient of a plurality of pairs consisting of different combinations of four characteristic information based on the repetition scan of this scan line. calculate. The plurality of pairs considered here are, for example, a pair of the first characteristic information and the second characteristic information, a pair of the second characteristic information and the third characteristic information, and a third characteristic information and the fourth characteristic information. Is a pair of. The OCT data analysis unit 231 determines whether or not the calculated correlation coefficient is less than a predetermined threshold value. If the correlation coefficient is less than the threshold value, it is determined that a blink has occurred during the repetition scan of this scan line.

Generally, the interference signal acquired while blinking is generated is only a noise component, and the correlation coefficient becomes almost zero. The above-mentioned blink detection is a process utilizing such a phenomenon.

(2) Detection of relatively large fixation deviation For each scan line included in one unit scan, the OCT data analysis unit 231 performs a plurality of pairs consisting of different combinations of four characteristic information based on the repetition scan of this scan line. Calculate the average squared error of each. The plurality of pairs considered here are, for example, all combinations ( ₄ C ₂ = 6) in which two are selected from the four characteristic information. The OCT data analysis unit 231 determines whether or not the calculated error exceeds a predetermined threshold value. When the calculated error exceeds a predetermined threshold value, it is determined that the eye E to be inspected is displaced (displacement of fixation occurs) during the repetition scan of this scan line.

Correlation coefficients can also be applied instead of the mean square error. Also, unlike the following (3), which requires 20 B scan data obtained by one unit scan, this detection process (2) uses only a part of it, so it has the advantage of being able to detect fixation deviation at an early stage. There is. It is also possible to configure so that only one of the detection processes (2) and (3) is executed.

(3) Detection of relatively small fixation deviation For each scan line included in one unit scan, the OCT data analysis unit 231 performs a plurality of pairs consisting of different combinations of four characteristic information based on the repetition scan of this scan line. The average squared error of each of the above is calculated, and the maximum value and the minimum value among the plurality of calculated average squared errors are specified. The plurality of pairs considered here are, for example, all combinations in which two are selected from the four characteristic information.

The OCT data analysis unit 231 specifies the maximum value and the minimum value from the five maximum values and the five minimum values specified for the five scan lines that are the targets of this unit scan. The maximum value and the minimum value specified here are the maximum value among the above five maximum values and the minimum value among the above five minimum values, respectively. The OCT data analysis unit 231 calculates the difference between the maximum value and the minimum value corresponding to this unit scan, and determines whether or not this difference exceeds a predetermined threshold value. If the difference exceeds the threshold value, it is determined that the eye E to be inspected has been displaced (a fixation shift has occurred) during this unit scan.

When the fixation shift occurs between the B scans of one of the repetition scans, the difference between the maximum value and the minimum value of the average squared error becomes large. On the other hand, when the fixation deviation occurs evenly, the difference between the maximum value and the minimum value becomes small. In this detection process (3), an abnormality detection omission is avoided by comparing the average squared error corresponding to each repetition scan included in the unit scan.

In the above example, the maximum value of the average squared error is obtained in consideration of all combinations (6 pieces) of the four characteristic information, but the present invention is not limited to this. For example, any of the four B scans included in the repetition scan can be regarded as a scan for redundancy, and the maximum value can be obtained by excluding the B scan that gives outliers. Since the repetition scan is performed in an extremely short time, it is considered that the factor that worsens the value of the mean square error is not the fixation deviation but the mixing of noise. According to this modification, it is possible to prevent erroneous detection of an abnormality due to the mixing of noise.

<Processing executed by the shooting data analysis unit 232>
An example of the process executed by the shooting data analysis unit 232 will be described. As described above, the photographing data analysis unit 232 detects an abnormality by analyzing two or more fundus images including one or more fundus images acquired by the fundus camera unit 2 in response to the unit scan.

The two or more fundus images analyzed include at least one fundus image acquired between the start and end of this unit scan. In this example, an infrared fundus observation image is acquired in parallel with the above three-dimensional scan. The infrared fundus observation image is a moving image having a predetermined frame rate. The frame rate is set so that at least one frame is obtained during each unit scan. In other words, the frame rate of the infrared fundus observation image and the scan conditions of OCT (scan rate, total number of scan lines, number of repetitions of repetition scan, number of scan lines included in unit scan, etc.) are at least for each unit scan. It is set so that one frame can be obtained.

