JP6946696B2 - Fundus analyzer and fundus analysis program - Google Patents

Description

The present disclosure relates to a fundus analyzer and a fundus analysis program for acquiring analysis information of the fundus to be inspected.

Conventionally, a fundus analyzer for acquiring a tomographic image of the fundus using optical interference technology and evaluating the state of the eye to be inspected from the obtained tomographic image of the fundus (retinal tomographic image) is known (Patent Document 1). reference). In such a fundus analyzer, a fundus image obtained by photographing the fundus with infrared light is displayed on a monitor, and a part of the displayed fundus image (site) is selected for selection. A fundus tomographic image of the affected area is acquired by using an optical interference technique (see, for example, Patent Document 1). After that, the acquired fundus tomographic image is analyzed by a personal computer (PC) or the like, and the analysis information is displayed on the monitor. The examiner judges whether or not there is an abnormality in the eye to be inspected by looking at the analysis information of the fundus tomographic image obtained in this way.

Japanese Unexamined Patent Publication No. 2008-29467

By the way, when acquiring the analysis information about the macula, the macula of the fundus of the eye to be inspected is detected, the analysis process is performed within the analysis range based on the detected macula, and the analysis information about the macula is acquired. There is. However, the macula may be deformed due to the subject's illness or the like, and it may be difficult to detect the macula well. In this case, it has been difficult to easily and satisfactorily obtain analytical information on the macula.

In view of the above problems, it is a technical subject of the present disclosure to provide a fundus analyzer and a fundus analysis program capable of easily and satisfactorily acquiring analysis information on the macula.

In order to solve the above problems, the present disclosure is characterized by having the following configurations.

(1) The fundus analyzer according to the first aspect of the present disclosure analyzes and processes the OCT image data acquired by the optical coherence stromography device for obtaining the OCT image data of the eye fund to be examined, and analyzes the fundus of the eye to be examined. An OCT image data acquisition means for acquiring information, which is an OCT image data acquisition device for acquiring at least an OCT image data including a yellow spot acquired by an optical coherence stromography device, and a fixation lamp at the time of acquiring the OCT image data. It is a fixation position information acquisition means for acquiring fixation position information, and by acquiring the position of the fixation lamp on the OCT image data based on the fixation position information, the yellow spot portion on the OCT image data A setting means for setting a fixation position information acquisition means for acquiring a position and an analysis range for acquiring analysis information based on the yellow spot portion whose position on the OCT image data has been acquired by the fixation position information acquisition means. The analysis information acquisition means for acquiring the analysis information of the fundus of the eye to be inspected acquired by the analysis processing of the OCT image data in the analysis range set by the setting means.
(2) The fundus analysis program according to the second aspect of the present disclosure analyzes and processes the OCT image data acquired by the optical coherence stromography device for obtaining the OCT image data of the test eye fundus, and analyzes the test eye fundus. It is a fundus analysis program used in the fundus analysis device for acquiring information, and is executed by the processor of the fundus analysis device to acquire OCT image data including at least the yellow spot portion acquired by the optical coherent stromography device. The image data acquisition step and the fixation position information acquisition step of acquiring the fixation position information of the fixation lamp when the OCT image data is acquired , which are on the OCT image data based on the fixation position information. The position on the OCT image data was acquired by the fixation position information acquisition step of acquiring the position of the yellow spot on the OCT image data by acquiring the position of the fixation lamp and the fixation position information acquisition step. Analysis of the fundus of the eye to be inspected acquired by the analysis process of the OCT image data in the setting step for setting the analysis range for acquiring the analysis information based on the yellow spot portion and the analysis range set by the setting step. It is characterized in that the analysis information acquisition step of acquiring information is executed by the fundus analysis apparatus.

It is a block diagram explaining the structure of the fundus analysis apparatus which concerns on this Example. It is a figure which shows the outline of the OCT device which concerns on this Example. It is a figure explaining the acquisition of analysis information with respect to the macula part.

<Overview>
Hereinafter, one of the typical embodiments will be described with reference to the drawings. 1 to 3 are diagrams for explaining the fundus analysis device and the fundus analysis program according to the present embodiment. In the following description, a fundus analyzer will be described as an example. The items classified by <> below can be used independently or in relation to each other.

The present disclosure is not limited to the apparatus described in the present embodiment. For example, terminal control software (program) that performs the functions of the following embodiments is supplied to a system or device via a network or various storage media. Then, a system or a control device of the device (for example, a CPU or the like) can read and execute the program.

For example, the fundus analyzer (for example, the fundus analyzer 1) may be configured to include an optical coherence tomography device (for example, an optical coherence tomography device 10). That is, for example, the device may be a device in which a fundus analyzer and an optical coherence tomography device are integrated. Further, for example, the fundus analyzer and the optical coherence tomography device may be separately provided. In this case, for example, the optical coherence tomography device and the fundus analyzer may be connected by at least one of wireless and wired. For example, wireless configurations include wireless LAN, infrared communication, WiFi (registered trademark), Bluetooth (registered trademark), and the like. Further, for example, as a wired configuration, a configuration such as a USB cable or a LAN cable can be mentioned. For example, a general-purpose personal computer may be used as the fundus analyzer. In the following description, a configuration in which a fundus analyzer and an optical coherence tomography device are separately provided will be described as an example.

For example, in the present embodiment, the fundus analyzer analyzes the OCT image data acquired by the optical coherence tomography device for obtaining the OCT image data of the fundus to be examined, and acquires the analysis information of the fundus to be examined. It may be. For example, the fundus analyzer may include an OCT image data acquisition means (for example, a control unit 70) that acquires OCT image data including at least the macula acquired by an optical coherence tomography device. For example, the fundus analysis device may include a fixation position information acquisition means (for example, a control unit 70) for acquiring the fixation position information of the fixation lamp when the OCT image data is acquired. For example, the fundus analysis device may include a setting means (for example, a control unit 70) for setting an analysis range for acquiring analysis information based on the macula based on the fixation position information. For example, the fundus analysis apparatus may include analysis information acquisition means for acquiring analysis information of the fundus to be inspected acquired by the analysis process of OCT image data in the analysis range set by the setting means. With such a configuration, even when the macula is deformed, analysis information regarding the macula can be easily and satisfactorily obtained.

