JP6995485B2 - Ophthalmic appliances, device control methods and programs - Google Patents

Description

The present invention relates to an ophthalmic apparatus that generates a blood vessel-containing image including blood vessels of an eye to be inspected, a control method of an apparatus that generates a blood vessel-containing image of a subject including an eye to be inspected, and a program for causing a computer to execute the control method. It is about.

In recent years, an optical coherence tomography (hereinafter referred to as "OCT") device using interference due to low coherence light has been put into practical use as an ophthalmic device for ophthalmic examination. This OCT device can, for example, depict the three-dimensional structure of the retina of the eye to be inspected. Furthermore, in recent years, OCT devices have been equipped with OCT angiography technology that non-invasively visualizes retinal blood vessels by utilizing not only the retinal structure but also signal changes between continuously acquired tomographic images. It has been developed (see, for example, Patent Document 1).

Japanese Unexamined Patent Publication No. 2016-209200

Recent research results discuss the usefulness of OCT angiography. In particular, OCT angiography in which the vascular condition is visualized is effective for diagnosing a disease of the eye to be inspected, such as age-related macular degeneration and diabetic retinopathy. In this respect, the technique of Patent Document 1 is a technique for accurately imaging a blood vessel, and does not consider providing information that can be used for diagnosing a disease of an eye to be inspected by using an OCT angiography image. rice field.

The present invention has been made in view of such problems, and an object of the present invention is to provide information that can be used for diagnosing a disease of an eye to be inspected.

The ophthalmic apparatus of the present invention is a generation means for generating an OCTA image which is a blood vessel-containing image including a blood vessel of a test eye, and a blood vessel confluence portion in which at least two blood vessels are merged into one blood vessel from the OCTA image. An extraction means for extracting an image region containing the blood vessel, an acquisition means for acquiring a plurality of brightness profiles in a direction intersecting the blood flow direction of the one blood vessel from the image region including the blood vessel confluence portion, and the plurality of brightness. An analysis means for analyzing a profile to acquire laminar flow information related to laminar flow of blood flowing from each of the two blood vessels in the one blood vessel, and a display for controlling display of the laminar flow information on a display unit. It has a control means, and the analysis means acquires information including information on the length of the laminar flow in the blood flow direction of the one blood vessel as the laminar flow information .
Another aspect of the ophthalmic apparatus of the present invention is a generation means for generating an OCTA image which is a blood vessel-containing image including a blood vessel of a test eye, and at least two blood vessels from the OCTA image are merged into one blood vessel. An extraction means for extracting an image region including a blood vessel confluence portion, and an acquisition means for acquiring a plurality of brightness profiles in a direction intersecting the blood flow direction of the one blood vessel from the image region including the blood vessel confluence portion. An analysis means for analyzing the plurality of brightness profiles and acquiring laminar flow information related to the laminar flow of blood flowing from each of the two blood vessels in the one blood vessel, and displaying the laminar flow information on the display unit. The analysis means has a display control means for controlling, and the analysis means has, as the laminar flow information, a laminar flow of blood flowing from one of the two blood vessels in the one blood vessel and the two blood vessels. Information including information on the laminar flow ratio, which is the ratio of the blood flowing from the other blood vessel to the laminar flow, is acquired.
The present invention also includes a method for controlling an apparatus including the above-mentioned ophthalmic apparatus, and a program for causing a computer to execute the control method.

According to the present invention, it is possible to provide information that can be used for diagnosing a disease of an eye to be inspected.