The photographing data analysis unit 232 analyzes two front images (frames of the infrared fundus observation image) acquired at different timings to determine the displacement amount (displacement direction) of the fundus Ef depicted in these front images. Including) is calculated. In this analysis, for example, pattern matching such as a normalized correlation method or a phase-limited correlation method (POC) is used as in the conventional case. One of the two frames to be compared is, for example, a reference image (baseline image) acquired at the start of imaging (for example, at the start of OCT scan). In this case, the shooting data analysis unit 232 calculates the amount of displacement between the newly acquired front image (frame acquired during a certain unit scan) and the reference image.

(4) Detection of the inability to determine the presence or absence of fixation deviation The displacement amount of the fundus Ef can be obtained when the range of the fundus Ef depicted in the two front images is completely different or when the focus is out of focus. There are cases where it cannot be done. In order to detect such an abnormality, for example, the following processing can be executed. The shooting data analysis unit 232 obtains a normalized correlation value between the newly acquired front image and the reference image. When this normalization correlation value is less than a predetermined threshold value, it is determined that an abnormality has occurred.

Here, it is also possible to use an image different from the infrared fundus observation image. For example, it is possible to create a phase image showing the time change of the phase between a plurality of B scan images obtained by the repetition scan, and to utilize the correlation between such phase images. It is also possible to use a fundus image (such as the above-mentioned captured image) obtained by flashing visible light or a fluorescent image.

The threshold value used to determine the magnitude of the correlation value is set by an arbitrary method. For example, the threshold value can be set in consideration of the fact that the correlation value becomes low in the eye to be inspected, which is opaque due to cataract or the like. Further, when an abnormality is continuously detected a predetermined number of times in this detection process (4) (when an error determination is made), the threshold value can be continuously or stepwise lowered.

(5) Detection of amount (direction) of fixation deviation As described above, the photographing data analysis unit 232 can calculate the displacement amount (displacement amount of the eye E to be inspected) between the two front images. This process is executed, for example, when the occurrence of displacement is detected by the OCT data analysis unit 231. Thereby, the amount of the detected displacement can be obtained from the infrared fundus observation image or the like while detecting the occurrence of the displacement by using the OCT data.

The main control unit 211 can feed back the calculated displacement amount to the OCT scan. For example, the storage unit 212 stores the control information of the optical scanner 42 when the reference image is acquired and the control information of the optical scanner 42 in each unit scan. The control information includes, for example, a coordinate group corresponding to the B scan. The main control unit 211 corrects the control information with the displacement amount calculated by the photographing data analysis unit 232, and can re-execute the unit scan in which the displacement is detected by using the corrected control information. Further, the displacement amount between the latest front image and the reference image can be obtained, and this can be reflected in the control information to execute the unit scan. Further, the abnormality is detected by obtaining the displacement amount between the front image and the reference image corresponding to this unit scan and determining whether the difference between the displacement amount and the control information (coordinate group) is equal to or more than a predetermined threshold value. Can be done. The threshold value at this time is set to, for example, 0.5 pixel, 0.7 pixel, or 1.0 pixel.

<motion>
The operation of the ophthalmologic photographing apparatus 1 will be described. An example of the operation is shown in FIG.

(Preparation for shooting)
First, preparations for shooting are made. When the examiner activates the ophthalmologic imaging device 1 and operates a key (such as a graphic user interface icon) for executing the above-mentioned three-dimensional scan, the main control unit 211 observes the fundus Ef with a live OCT image. Is displayed on the display unit 241. The examiner uses the operation unit 242 (for example, a joystick) to move the device main body (fundus camera unit 2 or the like) away from the jaw holder or the like. This makes it possible to observe the anterior segment of the eye.