<Optical coherence tomography device>
For example, the optical coherence tomography device may be based on Fourier domain optical coherence tomography (FD-OCT). For example, an optical coherence tomography device includes an OCT optical system (eg, an OCT optical system 100). For example, the optical coherence tomography device may include an arithmetic control unit (eg, control unit 70). For example, the arithmetic control unit of the optical coherence tomography device may be a separate arithmetic control unit of a different device. The technology of this device is, for example, standard OCT for detecting the reflection intensity of a test object, OCT angiography (for example, Doppler OCT) for detecting motion contrast data of a test object, and polarization-sensitive OCT (PS-). OCT: polarization sensitive OCT) may also be applied. Further, it may be a multifunctional OCT in which a standard OCT and a PS-OCT are combined. For example, as the FD-OCT, a wavelength sweep type OCT (SS-OCT: Swept source-OCT) or a spectral domain OCT (SD-OCT: Spectral Domain OCT) may be used.

For example, the OCT optical system may include a configuration related to an interferometer for obtaining a tomographic image of a test object using the OCT principle. For example, the OCT optical system includes a splitter (optical divider) (for example, a coupler 104), a measurement optical path, a reference optical path, a combiner (photosynthesis device) (for example, a coupler 104, a photodetector (hereinafter, a detector)) (for example, detection). A device 120) may be provided. For example, the splitter may divide the light from the light source (for example, the light source 102) into a measurement optical path and a reference optical path. For example, the splitter and the combiner may include, for example, a beam splitter. A half mirror, fiber coupler, circulator, or the like may be used. For example, the measurement optical path may be configured to guide the light to the fundus of the eye to be examined. For example, the reference optical path may allow the light to travel in the device. The combiner may have a configuration for interfering with the measurement light. For example, the combiner may synthesize (interfere) the measurement light from the measurement optical path reflected by the fundus of the eye to be inspected with the reference light from the reference optical path. For example, the detector may receive the interference signal light generated by the interference between the measurement light and the reference light. For example, the measurement optical path may be provided with an optical scanner (for example, an optical scanner 108). For example, an optical scanner may be used to scan the measurement light on the fundus of the eye to be inspected.

For example, the arithmetic control unit (hereinafter, control unit) may perform control processing, image processing, arithmetic processing, and the like for each configuration of the device. For example, the control unit may acquire the OCT signal by processing the spectral intensity (spectral interference signal) of the interference signal light from the detector that has received the interference signal light. For example, the control unit may acquire OCT image data based on the OCT signal.
For example, the OCT image data includes tomographic image data showing the reflection intensity characteristics of the eye to be inspected, OCT angio image data of the eye to be inspected (for example, OCT motion contrast image data), Doppler OCT image data showing the Doppler characteristics of the eye to be inspected, and the eye to be inspected. It may be at least one of the polarization characteristic image data showing the polarization characteristics of the above. In addition, each data may be the data of the generated image, or may be the signal data before the image is generated.

For example, the tomographic image data may be B-scan tomographic image data. Further, in this case, for example, the tomographic image data may be three-dimensional tomographic image data. Further, in this case, for example, the OCT image data is the OCT front (Enface) image data acquired from the three-dimensional tomographic image data (for example, the integrated image integrated in the depth direction, the integrated spectrum data at each XY position). It may be a value, brightness data at each XY position in a certain depth direction, a retinal surface image, etc.). For example, the B scan tomographic image data is tomographic image data acquired by scanning the measurement light in any direction (for example, the X direction) in the XY direction along the scanning line (crossing position). It may be. For example, the three-dimensional tomographic image data may be tomographic image data acquired by two-dimensionally scanning the measurement light.

For example, the OCT angio image data may be two-dimensional OCT angio image data. Further, for example, the OCT angio image data may be three-dimensional OCT angio image data. Further, for example, the OCT angio image data may be front (Enface) motion contrast data acquired from the three-dimensional motion contrast data. For example, the two-dimensional OCT angio image data is acquired by scanning the measurement light in any direction (for example, the X direction) in the XY direction along the scanning line (transverse position). It may be image data. For example, the three-dimensional OCT angio image data may be OCT angio image data acquired by scanning the measurement light two-dimensionally.

<OCT image data acquisition means>
For example, the OCT image data acquisition means may be configured to acquire the acquired OCT image data by the OCT optical system included in the optical coherence tomography device when the fundus analyzer includes the optical coherence tomography device. Further, for example, the OCT image data acquisition means receives the OCT image data acquired by the OCT optical system included in the optical coherence tomography device when the fundus analyzer does not include the optical coherence tomography device. Image data may be acquired. That is, for example, the OCT image data acquisition means may be configured to acquire the OCT image data by receiving the OCT image data acquired by the OCT optical system of an apparatus different from the fundus analysis apparatus. Further, for example, the OCT image data acquisition means may be configured to acquire the OCT image data by inputting the OCT image data by the examiner and receiving the input OCT image data. In this case, for example, the OCT image data may be input by the examiner by connecting a memory that can be attached to and detached from the fundus analysis device to the fundus analysis device.

For example, the OCT image data acquisition means may acquire OCT image data including the macula and the characteristic portion acquired by photographing a wide area of the fundus of the eye to be inspected. In this case, for example, when analyzing a wide range of OCT image data acquired over a wide area of the fundus of the eye to be inspected, the analysis range of the OCT image data based on the fixation position information is set with reference to the yellow spot. It may be. For example, when analyzing OCT image data taken over a wide range of the fundus of the eye to be inspected, it is necessary to change the analysis process according to each feature portion. For example, since it is possible to take a wide range of images, feature parts other than the macula are included in the OCT image data, and when the analysis information is acquired by the analysis process corresponding to the macula, it is acquired. The analysis information may not be good. Therefore, a wide range of OCT image data can be acquired using a device capable of acquiring a wide range of OCT image data by easily setting an analysis range based on the macula based on the fixation position information. Even in this case, it is more useful because the analysis information on the macula can be easily and satisfactorily obtained.

For example, the feature portion may be the papilla. In this case, for example, the OCT image data acquisition means may acquire OCT image data including the macula and the papilla acquired by photographing a wide area of the fundus of the eye to be inspected. Further, for example, the characteristic portion may be a lesion portion. Of course, for example, the characteristic portion is not limited to the above portion, and may be a characteristic portion in the fundus of the eye to be inspected.

<Means for acquiring fixation position information>
For example, when the fundus analyzer includes the fixation target projection unit, the fixation position information acquisition means of the fixation lamp of the fixation target projection unit (for example, the fixation target projection unit 300) included in the optical coherence tomography device. The fixation position information of the fixation lamp may be called and acquired from a memory (for example, memory 72) in which the position information is stored in advance. Further, for example, the fixation position information acquisition means receives the fixation position information of the fixation lamp in the fixation target projection unit provided in the optical coherence tomography device when the fundus analyzer does not include the fixation target projection unit. By doing so, the fixation position information may be acquired. That is, for example, the fixation position information acquisition means acquires the fixation position information by receiving the fixation position information of the fixation lamp in the fixation target projection unit of the device different from the fundus analysis device. You may. Further, for example, the fixation position information acquisition means may be configured to acquire the fixation position information by inputting the fixation position information by the examiner and receiving the input fixation position information. In this case, for example, the examiner may input the fixation position information by connecting a memory that can be attached to and detached from the fundus analysis device to the fundus analysis device.