It is a figure which shows an example of the schematic structure of the ophthalmic apparatus which concerns on embodiment of this invention. It is a figure which shows an example of the image area extraction processing by the extraction means of FIG. It is a figure which shows an example of the OCTA image which concerns on the image area containing the blood vessel confluence part generated by the generation means of FIG. It is a figure which shows an example of the luminance profile acquired by the analysis means of FIG. It is a flowchart which shows an example of the processing procedure in the control method of the ophthalmologic apparatus which concerns on embodiment of this invention. It is a figure for demonstrating the laminar flow information obtained by the analysis process of step S108 of FIG. It is a flowchart which shows an example of the detailed processing procedure which concerns on aspect 1 in the analysis processing of step S108 of FIG. It is a flowchart which shows an example of the detailed processing procedure which concerns on aspect 2 in the analysis processing of step S108 of FIG. It is a figure which shows the embodiment of this invention, and shows the example which applied the fundus image obtained by the fluorescent fundus angiography as the blood vessel containing image including the blood vessel of the eye under test.

Hereinafter, embodiments (embodiments) for carrying out the present invention will be described with reference to the drawings.

FIG. 1 is a diagram showing an example of a schematic configuration of an ophthalmic apparatus 100 according to an embodiment of the present invention. As the ophthalmic appliance 100 according to the present embodiment, an example in which an SS (Swept source) -OCT apparatus is applied will be described, but the present invention is not limited to this. For example, as the ophthalmic appliance 100 according to the present embodiment, it is included in the present invention that an OCT apparatus of another type is applied, and further, an ophthalmic appliance other than the OCT apparatus is applied.

As shown in FIG. 1, the ophthalmologic apparatus 100 includes a wavelength sweep light source 110, an optical signal branch / combine unit 120, an interference light detection unit 130, a computer 140, a measurement arm 150, a reference arm 160, and a display unit 170. It is composed of. Here, the computer 140 includes, for example, a hardware configuration including a central processing unit (CPU) and a storage device. At this time, the storage device includes, for example, a memory (RAM and ROM) and a large-capacity storage device (HDD). Further, a part or all of the storage device may be provided outside the computer 140.

The wavelength sweep light source 110 emits light having a wavelength of, for example, 980 nm to 1100 nm at a frequency of 100 kHz (A scan rate) under the control of the computer 140. Here, the wavelength and the frequency are examples, and the present embodiment is not limited to the above-mentioned values. Similarly, in the following description, the described numerical values are examples, and are not limited to the described numerical values in the present embodiment. Further, in the present embodiment, an example in which the fundus Ef of the eye to be inspected E is applied as an imaging target will be described, but the present invention is not limited to this, and for example, other parts of the eye to be inspected (for example, the front). It is also included in the present invention to target the eye portion).

As shown in FIG. 1, the optical signal branch / combine unit 120 includes a coupler 121 and a coupler 122. First, the coupler 121 is a branching member that branches into an irradiation light that irradiates the fundus Ef of the eye E to be inspected with light emitted from the wavelength sweep light source 110 and a reference light. The irradiation light is applied to the eye E to be inspected via the measurement arm 150. More specifically, the irradiation light incident on the measurement arm 150 is emitted as spatial light from the collimator 152 after the polarization state is adjusted by the polarization controller 151. After that, the irradiation light is applied to the fundus Ef of the eye E to be inspected via the X-axis scanner 153, the Y-axis scanner 154, and the focus lens 155. The X-axis scanner 153 and the Y-axis scanner 154 are scanning members having a function of scanning the fundus Ef with irradiation light. The scanning member changes the irradiation position of the irradiation light on the fundus Ef. Here, acquiring information in the depth direction (depth direction) of one point of the eye E to be inspected is called A scan. Further, acquiring a two-dimensional tomographic image along a direction orthogonal to the A scan is a B scan, and further acquiring a two-dimensional tomographic image along a direction perpendicular to the two-dimensional tomographic image of the B scan is C. Called a scan.

The X-axis scanner 153 and the Y-axis scanner 154 are each composed of mirrors arranged so that their rotation axes are orthogonal to each other. The X-axis scanner 153 scans in the X-axis direction, and the Y-axis scanner 154 scans in the Y-axis direction. Each of the X-axis direction and the Y-axis direction is a direction perpendicular to the eye axis direction of the eyeball and is a direction perpendicular to each other. Further, the line scanning direction such as B scan and C scan and the X-axis direction or the Y-axis direction do not have to coincide with each other. Therefore, the line scanning directions of the B scan and the C scan can be appropriately determined according to the two-dimensional tomographic image or the three-dimensional tomographic image to be captured.