The subject is seated in a chair (not shown), the chin is placed on the chin rest, and the forehead is brought into contact with the forehead pad. The examiner adjusts the height of the chin rest and the like according to the sitting height of the subject. In response to a predetermined operation, the main control unit 211 turns on the observation light source 11 and causes the display unit 241 to display an observation image (anterior eye portion observation image) based on the output from the image sensor 35. The examiner (or the ophthalmologic imaging apparatus 1) adjusts the position of the apparatus main body so that the pupil is drawn in the center of the frame of the observation image. When this position adjustment is completed, the examiner (or the ophthalmologic imaging apparatus 1) brings the apparatus main body closer to the eye E to be inspected. As a result, the observation target is switched from the anterior eye portion to the fundus Ef, and the observation image of the fundus Ef is displayed on the display unit 241.

At this stage or earlier, the main control unit 211 controls the alignment optical system 50 to start projection of the alignment index (two alignment bright spots). Two alignment bright spot images are drawn on the observation image. The examiner (or the ophthalmologic imaging apparatus 1) adjusts the position of the apparatus main body so that the two alignment bright spot images are drawn so as to overlap with each other in the target (bracket mark or the like) presented at the center of the frame.

When this position adjustment is completed, optimization of various settings for executing OCT is executed. At this stage or earlier, the main control unit 211 controls the focus optical system 60 to start projection of the split index. In this optimization, adjustment of the optical path length (for example, adjustment of the position of at least one of the optical path length changing unit 41 and the corner cube 114), adjustment of the polarization state (for example, control of at least one of the polarization controllers 103 and 118), Adjustment of the amount of light (for example, control of the attenuator 120), adjustment of the focus (for example, adjustment of the position of the OCT focusing lens 43), and the like are executed.

After the optimization is completed, the examiner (or the ophthalmologic imaging apparatus 1) confirms whether the observation image has a problem such as flare contamination. When it is confirmed that no problem has occurred, the examiner performs an operation for starting shooting by using the operation unit 242. Upon the start of imaging, the main control unit 211 can overlay an image representing the current scan position by OCT on the observation image.

(S11: Acquire a reference image)
The main control unit 211 registers the frame (front image) of the observation image obtained at this stage as a reference image. The shooting data analysis unit 232 starts a process of detecting the displacement between the reference image and the frame acquired thereafter. When the displacement exceeds the threshold value or the displacement cannot be detected due to the influence of blinking or fixation deviation, the main control unit 211 registers the newly acquired frame as a new reference image.

When the reference image is registered, the shooting data analysis unit 232 sequentially calculates the displacement between the frame and the reference image acquired thereafter. The main control unit 211 corrects the orientation of the optical scanner 42 so as to cancel the sequentially calculated displacement. This process may be performed in the same manner as conventional tracking. The orientation correction of the optical scanner 42 is not performed while one repetition scan is being executed, but is performed after the completion of the repetition scan.

The method and timing for registering the reference image are not limited to this. For example, the reference image can be registered by any method at any timing of the subsequent processing. In addition, the reference image can be updated by any method and at any timing (any condition).

(S12: Determine the shooting position)
The main control unit 211 determines the scan position (shooting position) by OCT. Immediately after the start of shooting, the range to be scanned in 3D is set. Now refer to FIG. Reference numeral F indicates a frame of the observed image, and reference numeral R indicates a scan area of a three-dimensional scan. Further, the scan area R is divided into 64 unit scan areas U1 to U64. The unit scan areas U1 to U64 correspond to the unit scans "# 1 Unit scan" to "# 64 Unit scan" shown in FIG. 4A, respectively. This scan area R is set immediately after the start of shooting.

(S13: Execute OCT for 1 unit)
The main control unit 211 executes an OCT scan based on the shooting position determined in step S12. Immediately after the start of shooting, the three-dimensional scan for the scan area R is started from the scan for the first unit scan area U1 (“# 1 Unit scan” shown in FIG. 4A). Infrared moving image of the fundus Ef is executed at a predetermined frame rate in parallel with OCT.