For example, the fixation target projection unit may have an optical system for guiding the line-of-sight direction of the eye to be inspected. For example, the fixation target projection unit may have a fixation lamp, and by turning on the fixation lamp, the fixation target may be presented to the eye to be inspected so that the eye to be inspected can be guided in a plurality of directions.

For example, the fixation target projection unit has a fixation lamp (fixation light source) that emits visible light, and changes the presentation position of the fixation target two-dimensionally. As a result, the line-of-sight direction is changed, and as a result, the imaging region is changed. For example, when the fixation target is presented from the same direction as the imaging optical axis, the central portion of the fundus is set as the imaging region. Further, when the fixation target is presented upward with respect to the imaging optical axis, the upper part of the fundus is set as the imaging region. That is, the imaging portion is changed according to the position of the optotype with respect to the imaging optical axis.

For example, the fixation target projection unit has a configuration in which the fixation position is adjusted according to the lighting position of the fixation lamps (for example, LEDs) arranged in a matrix, and the light from the light source is scanned by using an optical scanner. , Various configurations such as a configuration in which the fixation position is adjusted by controlling the lighting of a light source, a display (for example, LCD (Liquid Crystal Display), organic EL (Electro Luminescence), etc.) can be considered. Further, the projection unit may be an internal fixation lamp type or an external fixation light type.

For example, the fixation lamp may be formed of a plurality of fixation lamps or may be formed of one fixation lamp. For example, when the fixation lamp is formed of a plurality of fixation lamps, the fixation lamp is fixed to the eye to be inspected by lighting at least one of the plurality of fixation lamps. The mark may be presented. For example, when the fixation lamp is formed of a plurality of fixation lamps, the direction of the subject's line of sight is guided by selecting the lighting position of the fixation lamp, and the imaged portion in the fundus of the eye to be inspected is photographed. You may change it. That is, the line-of-sight direction of the subject may be changed by changing the fixed-eye lamp to be turned on among the plurality of fixed-eye lamps, and the imaging portion may be changed.

For example, when it is formed by one fixation lamp, the position of one fixation lamp may be used as the fixation position information as the fixation position information. For example, when it is formed by a plurality of fixation lamps, the center position of the plurality of fixation lamps may be used as the fixation position information as the fixation position information. Further, for example, when the film is formed by a plurality of fixation lamps, the fixation position information may be any position of the plurality of fixation lamps. Further, for example, when the film is formed by a plurality of fixation lamps, the fixation position information may be the average position of the positions of the plurality of fixation lamps.

For example, when it is formed by a plurality of fixed-eye lamps and one fixed-eye lamp is lit, the position of the lit fixed-eye lamp may be used as the fixed-eye position information as the fixed-eye position information. Further, for example, when a plurality of fixed-eye lamps are formed and a plurality of fixed-eye lamps to be turned on are selected, the fixed-eye position information includes the center position of the plurality of fixed-eye lamps that are turned on. It may be information. Further, for example, when a plurality of fixed-eye lamps are formed and a plurality of fixed-eye lamps to be turned on are selected, the fixed-eye position information is one of the plurality of fixed-eye lamps that are turned on. The position of the sight lamp may be used as the fixation position information. Further, for example, when a plurality of fixation lamps are formed and a plurality of fixation lamps to be turned on are selected, the position obtained by averaging the positions of the plurality of fixed vision lamps turned on is used as the fixation position information. It may be used as fixation position information.

For example, the position of the fixation lamp may be arranged at a position where OCT image data is acquired with reference to the macula. In this case, for example, the position of the fixation lamp may be arranged around the macula at a position where OCT image data is acquired. Further, in this case, for example, the position of the fixation lamp may be arranged at a position where the OCT image data is acquired so as to include at least the macula.

For example, when acquiring OCT image data centered on the yellow spot, the optical axis of the fixation target projection unit (position of the fixation lamp) for acquiring at least the OCT image data including the yellow spot is the OCT optical system. The fixation lamp may be arranged so as to be coaxial with the optical axis of. Further, for example, when the OCT image data is acquired so that at least the macula is included, the fixation lamp for acquiring the OCT image data including at least the macula is included in the imaging range of the OCT optical system. As such, the fixation lamp may be arranged.

Note that, for example, when the fixation lamp is observed by the subject, the visual axis of the eye to be inspected and the fixation target projection unit (position of the fixation lamp) coincide with each other. That is, when the fixation lamp is observed by the subject, the position of the macula coincides with the position of the fixation lamp. Therefore, the macula position information can be acquired by acquiring the fixation position information. In addition, in this embodiment, coincidence includes substantially coincidence.

For example, by acquiring in advance where the position of the fixation lamp is located in the imaging range of the OCT optical system, the position of the fixation lamp on the OCT image data can be acquired. For example, by acquiring the positional relationship between the position of the fixation lamp and the optical axis of the OCT optical system in advance, the position of the fixation lamp on the OCT image data can be acquired. Of course, the position of the fixation lamp is not limited to the above configuration as long as the positional relationship with the imaging range of the OCT optical system can be acquired. As described above, since the position of the fixation lamp on the OCT image data can be acquired, the position of the macula on the OCT image data can be acquired. That is, since the position of the fixation lamp and the position of the macula coincide with each other, the position of the fixation lamp on the OCT image data can be acquired, so that the position of the macula on the OCT image data can be acquired.

<Setting means>
For example, when setting the analysis range based on the macula, the setting means may set the analysis range centered on the macula based on the fixation position information. For example, by acquiring the analysis information in the analysis range centered on the macula, the analysis process can be performed on the premise that the macula is in the center of the analysis range. It is possible to suppress performing extra processing such as matching processing, and it is possible to easily perform analysis processing.

When setting the analysis range based on the macula, the analysis range may be set based on the fovea centralis of the macula. In other words, the analysis range may be set with the fixation position as the position of the fovea.

Further, for example, when setting the analysis range based on the macula, the setting means may set at least the analysis range including the macula. For example, if the macula is included in any part of the analysis range, analysis information regarding the macula can be obtained.

For example, as the analysis range, a preset range (region) may be set with the macula as a reference. Further, for example, as the analysis range, the range may be set according to the shape and position of the macula. Further, for example, an arbitrary range may be set as the analysis range. In this case, for example, an arbitrary range may be set by the examiner.