The reflected light from the fundus Ef passes through the coupler 121 again via the same path such as the focus lens 155 and is incident on the coupler 122. By closing the shutter 156 and measuring, the background (noise floor) can be measured by cutting the reflected light from the eye E to be inspected.

On the other hand, the reference light enters the coupler 122 via the reference arm 160. More specifically, the reference light incident on the reference arm 160 is emitted as spatial light from the collimator 162 after the polarization state is adjusted by the polarization controller 161. After that, the reference light passes through the dispersion compensating glass 163, the optical path length adjusting optical system 164, and the dispersion adjusting prism pair 165, is incident on the optical fiber via the collimator 166, is emitted from the reference arm 160, and is incident on the coupler 122.

In the coupler 122, the return light of the measurement light from the eye E to be inspected via the measurement arm 150 and the reference light passing through the reference arm 160 interfere with each other. Then, the interference light is detected by the interference light detection unit 130. The interference light detection unit 130 includes a differential detector 131 and an A / D converter 132. In the interference light detection unit 130, first, the interference light demultiplexed by the coupler 122 is detected by the differential detector 131. Then, the OCT interference signal converted into an electric signal by the differential detector 131 (hereinafter, may be simply referred to as “interference signal”) is converted into a digital signal by the A / D converter 132. Here, the interference light sampling of the differential detector 131 is performed at equal wavenumber intervals based on the k clock signal transmitted by the clock generator incorporated in the wavelength sweep light source 110. Then, the digital signal output by the A / D converter 132 is sent to the computer 140. After that, the computer 140 performs signal processing on the interference signal converted into a digital signal, and generates an OCT angiography image (hereinafter, referred to as "OCTA image") by calculation.

The CPU included in the computer 140 executes various processes. Specifically, the CPU of the computer 140 functions as the generation means 141, the extraction means 142, the analysis means 143, the storage means 144, and the display control means 145 by executing the program stored in the storage device of the computer 140. The CPU and the storage device included in the computer 140 may be one or a plurality. That is, at least one processing device (CPU) and at least one storage device (ROM, RAM, etc.) are connected, and at least one processing device executes a program stored in at least one storage device. If so, the computer 140 functions as the above-mentioned means 141 to 145.

Hereinafter, the generation means 141, the extraction means 142, the analysis means 143, the storage means 144, and the display control means 145, which are functional configurations of the computer 140, will be described.

The generation means 141 is a digital interference signal based on a digital signal output from the A / D converter 132 (a digital interference signal based on the interference light between the return light from the test eye E and the reference light of the measurement light scanned with respect to the test eye E). ) Is used to generate an OCTA image. Here, the OCTA image corresponds to a blood vessel-containing image including a blood vessel of the eye E (specifically, the fundus Ef in this embodiment). Hereinafter, an example of a method for generating an OCTA image by the generation means 141 will be described.

First, the generation means 141 acquires a tomographic image by Fourier transforming the interference signal acquired from the A / D converter 132. Specifically, the generation means 141 acquires an OCT complex signal composed of a phase and an amplitude by applying a fast Fourier transform (FFT) to the interference signal. The maximum entropy method may be used for frequency analysis. Further, the generation means 141 obtains a tomographic image showing the integrity (hereinafter, may be simply referred to as “tomographic image”) by squaring the absolute value of the OCT complex signal and calculating the signal intensity (Intensity). .. This tomographic image corresponds to an example of tomographic image data showing a tomographic fault of the fundus Ef of the eye E to be inspected. That is, when the measurement light is scanned a plurality of times at substantially the same position of the fundus Ef of the eye E to be inspected, the generation means 141 will acquire a plurality of tomographic image data indicating the tomography at substantially the same position of the subject. The plurality of tomographic image data are data acquired by the measurement light scanned at different timings.