(S21: Acquire OCT data / front image)
The main control unit 211 sends the data collected by the OCT scan for one unit scan area in step S13 and the frame of the observation image acquired in parallel with the unit scan to the data processing unit 230. Immediately after the start of shooting, the data processing unit 230 includes OCT data for 20 B scans collected by the first unit scan (“# 1 Unit scan”) for the first unit scan area U1 and the first unit. The frame of the observation image acquired in parallel with the scan is acquired. The OCT scan and infrared moving image imaging started in step S13 are executed in parallel with the abnormality detection processing in steps S21 to S25.

(S22: Execute the process to detect the occurrence of an abnormality)
The OCT data analysis unit 231 executes a process for detecting the occurrence of an abnormality such as displacement or blinking of the eye E to be inspected. For example, the OCT data analysis unit 231 executes any of the above-mentioned detection processes (1) to (3). Further, the shooting data analysis unit 232 executes, for example, the detection process (4) to detect the occurrence of an abnormality.

(S23: Did you detect the occurrence of an abnormality?)
If the occurrence of an abnormality is not detected in step S22 (S23: No), that is, if it is determined that no abnormality has occurred during the unit scan, the process proceeds to step S25. On the other hand, when an abnormality generated during the unit scan is detected (S23: Yes), the process proceeds to step S24.

(S24: Detects the amount of abnormality)
When the occurrence of an abnormality is detected in step S22 (S23: Yes), the photographing data analysis unit 232 executes, for example, the detection process (5) to displace the eye E to be inspected (displacement direction and displacement amount). Ask for. Then, the process proceeds to step S25.

The abnormality detection process in steps S22 to S24 is executed, for example, as follows. First, the detection process (1) is executed. Specifically, the OCT data analysis unit 231 obtains the above-mentioned characteristic information based on the OCT data obtained in the first four B scans of the unit scan, and calculates the correlation coefficient thereof. If this correlation coefficient is less than the threshold value, it is determined that an abnormality has occurred, another process for detecting the occurrence of the abnormality is skipped, and the process proceeds to step S24.

If the occurrence of an abnormality is not detected in the detection process (1), the process proceeds to the detection process (2). Specifically, the OCT data analysis unit 231 calculates the average square error of each of the six pairs consisting of all combinations of the four characteristic information based on the repetition scan, and determines whether or not the average square error exceeds the threshold value. do. If the average squared error exceeds the threshold value, it is determined that an abnormality has occurred, and other processes for detecting the occurrence of the abnormality are skipped, and the process proceeds to step S24. At this time, the maximum value and the minimum value of the average squared error are retained.

If the occurrence of an abnormality is not detected in the detection process (2), the detection processes (1) and (2) are executed for the four B scan data corresponding to the other scan lines included in the unit scan.

When the detection processes (1) and (2) based on the OCT data for 20 B scans obtained by the unit scan are completed, the process proceeds to the detection process (3). Specifically, the OCT data analysis unit 231 identifies the maximum value and the minimum value from the five maximum values and the five minimum values specified for the five scan lines that are the targets of the unit scan, and these Calculate the difference between. If this difference exceeds the threshold value, it is determined that an abnormality has occurred, another process for detecting the occurrence of the abnormality is skipped, and the process proceeds to step S24.

If no abnormality is detected in any of the detection processes (1) to (3) and the reference image is not registered at this stage, the final B scan (20th B scan) of the unit scan is performed. ), The observation image (frame) acquired at the timing corresponding to) can be adopted as the reference image.

If no abnormality is detected in any of the detection processes (1) to (3), the process proceeds to the detection process (4). Specifically, the shooting data analysis unit 232 applies a normalized correlation method or a phase-limited correlation method to each of the frames acquired during the unit scan and the reference image (or a phase image). (By executing the correlation calculation etc.), the occurrence of an abnormality is detected. If no abnormality is detected in any of the detection processes (1) to (4) (S23: No), the process proceeds to step S25.

If no abnormality is detected in any of the detection processes (1) to (4) and the displacement from the reference image is calculated for a plurality of frames, the next process can be executed: calculated. Calculate the difference between multiple displacements; determine if this difference deviates by a threshold (eg 0.5 pixel) or more in at least one of the x and y directions (taking into account the amount of tracking scan position correction). Yes: If it is determined that the difference is greater than or equal to the threshold value, it is determined that an abnormality has occurred.