<Analysis information acquisition means>
For example, the analysis information acquisition means may perform analysis processing of the OCT image data in the set analysis range to acquire the analysis information of the fundus of the eye to be inspected. In the set analysis range, the analysis information may be acquired for the OCT image data before the analysis processing of the OCT image data is performed and the analysis information of the fundus of the eye to be inspected is acquired. For example, when the analysis information of the set analysis range is acquired when the analysis information has been acquired in advance, the analysis information different from the analysis information acquired in advance may be acquired. .. More specifically, for example, a layer thickness map showing the thickness of the retinal layer of the eye to be examined (for example, the layer thickness map may be a layer thickness map corresponding to the entire OCT image data, or corresponds to a set analysis range. The layer thickness map may be acquired), and the difference map described later may be acquired by the analysis process of the set analysis range.

Further, for example, the analysis information acquisition means may acquire the analysis information of the fundus of the eye to be inspected by extracting the analysis information of the set analysis range from the analysis information acquired in advance. In this case, for example, the OCT image data may be analyzed and the analysis information may be acquired in advance.

For example, the analysis information may be analysis information regarding the layer thickness. Further, for example, the analysis information may be analysis information related to blood vessels. Of course, for example, the analysis information is not limited to the above analysis information. For example, the analysis information may be analysis information about each part of the fundus of the eye to be inspected (for example, the retinal layer, the blood vessel part, the macula part, the papilla, etc.).

For example, the analysis processing means acquires at least one of an analysis map, an analysis chart, a deviation map, an analysis parameter, a comparison result of analysis parameters in each region (section), and the like as analysis information of the fundus of the eye to be inspected. May be good.

For example, the analysis map may be a comparison map or a difference map. For example, as an example of the comparison map, a map showing a comparison result between the thickness of the retinal layer of the eye to be examined and the thickness of the retinal layer of a predetermined eye to be examined stored in the normal eye database may be used. Further, for example, as an example of the comparison map, a map showing the comparison result between the density of the blood vessels of the eye to be examined and the density of the blood vessels of a predetermined eye to be examined stored in the normal eye database may be used. Further, as an example of the comparison map, the comparison result between the OCT image data acquired at different dates and times (for example, each of the first timing and the second timing) (for example, the comparison result of the retinal layer of the eye to be inspected, the subject). It may be a map showing the comparison result of the density of blood vessels of optometry). That is, it may be a comparison map for follow-up. Further, for example, as an example of the difference map, a map showing the difference result between the thickness of the retinal layer of the eye to be inspected and the thickness of the retinal layer of a predetermined eye to be inspected stored in the database may be used. Further, for example, as an example of the difference map, a map showing the difference result between the density of the blood vessels of the eye to be examined and the density of the blood vessels of a predetermined eye to be examined stored in the normal eye database may be used. The analysis information regarding the layer thickness is not limited to the retinal layer. For example, the analysis information regarding the layer thickness may be the analysis information regarding the choroidal layer, or may be the analysis information of the entire fundus including the retinal layer and the choroidal layer. Further, as an example of the difference map, the difference result between the OCT image data acquired at different dates and times (for example, each of the first timing and the second timing) (for example, the difference result of the retinal layer of the eye to be inspected, the subject). It may be a map showing the difference result of the density of the blood vessels of the optometry). That is, it may be a difference map for follow-up.

For example, the analysis chart may be a chart showing analysis values for each preset section. For example, as the analysis value, the basic statistic of the analysis result may be obtained for each preset section. For example, the basic statistic may be a representative value (mean value, median value, mode value, maximum value, minimum value, etc.), dispersal degree (variance, standard deviation, coefficient of variation), or the like. More specifically, the analysis chart may be a chart showing representative values (for example, average value, median value) of the analysis result for each preset section. The analysis chart may be a chart showing the maximum value or the minimum value of the analysis result for each preset section. The analysis result for each section includes the analysis result at each position in the section, so that a stable analysis value can be obtained.

For example, in the deviation map, the difference between the thickness of the retinal layer of the test eye and the thickness of the retinal layer of the predetermined eye stored in the normal eye database is set in the retinal layer of the predetermined eye stored in the normal eye database. It may be a map showing the ratio divided by the thickness. Further, for example, the deviation map may be a map showing the deviation between the thickness of the retinal layer of the eye to be inspected and the thickness of the retinal layer of a predetermined eye to be inspected stored in the normal eye database with a standard deviation. Further, for example, in the deviation map, the difference between the density of the blood vessels of the test eye and the density of the blood vessels of the predetermined eye stored in the normal eye database is set in the normal eye database. It may be a map showing the ratio divided by blood vessels. Further, for example, the deviation map may be a map showing the deviation between the density of the blood vessels of the test eye and the density of the blood vessels of the predetermined eye to be stored stored in the normal eye database with a standard deviation.

A configuration in which a feature portion (for example, a macula portion) is detected and an analysis range is set based on the detection result and a configuration in which an analysis range is set based on fixation position information may be used in combination. As a result, the analysis range can be set more accurately. In this case, for example, when the feature portion is detected and the analysis range is set based on the detection result of the feature portion, when the feature portion cannot be detected well, the analysis range is set based on the fixation position information. You may do so. Further, in this case, the feature portion may be detected and the analysis range may be set based on the detection result, and the analysis range may be set based on the fixation position information. When the analysis range is set using both the feature portion and the fixation position information, the average range of the two analysis ranges may be set as the analysis range, or the feature portion and the fixation position may be set. One of the information may be selected and the analysis range may be set, or the analysis information may be acquired in the analysis range of both the feature portion and the fixation position information. When two analysis information is acquired, the final analysis information may be acquired based on at least one analysis information.

<Example>
Hereinafter, one of the typical examples will be described with reference to the drawings. FIG. 1 is a block diagram illustrating a configuration of a fundus analyzer according to the present embodiment.

For example, the fundus analysis device 1 is used for observing a fundus image taken by a fundus imaging device (for example, an optical coherence tomography device (OCT device)) on a monitor. For example, the fundus analysis device 1 includes a CPU (arithmetic control unit) 70, a mouse (operation unit) 76, a non-volatile memory (storage unit) 72, and a monitor 75, for example. Each unit is electrically connected to the arithmetic control unit (control unit) 70 via a bus or the like.

The fundus analysis device 1 is connected to a fundus photography device for taking an image at a predetermined portion of the eye to be inspected. As an example, in this embodiment, an optical coherence tomography apparatus (hereinafter referred to as an OCT device) 10 for photographing a tomographic image of the fundus Ef of the subject's eye E will be described as an example of the fundus imaging apparatus. .. In this embodiment, the configuration in which the OCT device 10 is connected to the fundus analysis device 1 is taken as an example, but the present invention is not limited to this. An OCT device may be integrated with the fundus analysis device 1.