The generation means 141 also functions as a means for controlling the X-axis scanner 153 and the Y-axis scanner 154.

Subsequently, the generation means 141 aligns a plurality of tomographic images. In the present embodiment, the generation means 141 aligns a plurality of tomographic images obtained by scanning substantially the same position of the fundus Ef of the eye E to be inspected with the measurement light a plurality of times. More specifically, the generation means 141 aligns a plurality of tomographic image data with each other before calculating the motion contrast value.

Alignment of tomographic images can be achieved by various known methods. The generation means 141 aligns a plurality of tomographic images so that the correlation between the tomographic images is maximized, for example. If the subject is not a specimen that moves like an eye, this alignment process is not necessary. Further, even if the subject is an eye, if the tracking performance is high, this alignment process is unnecessary. That is, the alignment of the tomographic images by the generation means 141 is not essential.

Subsequently, the generation means 141 calculates the motion contrast feature amount (hereinafter, may be referred to as “motion contrast value”). Here, the motion contrast is a contrast between a tissue having a flow (for example, blood) and a tissue having no flow among the tissue of the subject, and the feature amount expressing this motion contrast is defined as the motion contrast feature amount.

The motion contrast feature amount is calculated based on the change in data between a plurality of tomographic images obtained by scanning substantially the same position a plurality of times with the measurement light. For example, the generation means 141 calculates the variance of the signal strength (luminance) of a plurality of aligned tomographic images as a motion contrast feature amount. More specifically, the generation means 141 calculates the variance of the signal intensity at each corresponding position of the plurality of aligned tomographic images as a motion contrast feature amount. For example, since the signal intensity of the image corresponding to the blood vessel at a predetermined time and the signal intensity of the image corresponding to the blood vessel at a time different from the predetermined time change depending on the blood flow, the dispersion value of the portion corresponding to the blood vessel is the blood flow, etc. It is a large value compared to the dispersion value of the part where there is no flow of. That is, the motion contrast value is a value that increases as the change in the subject between the plurality of tomographic image data increases. Therefore, it is possible to express the motion contrast by generating an image based on this dispersion value. The motion contrast feature amount is not limited to the dispersion value, and may be, for example, any of a standard deviation, a difference value, a non-correlation value, and a correlation value. Although the generation means 141 uses the dispersion of the signal strength or the like, the motion contrast feature amount may be calculated by using the dispersion of the phase or the like.

Subsequently, the generation means 141 generates an averaged image by calculating the average value of the plurality of aligned tomographic images. This averaged image is a tomographic image in which the signal intensities of a plurality of tomographic images are averaged. This averaged image may be referred to as an Integrity averaged image. The generation means 141 compares the signal strength of the averaged image with the threshold value. When the signal intensity at a predetermined position of the averaged image is lower than the threshold value, the generation means 141 uses the motion contrast feature amount obtained based on the variance corresponding to the predetermined position of the averaged image as the feature amount indicating the blood vessel. Set to a different value from. For example, when the signal intensity of the averaged image is lower than the threshold value, the generation means 141 sets the motion contrast feature amount obtained based on the dispersion or the like to 0. That is, the generation means 141 sets the motion contrast value when the representative value indicating the signal strength is lower than the threshold value to be lower than the motion contrast value when the representative value indicating the signal strength is higher than the threshold value. The generation means 141 may compare the signal strength of the averaged image with the threshold value before calculating the variance of the signal strength of the plurality of tomographic images as the motion contrast feature amount. For example, the generation means 141 calculates the motion contrast feature amount as 0 when the signal strength of the averaged image is lower than the threshold value, and the signal strength of a plurality of tomographic images when the signal strength of the averaged image is higher than the threshold value. Is calculated as the motion contrast feature amount.