On the other hand, when an abnormality is detected in any of the above processes (S23: Yes), the process proceeds to step S24. In step S24, for example, the detection process (5) is executed. Specifically, the shooting data analysis unit 232 calculates the amount of displacement between the frame of the observation image and the reference image.

(S25: Save the detection result)
The abnormality detection result acquired by the data processing unit 230 is stored in the storage unit 212. If the occurrence of an abnormality is not detected in step S22 (S23: No), information indicating that fact is saved as a detection result.

On the other hand, when the occurrence of an abnormality is detected in step S22 (S23: No) and the amount of the abnormality is detected (S24), for example, information indicating that the abnormality has been detected, the type of the detected abnormality. Information indicating the above, information indicating the amount of detected abnormality, etc. are saved as the detection result.

(S14: Check the detection result)
The main control unit 211 confirms (sees) the detection result saved in step S25, and recognizes the presence or absence of an abnormality and its amount.

(S15: No abnormality?)
If no abnormality is detected (S15: Yes), the process proceeds to step S16. On the other hand, when an abnormality is detected (S15: No), the process returns to step S12. At this time, the shooting position is determined so as to return the scan position to the first position of the unit scan in which the abnormality is detected (S12). In addition, the shooting position can be corrected so as to cancel the detected displacement.

(S16: Is it the final unit?)
When no abnormality is detected (S15: Yes) and the unit scan is the OCT scan of the last unit scan area U64 (S16: Yes), the process proceeds to step S17.

On the other hand, if the unit is not an OCT scan of the last unit scan area U64 (S16: No), the process returns to step S12. At this time, the unit scan area next to the unit scan area of the unit scan (or the unit scan area next to the unit scan area where the unit scan is actually executed) is set as the shooting position (S12). At this time, the shooting position can be corrected so as to cancel the detected displacement.

(S17: No abnormality?)
If the unit scan is the last OCT scan of the unit scan area U64 (S16: Yes), the process proceeds to this step S17. If an abnormality is detected in the final unit scan (“# 64 Unit scan” shown in FIG. 4A) (S17: No), the process returns to step S12. At this time, the shooting position is determined so as to return the scan position to the first position of the last unit scan (S12). In addition, the shooting position can be corrected so as to cancel the detected displacement.

On the other hand, if no abnormality is detected in the final unit scan (S17: Yes), the main shooting ends. According to such a shooting mode, it is possible to sequentially scan a plurality of unit scan areas U1 to U64, and when an abnormality occurs, return to the unit scan area and execute the scan again.

<Action / effect>
The operation and effect of the ophthalmologic imaging apparatus according to the embodiment will be described.

The ophthalmologic imaging apparatus of the embodiment includes a data acquisition unit, an imaging unit, a control unit, and an abnormality detection unit. The data collection unit collects data by scanning the eye to be inspected using optical coherence tomography (OCT). The data acquisition unit includes, for example, an OCT unit 100 and an element in the fundus camera unit 2 forming a measurement optical path. The photographing unit photographs the eye to be inspected and acquires a frontal image. The photographing unit includes, for example, an illumination optical system 10 and a photographing optical system 30. The control unit controls the data acquisition unit so as to perform a series of scans along a preset route group. The control unit includes, for example, a main control unit 211. In the above embodiment, as this series of scans, a unit scan along a route group consisting of five scan lines is executed. The anomaly detection unit detects anomalies based on a series of data collected by a series of scans and two or more front images including one or more front images acquired by the photographing unit in response to this series of scans. do. One of the two or more front images may be a reference image. Abnormality detection may include at least one of detection of the occurrence of anomalies and detection of the amount of anomalies.

According to the embodiment configured in this way, it is possible to detect the movement or blinking of the eye to be inspected by using the OCT scan whose repetition rate is sufficiently higher than the frame rate of the video camera. In addition, it is possible to detect the movement of the eye to be inspected and the occurrence of blinking, and to detect the amount of movement of the eye to be inspected from the front image. Therefore, it is possible to acquire a highly accurate OCT image even when the eye to be inspected moves or blinks.