For example, the control unit 70 controls the operation of each unit based on the arithmetic program and various control programs stored in the memory 72. As the control unit 70, the operation unit 76, the memory 72, and the monitor 75, various programs are installed on the commercially available PC using the arithmetic processing unit, the input unit, the storage unit, and the display unit of the commercially available PC (personal computer). You may do so.

For example, FIG. 2 is a schematic configuration diagram illustrating the configuration of the OCT device 10 according to the present embodiment. Hereinafter, an outline of the apparatus configuration will be described with reference to FIGS. 1 and 2. For example, in this embodiment, the OCT device 10 is an OCT device for capturing OCT image data of the fundus Ef of the subject's eye E. For example, in this embodiment, a case where tomographic image data (hereinafter referred to as a tomographic image) is captured as OCT image data will be described as an example. For example, the OCT device 10 includes an interference optical system (OCT optical system) 100. Further, for example, the OCT device 10 includes a front observation optical system 200 and a fixation target projection unit 300. For example, the OCT device 10 is connected to the control unit 70. That is, the fundus analysis device 1 and the OCT device 10 are connected.

For example, the OCT optical system 100 irradiates the fundus with measurement light. For example, the OCT optical system 100 detects an interference state between the measurement light reflected from the fundus and the reference light by the light receiving element (detector 120). For example, in order to change the imaging position on the fundus Ef, the OCT optical system 100 uses an irradiation position changing unit (for example, an optical scanner 108, a fixation target projection unit 300) that changes the irradiation position of the measurement light on the fundus Ef. Be prepared. For example, the control unit 70 controls the operation of the irradiation position changing unit based on the set imaging position information, and acquires a tomographic image based on the received signal from the detector 120.

<OCT optical system>
The OCT optical system 100 will be described. For example, the OCT optical system 100 has a device configuration of a so-called optical coherence tomography (OCT) for ophthalmology, and captures a tomographic image of the eye E to be inspected. For example, the control unit 70 acquires the OCT signal by controlling the OCT optical system 100. The OCT optical system 100 divides the light emitted from the measurement light source 102 into the measurement light (sample light) and the reference light by the coupler (optical divider) 104. Then, the OCT optical system 100 guides the measurement light to the fundus Ef of the eye E by the measurement optical system 106, and guides the reference light to the reference optical system 110. After that, the detector 120 receives the interference light obtained by combining the measurement light reflected by the fundus Ef and the reference light.

The detector 120 detects an interference signal between the measurement light and the reference light. In the case of Fourier domain OCT, the spectral intensity (spectral interference signal) of the interference light is detected by the detector 120, and the OCT signal is acquired by the Fourier transform on the spectral intensity data.

For example, in the Fourier domain OCT, the depth profile (A scan signal) in a predetermined range is acquired by calculating the absolute value of the amplitude in the OCT signal acquired by the Fourier transform on the spectral intensity data. B-scan tomographic image data (B-scan tomographic image) is acquired by arranging the depth profiles of the measurement light scanned by the optical scanner 108 at each scanning position.

For example, examples of Fourier domain OCT include Spectral-domain OCT (SD-OCT) and Swept-source OCT (SS-OCT). Further, for example, it may be Time-domain OCT (TD-OCT). In the case of SD-OCT, a low coherent light source (broadband light source) is used as the light source 102, and the detector 120 is provided with a spectroscopic optical system (spectrometer) that disperses the interference light into each frequency component (each wavelength component). .. The spectrometer consists of, for example, a diffraction grating and a line sensor. In the case of SS-OCT, a wavelength scanning light source (wavelength variable light source) that changes the emission wavelength at high speed in time is used as the light source 102, and for example, a single light receiving element is provided as the detector 120. The light source 102 is composed of, for example, a light source, a fiber ring resonator, and a wavelength selection filter. Then, as a wavelength selection filter, for example, a combination of a diffraction grating and a polygon mirror, and a filter using Fabry-Perot Etalon can be mentioned.

The light emitted from the light source 102 is divided into a measured luminous flux and a reference luminous flux by the coupler 104. Then, the measured luminous flux is emitted into the air after passing through the optical fiber. The luminous flux is focused on the fundus Ef via the optical scanner 108 and other optical members of the measurement optical system 106. Then, the light reflected by the fundus Ef is returned to the optical fiber through the same optical path.

The optical scanner 108 scans the measurement light two-dimensionally (in the XY directions) on the fundus. The optical scanner 108 is arranged at a position substantially conjugate with the pupil. The optical scanner 108 is, for example, two galvano mirrors, and the reflection angle thereof is arbitrarily adjusted by the drive mechanism 50.

As a result, the luminous flux emitted from the light source 102 changes its reflection (traveling) direction and is scanned at an arbitrary position on the fundus. As a result, the imaging position on the fundus Ef is changed. The optical scanner 108 may have a configuration that deflects light. For example, in addition to a reflection mirror (galvano mirror, polygon mirror, resonant scanner), an acoustic optical element (AOM) that changes the traveling (deflection) direction of light is used.

The reference optical system 110 generates a reference light that is combined with the reflected light acquired by the reflection of the measurement light at the fundus Ef. The reference optical system 110 may be a Michaelson type or a Machzenda type. The reference optical system 110 is formed by, for example, a reflective optical system (for example, a reference mirror), and the light from the coupler 104 is reflected by the reflective optical system to be returned to the coupler 104 again and guided to the detector 120. As another example, the reference optical system 110 is formed by a transmission optical system (for example, an optical fiber) and guides the light from the coupler 104 to the detector 120 by transmitting it without returning it.

The reference optical system 110 has a configuration in which the optical path length difference between the measurement light and the reference light is changed by moving the optical member in the reference optical path. For example, the reference mirror is moved in the optical axis direction. The configuration for changing the optical path length difference may be arranged in the measurement optical path of the measurement optical system 106.

<Front observation optical system>
For example, the front observation optical system 200 acquires front image data of the eye to be inspected. The front image data may be the data of the generated image or the signal data before the image is generated. For example, the front observation optical system 200 is provided to obtain a front image of the fundus Ef. In this embodiment, the front observation optical system 200 is arranged at a position substantially conjugate with the fundus of the eye, for example, an optical scanner that scans the measurement light (for example, infrared light) emitted from the light source two-dimensionally on the fundus of the eye. It includes a second light receiving element that receives the reflected light from the fundus of the eye through the cofocal aperture, and has a device configuration of a so-called ophthalmic scanning laser ophthalmoscope (SLO).

The front observation optical system 200 may have a so-called fundus camera type configuration. Further, for example, an infrared photographing optical system for photographing a subject using infrared light may be used. Further, for example, the OCT optical system 100 may also serve as the front observation optical system 200. That is, the front image data (hereinafter referred to as a front image) may be acquired by using the data forming the tomographic image (OCT front image) obtained two-dimensionally.