It should be noted that the motion contrast feature amount may not be completely set to 0, but may be set to a value in the vicinity of 0. On the other hand, when the signal intensity of the averaged image is higher than the threshold value, the generation means 141 maintains the motion contrast feature amount obtained based on the dispersion or the like. That is, the generation means 141 calculates the motion contrast value based on the plurality of tomographic image data, and recalculates the motion contrast value based on the comparison result between the representative value indicating the signal strength and the threshold value.

Although the signal strength of the averaged image (average value of the signal strength) was used as a comparison target with the threshold value, representative values such as the maximum value, the minimum value, the median value, etc. of the signal strength at the corresponding positions of the plurality of tomographic images. May be used. Further, instead of comparing the signal strength obtained from a plurality of tomographic images with the threshold value, the generation means 141 also compares the signal strength of one tomographic image with the threshold value and controls the motion contrast feature amount. good.

As described above, the generation means 141 calculates the motion contrast value based on the comparison result between the representative value and the threshold value of the plurality of tomographic image data and the plurality of tomographic image data indicating the signal strength.

Subsequently, the generation means 141 generates an OCTA image based on the motion contrast feature amount. The OCTA image is an image of the motion feature amount calculated by the generation means 141. For example, the larger the motion contrast feature amount is, the higher the brightness is, and the lower the motion contrast feature amount is, the lower the brightness is. Here, in the present embodiment, the portion having high brightness is a portion corresponding to a blood vessel. It should be noted that the larger the motion contrast feature amount, the lower the brightness, and the lower the motion contrast feature amount, the higher the brightness. This OCTA image may be referred to as a motion contrast image. That is, the generation means 141 generates a motion contrast image of the subject based on the motion contrast value as the OCTA image.

When the generation means 141 calculates the three-dimensional motion contrast feature amount (three-dimensional data) from the three-dimensional tomographic image data, the generation means 141 can generate a three-dimensional OCTA image. In addition, the generation means 141 can also generate a two-dimensional OCTA image projected or integrated in an arbitrary depth range in the retinal direction of the three-dimensional OCTA image. That is, the generation means 141 can also generate a two-dimensional motion contrast image as an OCTA image by projecting or integrating motion contrast values in a predetermined range in the depth direction of the subject in the depth direction.

Further, the generation means 141 can also cut out an arbitrary depth range in the retinal direction from the three-dimensional OCTA image to generate a partial three-dimensional OCTA image. That is, the generation means 141 can also generate a three-dimensional motion contrast image based on the motion contrast value in a predetermined range in the depth direction of the subject as the OCTA image.

The depth range in the direction of the retina can be set by the inspector (operator). For example, the computer 140 displays selectable layer candidates such as a layer from IS / OS to RPE and a layer from RPE to BM on the display unit 170. The inspector selects a predetermined layer from the displayed layer candidates. Then, the generation means 141 integrates in the depth direction of the retina in the layer selected by the examiner to generate a two-dimensional OCTA image (en-face blood vessel image) or a partial three-dimensional OCTA image. May be.

Further, the generation means 141 may generate an OCTA image corresponding to a tomographic image from the motion contrast feature amount.

The extraction means 142 extracts from the OCTA image generated by the generation means 141 an image region containing a blood vessel confluence, which is an image region including a blood vessel confluence in which at least two blood vessels merge to form one blood vessel. I do. The processing of the extraction means 142 will be described with reference to FIG.

FIG. 2 is a diagram showing an example of an image area extraction process by the extraction means 142 of FIG. Specifically, in FIG. 2, the extraction means 142 contains a blood vessel confluence portion including a blood vessel confluence portion in which at least two blood vessels merge into one blood vessel from the OCTA image 200 generated by the generation means 141. An example of extracting the image areas 210, 220, and 230 is shown.

Then, in the present embodiment, the generation means 141 rescans the region of the fundus Er of the eye E to be inspected corresponding to the blood vessel confluence-containing image region extracted by the extraction means 142, and creates the blood vessel confluence-containing image region. Generate such an OCTA image.