In the embodiment, the abnormality detection unit includes a first abnormality detection unit that detects the occurrence of an abnormality based on a series of data collected by a series of scans using the OCT, and two or more front images obtained by the photographing unit. A second abnormality detection unit that detects the amount of abnormality based on the above may be included. For example, the first abnormality detection unit includes the OCT data analysis unit 231 and the second abnormality detection unit includes the photographing data analysis unit 232. Further, when the occurrence of an abnormality is detected by the first abnormality detecting unit, the second abnormality detecting unit may be configured to detect the amount of the abnormality.

In an embodiment, a series of scans using OCT may include scans (repetition scans) performed sequentially and a predetermined number of times for the route group. Further, the series of data may include a predetermined number of data sets (a plurality of B scan data obtained by repetition scan of each scan line) corresponding to each route included in this route group. Further, the first abnormality detection unit may be configured to obtain characteristic information of each of a predetermined number of data sets and detect the occurrence of an abnormality based on the characteristic information.

In the embodiment, the first anomaly detection unit calculates and calculates the error (average squared error, etc.) of each of a plurality of pairs consisting of different combinations of a predetermined number of characteristic information for each route of the above route group. It may be configured to specify the maximum and minimum values of a plurality of errors. Further, when the difference between the maximum value and the minimum value among the plurality of maximum values and the plurality of minimum values specified for this route group exceeds the threshold value, the first anomaly detection unit performs an abnormality during this series of scans. Can be determined to have occurred. An example of this process is the detection process (3) in the above embodiment.

In the embodiment, the first anomaly detection unit is configured to calculate the error (average squared error, etc.) of a plurality of pairs composed of different combinations of a predetermined number of characteristic information for each route of the above route group. good. Further, when the calculated error exceeds the threshold value, the first abnormality detection unit can determine that an abnormality has occurred during the scan for the path. An example of this process is the detection process (2) in the above embodiment.

In the embodiment, the first anomaly detection unit calculates the correlation coefficient of a plurality of pairs consisting of different combinations of a predetermined number of characteristic information for each route of the above route group, and the calculated correlation coefficient is less than the threshold value. If so, it may be configured to determine that an anomaly has occurred during the scan for that route. An example of this process is the detection process (1) in the above embodiment.

In the embodiment, the first abnormality detection unit has a plurality of A scan data included in this data set for each of the predetermined number of data sets (a plurality of B scan data obtained by repetition scan of each scan line) described above. Each of them may be analyzed to obtain a feature value representing the feature of the signal waveform, and the characteristic information may be obtained based on the obtained plurality of feature values. This feature value may be the number of predetermined feature points in this signal waveform. This feature point may be an extremum point or a zero cross point.

In the embodiment, the second abnormality detecting unit may be configured to detect the displacement between two or more front images as the amount of abnormality. Further, the second anomaly detection unit can calculate the displacement between two or more front images using the phase-limited correlation method.

In the embodiment, the abnormality detection unit may include a third abnormality detection unit that detects the occurrence of an abnormality based on a front image. The third anomaly detection unit calculates a correlation coefficient between two or more front images, and if this correlation coefficient is less than the threshold value, an abnormality (displacement of the eye to be inspected, defocus) during scanning for the path. Etc.) are configured to be determined to have occurred. An example of this process is the detection process (4) in the above embodiment. The shooting data analysis unit 232 is an example of the third abnormality detection unit.

In the embodiment, when an abnormality is detected by the abnormality detection unit (that is, when an abnormality occurs or the amount of the abnormality is large), the control unit performs a series of scans executed at the time of the occurrence of the abnormality. The data collection unit can be controlled to do it again. As a result, the area that was scanned when the abnormality occurred can be scanned again and the data can be reacquired.

In the embodiment, the control unit can control the data acquisition unit so as to sequentially perform a series of scans on a plurality of preset route groups. In this case, the abnormality detection unit can execute the above-mentioned abnormality detection for each route group. In the above embodiment, the unit scan is sequentially executed for the 64 unit scan areas, and the abnormality is detected for each unit scan area. This makes it possible to acquire a highly accurate three-dimensional OCT image (volume data, etc.) even when the eye to be inspected moves or blinks.