The front observation optical system 200 does not have to be integrated with the OCT device 10 or the like. In this case, for example, the front image data acquired by the separately provided front observation optical system 200 may be received by the OCT device 10 or the like.

<Focus target projection unit>
For example, the fixation target projection unit 300 has an optical system for guiding the line-of-sight direction of the eye E to be inspected. The fixation target projection unit 300 has an fixation target presented to the eye E to be inspected, and can guide the eye E to be inspected in a plurality of directions.

For example, the fixation target projection unit 300 has a fixation lamp that emits visible light, and changes the presentation position of the target in two dimensions. As a result, the line-of-sight direction is changed, and as a result, the imaging region is changed. For example, when the fixation target is presented from the same direction as the imaging optical axis of the OCT optical system 100, the central portion of the fundus is set as the imaging region. Further, when the fixation target is presented upward with respect to the imaging optical axis of the OCT optical system 100, the upper part of the fundus is set as the imaging region. That is, the imaging portion is changed according to the position of the fixation target with respect to the imaging optical axis.

The fixation target projection unit 300 has, for example, a configuration in which the fixation position is adjusted according to the lighting position of the fixation lamps (for example, LEDs) arranged in a matrix, and the light from the fixation lamp is scanned by an optical scanner. , A configuration in which the fixation position is adjusted by controlling the lighting of the fixation lamp, and the like, various configurations are conceivable. Further, the fixation target projection unit 300 may be an internal fixation lamp type or an external fixation light type.

<Control unit>
The control unit 70 includes a CPU (processor), RAM, ROM, and the like. The CPU of the control unit 70 controls the entire device (fundus analysis device 1, fundus photography device 10) such as each member of each configuration 100 to 300. The RAM temporarily stores various types of information. The ROM of the control unit 70 stores various programs, initial values, and the like for controlling the operation of the entire device. The control unit 70 may be composed of a plurality of control units (that is, a plurality of processors).

For example, the control unit 70 is electrically connected to a non-volatile memory (storage means) 72, an operation unit (control unit) 76, a display unit (monitor) 75, and the like. The non-volatile memory (memory) 72 is a non-transient storage medium capable of retaining the stored contents even when the power supply is cut off. For example, a hard disk drive, a flash ROM, an OCT device 10, a USB memory detachably attached to the OCT optical system 100, and the like can be used as the non-volatile memory 72.

For example, the memory 72 stores a photographing control program for controlling the photographing of the front image data and the tomographic image data by the OCT optical system 100. Further, the memory 72 stores a fundus analysis program that enables the use of the OCT device 10. Further, the memory 72 stores various information related to imaging such as B scan tomographic image data in the scanning line, three-dimensional tomographic image data), front image data (frontal image data of the fundus of the eye), information on the imaging position of the tomographic image data, and the like. NS. Various operation instructions by the inspector are input to the operation unit 76.

For example, the memory 72 stores the position information of the optical axis of the fixation target projection unit 300 (the fixation lamp of the fixation target projection unit 300) with respect to the optical axis of the OCT optical system 100. In this way, by storing the position information of the optical axis of the fixation target projection unit 300 with respect to the optical axis of the OCT optical system 100, the fixation on the tomographic image data and the front image data acquired by the OCT optical system 100. The position of the light can be grasped. The position information of the optical axis of the fixation target projection unit 300 with respect to the optical axis of the front observation optical system 200 may be stored.

For example, the operation unit 76 outputs a signal corresponding to the input operation instruction to the control unit 70. For the operation unit 76, for example, at least one of a mouse, a joystick, a keyboard, a touch panel, and the like may be used.

For example, the monitor 75 may be a display mounted on the main body of the apparatus or a display connected to the main body. A display of a personal computer (hereinafter referred to as "PC") may be used. A plurality of displays may be used together. Further, the monitor 75 may be a touch panel. When the monitor 75 is a touch panel, the monitor 75 functions as an operation unit. Various images including tomographic image data and frontal image data taken by the OCT optical system 100 are displayed on the monitor 75.

<Fault imaging operation>
Hereinafter, a series of photographing operations using the OCT device 10 will be described. For example, patient information (ID number for identifying a patient, name, age, gender, chief complaint, comment, etc.) is input as a preparation for acquisition of a tomographic image by the OCT device 10. A tomographic image acquired by the OCT optical system 100, a front image acquired by the front observation optical system 200, a setting screen for various imaging conditions, and the like are displayed on the monitor 75.

For example, when the operation unit 76 is operated by the examiner and the wide range shooting mode is selected, the control unit 70 turns on the fixation lamp for the wide range shooting mode. For example, the control unit 70 controls the fixation target projection unit 300 and turns on the fixation lamp. In this embodiment, for example, the lighting position of the fixation lamp is set to a position where a tomographic image including the macula and the papilla can be obtained when the eye to be inspected observes the fixation target. That is, in this embodiment, the target imaging portion and the lighting position of the fixation lamp of the fixation target projection unit 300 are associated with each other, and the lighting position of the fixation lamp is set based on this, so that the examiner can set the lighting position. A tomographic image of the desired fundus region can be easily obtained. The OCT optical system 100 in this embodiment has a configuration capable of photographing the eye to be inspected in a wide range of imaging. Therefore, it is possible to easily acquire a tomographic image in the range including the macula and the papilla in the fundus of the eye to be inspected.

For example, after the fixation lamp is turned on, the examiner instructs the subject to gaze at the fixation target of the fixation target projection unit 300, and then the subject is photographed by an anterior eye observation camera (not shown). While viewing the anterior segment observation image on the monitor 75, the alignment operation is performed using the operation unit 76 (for example, a joystick (not shown)) so that the measurement optical axis comes to the center of the pupil of the eye to be inspected.

For example, when the alignment operation is completed, the control unit 70 controls the drive of the optical scanner 108, scans the measurement light on the fundus in a predetermined direction, and scans a predetermined scan from the output signal output from the detector 120 during scanning. A tomographic image is formed by acquiring a light receiving signal corresponding to a region. Further, the control unit 70 controls the OCT optical system 100 and acquires a tomographic image, and also controls the observation optical system 200 to acquire a frontal image of the fundus. Then, the control unit 70 acquires a tomographic image by the OCT optical system 100 and a front image (front image) by the observation optical system 200 at any time. As a result, the tomographic image and the front image are displayed on the screen of the monitor 75. In this embodiment, the front image includes the macula and the papilla.

For example, the examiner operates the operation unit 76 to perform optimization control (for example, optical path length adjustment, focus adjustment, polarization adjustment, etc.). For example, the examiner then operates the operation unit 76 to select a scanning pattern (line, cross line, raster, circle, radial, etc.) of the measurement light. In this embodiment, for example, a case where the examiner selects a raster scan and acquires three-dimensional tomographic image data (three-dimensional tomographic image) by the OCT optical system 100 will be described as an example. Of course, the configuration for acquiring a three-dimensional tomographic image is not limited to raster scan.

For example, the examiner operates the operation unit 76 and sets the scanning position using the front image of the front observation optical system 200. In this embodiment, for example, the examiner sets the scanning position so that the macula and the papilla of the fundus of the eye to be inspected are included in the scanning range (for example, a rectangular region of 12 mm in length × 12 mm in width) in the scanning pattern. This makes it possible to acquire a wide range of three-dimensional tomographic images.

For example, the examiner operates the operation unit 76 to select a shooting switch (not shown). When the operation unit 76 outputs a signal for starting imaging, the control unit 70 controls the drive of the optical scanner 108 based on the set imaging conditions, scans the measurement light on the fundus in a predetermined direction, and scans the light. A light receiving signal corresponding to a predetermined scanning region is acquired from the output signal output from the detector 120 inside, and a tomographic image is acquired.

Further, the control unit 70 controls the front observation optical system 200 and acquires a front image. Further, for example, the control unit 70, together with the captured tomographic image, capture information (fixation position information, imaging site information, left and right eye information, etc.) and selection range information (scanning pattern, scanning position, scanning range, etc.). Is stored in the memory 72. As described above, the tomographic image is acquired by the OCT device 10.

<Analysis processing>
Next, when the operation unit 76 is operated by the examiner and the analysis mode changeover switch on the monitor 75 screen is selected, the control unit 70 switches to the analysis mode. In the analysis mode, the control unit 70 analyzes the three-dimensional tomographic image stored in the memory 72 and acquires the analysis information. The switching to the analysis mode may be configured to be automatically switched, for example, after the tomographic image is acquired by the fundus photography apparatus 10. In this case, for example, the control unit 70 stores the acquired tomographic image in the memory 72 and switches to the analysis mode.

For example, when performing analysis processing, it is preferable that the control unit 70 performs analysis processing according to each site (for example, macula, papilla, etc.) in the tomographic image. Hereinafter, a case of acquiring analysis information based on the macula based on the fixation position information will be described.

FIG. 3 is a diagram illustrating acquisition of analysis information based on the macula. For example, when the mode is switched to the analysis mode, the control unit 70 displays the OCT front (Enface) image 40 based on the three-dimensional tomographic image on the screen of the monitor 75. For example, the OCT front image 40 is acquired by integrating the spectral data at each XY position in the three-dimensional tomographic image.

Next, when the examiner selects a switch (not shown) for acquiring analysis information of the macula, the control unit 70 sets an analysis range based on the macula from the range of the OCT front image 40, and analyzes the range. The frame Z indicating the above is superimposed and displayed on the OCT front image 40.

The setting of the analysis range will be described below. For example, the control unit 70 has an analysis range (for example, 9 mm in length × 9 mm in width) based on the macula F from a wide range of OCT front image 40 including the macula F and the papilla N based on the fixation position information. To set. In this embodiment, a case where an analysis range centered on the macula F is set as the analysis range will be described as an example.

For example, the control unit 70 calls and acquires the fixation position information when the OCT front image 40 is acquired from the memory 72. For example, by acquiring the fixation position information, the macula position information can be acquired. In this embodiment, for example, the fixation position information indicates the position coordinates of the fixation lamp on the scanning range (imaging range) of the OCT optical system 100. For example, by acquiring the fixation position information, the position of the fixation lamp on the OCT front image 40 can be acquired. Thereby, the position of the macula on the OCT front image 40 can be acquired.

For example, the control unit 70 sets the analysis range centering on the position of the fixation lamp based on the acquired fixation position information. That is, for example, the control unit 70 sets the analysis range from the range of the OCT front image 40. This makes it possible to set the analysis range centered on the macula F. For example, when the analysis range centered on the macula F is set, the control unit 70 superimposes and displays the frame Z indicating the analysis range on the OCT front image 40.

For example, when the analysis range is confirmed by the examiner and a switch (not shown) for starting the acquisition of analysis information is selected, the control unit 70 sets the three-dimensional fault which is the basis of the OCT front image 40 in the set analysis range. Perform image analysis processing. As a result, it is possible to acquire analysis information of the fundus of the eye to be inspected in the analysis range centered on the macula F. In this embodiment, when the analysis range is set, the frame Z is displayed, and the configuration confirmed by the examiner has been described as an example, but the present invention is not limited to this. For example, if the control unit 70 sets the analysis range based on the macula F, the control unit 70 may acquire the analysis information in the analysis range.

For example, in this embodiment, a case where a comparison map is acquired as analysis information will be described as an example. For example, when detecting a layer, the control unit 70 detects the brightness level of the tomographic image. The control unit 70 extracts a layer boundary corresponding to a predetermined retinal layer (for example, the retinal surface and the retinal pigment epithelial layer) by image processing. Then, the control unit 70 acquires the layer thickness (layer thickness) information by measuring the interval between the layer boundaries. In this embodiment, a configuration using a comparison map is given as an example of analysis information, but the present invention is not limited to this. For example, the analysis information may be configured to acquire other analysis information. Further, for example, it may be configured to acquire a plurality of analysis information.

For example, the control unit 70 acquires the layer thickness information at each position in the XY direction in the set analysis range, and refers to the normal eye database for the layer thickness information at each position regarding the layer thickness. Get analysis information. Further, of course, in the analysis using the layer thickness, the total value of a plurality of layer thicknesses may be used.

For example, the normal eye database may store characteristic information (interval between layers, shape of predetermined portion, size of predetermined portion, etc.) in the eye to be examined as normal. The normal eye database may be created by integrating the data of a plurality of eyes to be examined. For example, as a normal eye database, statistical feature information acquired from data of a plurality of examinees may be stored.

For example, when acquiring analysis information regarding the layer thickness, the control unit 70 acquires the analysis information using at least the interval of each layer stored in the database. For example, as information on the interval between each layer in the normal eye database, the range of the layer thickness considered to be normal, the range of the layer thickness considered to be the normal borderline, the range of the layer thickness considered to be abnormal, etc. It is stored as information about the layer thickness.