The embodiments described above are merely examples of the present invention. A person who intends to carry out the present invention can arbitrarily make modifications (omission, substitution, addition, etc.) within the scope of the gist of the present invention.

1 Ophthalmology imaging device 2 Fundus camera unit 10 Illumination optical system 30 Imaging optical system 100 OCT unit 211 Main control unit 231 OCT data analysis unit 232 Imaging data analysis unit

Claims (9)

A data collection unit that collects data by scanning the eye to be inspected using optical coherence tomography,
An imaging unit that photographs the eye to be inspected and acquires a frontal image,
A control unit that controls the data acquisition unit to perform a unit scan consisting of a series of scans for a preset route group, and a control unit.
Anomalies that detect anomalies based on a series of data collected by the series of scans and two or more frontal images including one or more frontal images acquired by the photographing unit in response to the series of scans. Equipped with a detector
The route group includes a plurality of routes having different positions from each other.
The data acquisition unit sequentially scans the plurality of routes at the first rate, which is the repetition rate of the B scan.
The photographing unit acquires two or more front images at a second rate slower than the first rate.
The abnormality detection unit is
A first abnormality detecting unit that detects the occurrence of displacement of the eye to be inspected based on all of a series of data collected from the plurality of paths at the first rate by the data collecting unit.
The imaging unit includes a second abnormality detecting unit that detects the amount of displacement of the eye to be inspected based on the two or more front images acquired at the second rate.
The series of scans includes scans performed sequentially and a predetermined number of times for the plurality of routes.
The series of data includes a predetermined number of data sets corresponding to each of the plurality of routes.
The first abnormality detection unit is
Obtaining the characteristic information of each of the predetermined number of data sets,
For each of the plurality of routes, the error of each of the plurality of pairs consisting of different combinations of the predetermined number of characteristic information is calculated, and the maximum value and the minimum value among the calculated errors are specified.
When the difference between the maximum value and the minimum value among the plurality of maximum values and the plurality of minimum values specified for the plurality of paths exceeds the threshold value, the displacement of the eye to be inspected occurs during the series of scans. An ophthalmologic imaging device characterized by determining that. The ophthalmologic imaging apparatus according to claim 1, wherein when the first abnormality detecting unit detects the occurrence of the displacement of the eye to be inspected, the second abnormality detecting unit detects the amount of the displacement. .. The first anomaly detection unit analyzes each of a plurality of A scan data included in the predetermined number of data sets for each of the predetermined number of data sets, obtains feature values representing the characteristics of the signal waveform, and obtains a plurality of obtained data sets. The ophthalmologic imaging apparatus according to claim 1, wherein the characteristic information is obtained based on the characteristic value of the above. The ophthalmologic photographing apparatus according to claim 3, wherein the first abnormality detecting unit obtains the number of predetermined feature points in the signal waveform as the feature value. The ophthalmologic imaging apparatus according to claim 4, wherein the predetermined feature point is an extremum point. The second abnormality detecting unit is characterized in that the displacement between the two or more front images acquired by the photographing unit at the second rate is detected as the amount of the displacement of the eye to be inspected. Item 6. The ophthalmologic photographing apparatus according to any one of Items 1 to 5. The ophthalmologic photographing apparatus according to claim 6, wherein the second abnormality detecting unit calculates the displacement between the two or more front images by using a phase-limited correlation method. When the displacement of the eye to be inspected is detected by the first abnormality detection unit, the control unit causes the data acquisition unit to perform sequential scanning of the plurality of paths at the first rate again. The ophthalmologic imaging apparatus according to any one of claims 1 to 7, wherein the device is controlled. The control unit controls the data acquisition unit so as to sequentially perform a series of scans on a plurality of preset route groups.
Each of the plurality of route groups includes a plurality of routes having different positions from each other.
The series of scans for each of the plurality of route groups is a sequential scan at the first rate for the plurality of routes included in the route group.
The ophthalmologic imaging according to any one of claims 1 to 8, wherein the first abnormality detecting unit detects the occurrence of displacement of the eye to be inspected for each of the plurality of route groups. Device.

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