For example, the control unit 70 determines which layer thickness range the layer thickness information at each position belongs to in the normal eye database. Based on the determination result, the control unit 70 refers to the normal eye database and acquires a comparison map. For example, in this embodiment, the control unit 70 creates a map (for example, a color map) that graphically shows the analysis information of the three-dimensional tomographic image based on the determination result as a comparison map. For example, the control unit 70 compares the layer thickness of the retinal layer of the eye to be inspected with the layer thickness stored in the normal eye database, and displays a graphic showing a normal part, a borderline part, and an abnormal part according to the comparison result. do. Further, for example, the control unit 70 may associate the acquired comparison map with the patient information and store it in the memory 72.

Since the acquired three-dimensional tomographic image also includes the papilla, analysis information based on the papilla may be acquired. For example, when analyzing the papilla, the control unit 70 analyzes the OCT front image 40 to detect the papilla. For example, since the papilla has a high brightness and a large size with respect to the macula, it is easy to detect even if the papilla is deformed due to a cause such as a disease of the subject. For example, the control unit 70 sets the analysis range with reference to the papilla after detecting the papilla. For example, the control unit 70 acquires analysis information in the set analysis range. When the analysis process is performed when the analysis information is acquired, the analysis process for the nipple is performed and the analysis information is acquired.

As described above, for example, the fundus analyzer analyzes the OCT image data acquired by the optical coherence tomography device for obtaining the OCT image data of the fundus to be examined, and acquires the analysis information of the fundus to be examined. It may be an analyzer. Further, for example, the fundus analyzer is an OCT image data acquisition means for acquiring OCT image data including at least a yellow spot acquired by an optical coherence stromography device, and a fixation position of a fixation lamp when the OCT image data is acquired. OCT in the fixation position information acquisition means for acquiring information, the setting means for setting the analysis range for acquiring analysis information based on the yellow spot based on the fixation position information, and the analysis range set by the setting means. An analysis information acquisition means for acquiring the analysis information of the fundus of the eye to be inspected acquired by the analysis process of the image data may be provided. Thereby, even when the macula is deformed, the analysis information about the macula can be easily and satisfactorily obtained.

Further, for example, the setting means may set the analysis range centered on the macula based on the fixation position information. By acquiring the analysis information in the analysis range centered on the macula, the analysis process can be performed on the premise that the macula is in the center of the analysis range. It is possible to suppress performing extra processing such as, etc., and it is possible to easily perform analysis processing.

Further, for example, the OCT image data acquisition means may acquire OCT image data including the macula and the characteristic portion (for example, the papilla) acquired by photographing a wide area of the fundus of the eye to be inspected. For example, when analyzing OCT image data taken over a wide range of the fundus of the eye to be inspected, it is necessary to change the analysis process according to each feature portion. For example, since it is possible to take a wide range of images, feature parts other than the macula are included in the OCT image data, and when the analysis information is acquired by the analysis process corresponding to the macula, it is acquired. The analysis information may not be good. Therefore, a wide range of OCT image data can be acquired using a device capable of acquiring a wide range of OCT image data by easily setting an analysis range based on the macula based on the fixation position information. Even in this case, it is more useful because the analysis information on the macula can be easily and satisfactorily obtained.

In this embodiment, a configuration for acquiring analysis information based on the macula based on the fixation position information has been described as an example, but the present invention is not limited to this. For example, by acquiring the positional relationship of the fixation lamp in advance for other feature portions of the fundus of the eye to be inspected, it is possible to acquire analysis information based on the feature portion based on the fixation position information. .. As an example, by acquiring the positional relationship of the fixation lamp in advance for the papilla, it is possible to acquire analysis information based on the papilla based on the fixation position information.

The present invention is not limited to the apparatus described in the present embodiment. For example, fundus analysis software (program) that performs the functions of the above embodiment is supplied to the system or device via a network or various storage media. Then, a system or a control device of the device (for example, a CPU or the like) can read and execute the program.

1 Fundus analyzer 10 Optical coherence tomography device 70 Control unit 72 Memory 75 Monitor 76 Operation unit 100 Interference optical system (OCT optical system)
108 Optical scanner 120 Detector 200 Front observation optical system 300 Fixed target projection unit

Claims (5)

It is a fundus analysis device that analyzes and processes the OCT image data acquired by the optical coherence tomography device for obtaining the OCT image data of the fundus of the eye to be inspected, and acquires the analysis information of the fundus of the eye to be inspected.
An OCT image data acquisition means for acquiring OCT image data including at least a yellow spot acquired by an optical coherence tomography device, and an OCT image data acquisition means.
It is a fixation position information acquisition means for acquiring the fixation position information of the fixation lamp when the OCT image data is acquired, and the position of the fixation lamp on the OCT image data is determined based on the fixation position information. An fixation position information acquisition means for acquiring the position of the yellow spot on the OCT image data by acquiring the data , and
A setting means for setting an analysis range for acquiring analysis information based on the macula whose position on the OCT image data has been acquired by the fixation position information acquisition means.
In the analysis range set by the setting means, the analysis information acquisition means for acquiring the analysis information of the fundus of the eye to be inspected acquired by the analysis process of the OCT image data, and the analysis information acquisition means.
A fundus analyzer characterized by being equipped with. In the fundus analyzer of claim 1,
The setting means is a fundus analysis apparatus characterized in that an analysis range centered on the macula portion whose position on the OCT image data has been acquired by the fixation position information acquisition means is set. In the fundus analyzer of claim 1 or 2,
The OCT image data acquisition means is a fundus analysis device that acquires the OCT image data including the macula and the characteristic portion acquired by photographing a wide area of the fundus of the eye to be inspected. In the fundus analyzer of claim 3,
The characteristic part is the nipple,
The OCT image data acquisition means is a fundus analysis device that acquires the OCT image data including the macula and the papilla acquired by photographing a wide area of the fundus of the eye to be inspected. It is a fundus analysis program used in a fundus analysis apparatus that analyzes and processes OCT image data acquired by an optical coherence tomography device for obtaining OCT image data of the fundus of the eye to be inspected and acquires the analysis information of the fundus of the eye to be inspected. By being executed by the processor of the fundus analyzer,
An OCT image data acquisition step of acquiring OCT image data including at least a yellow spot acquired by an optical coherence tomography device, and
In the fixation position information acquisition step of acquiring the fixation position information of the fixation lamp when the OCT image data is acquired , the position of the fixation lamp on the OCT image data is determined based on the fixation position information. The fixation position information acquisition step of acquiring the position of the yellow spot on the OCT image data by acquiring, and the fixation position information acquisition step .
A setting step for setting an analysis range for acquiring analysis information based on the macula whose position on the OCT image data has been acquired by the fixation position information acquisition step, and a setting step.
In the analysis range set by the setting step, an analysis information acquisition step for acquiring the analysis information of the fundus of the eye to be inspected acquired by the analysis process of the OCT image data, and the analysis information acquisition step.
Is executed by the fundus analyzer.

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