FIG. 3 is a diagram showing an example of an OCTA image 300 related to a blood vessel confluence-containing image region generated by the generation means 141 of FIG. 1. The OCTA image 300 shown in FIG. 3 is an OCTA image corresponding to the blood vessel confluence-containing image region 210 shown in FIG. Further, the OCTA image 300 shown in FIG. 3 is an image relating to an image region including a blood vessel confluence portion (blood vessel confluence point) 301 in which two blood vessels 310 and 320 merge to form one blood vessel 330. Here, the blood vessel confluence portion (blood vessel confluence point) 301 is defined by, for example, the intersection of the center line of one blood vessel 310 and the center line of the other blood vessel 320 of the above-mentioned two blood vessels.

The analysis means 143 analyzes an image relating to the blood vessel confluence-containing image region extracted by the extraction means 142 (in this embodiment, an OCTA image relating to the blood vessel confluence-containing image region generated by the generation means 141). In one blood vessel 330 shown in FIG. 3, laminar flow information relating to the laminar flow of blood flowing from each of the two blood vessels 310 and 320 shown in FIG. 3 is acquired. Here, the analysis means 143 acquires, for example, information including information on the length of the laminar flow in the blood flow direction of the blood vessel 330 shown in FIG. 3 as the laminar flow information. Further, as laminar flow information, the analysis means 143 is, for example, the ratio of the laminar flow of blood flowing from the blood vessel 310 shown in FIG. 3 to the laminar flow of blood flowing from the blood vessel 320 in the blood vessel 330 shown in FIG. Acquire information including information on laminar flow ratio. Further, the analysis means 143 provides laminar flow information, for example, comparative information comparing the blood vessel diameter ratio, which is the ratio between the blood vessel diameter of the blood vessel 310 and the blood vessel diameter of the blood vessel 320 shown in FIG. 3, and the above-mentioned laminar flow ratio. Get information including. Here, when the analysis means 143 acquires the laminar flow information, the luminance profile is acquired from the OCTA image, and the laminar flow information is acquired using the luminance profile. Hereinafter, the luminance profile used by the analysis means 143 to acquire the laminar flow information will be described.

FIG. 4 is a diagram showing an example of a luminance profile acquired by the analysis means 143 of FIG. Hereinafter, FIG. 4 will be described with reference to FIG.

FIG. 4A is a direction that intersects (for example, orthogonally) with the blood flow direction of the blood vessel 330 with reference to the blood vessel confluence portion (blood vessel confluence point) 301 shown in FIG. An example of the brightness profile of the line segment is shown. In FIG. 4A, the horizontal axis indicates the distance (number of pixels) from the measurement point 302 to the measurement point 303, and the vertical axis indicates the brightness value (shading value). In FIG. 4A, the blood flow (laminar flow) of the blood flowing from the blood vessel 310 and the blood of the blood flowing from the blood vessel 320 crossing the measurement points 302 and the measurement points 303 shown in FIG. 3 at both ends. Two maximum brightness values a1 and b1 indicating a flow (laminar flow) are shown. Specifically, FIG. 4A shows a first brightness maximum value a1 regarding blood flow (laminar flow) of blood flowing from the blood vessel 310 between 20 and 30 on the horizontal axis, and 55 on the horizontal axis. The second maximum brightness value b1 regarding the blood flow (laminar flow) of the blood flowing from the blood vessel 320 is shown between. At this point, since the shape and laminar flow of red blood cells in the blood vessels are maintained at the blood vessel confluence portion (vascular confluence point) 301, FIG. 4A shows two blood vessels 310 and 320 in a single blood vessel 330. It means that two maximum brightness values a1 and b1 indicating the laminar flow of blood flowing in from each of the above are observed. Further, FIG. 4A shows a luminance minimum value c1 between the first luminance maximum value a1 and the second luminance maximum value b1, and the portion of the luminance minimum value c1 is shown in FIG. In the OCTA image 300 shown, it is black, and it can be seen that it is a portion where there is no change (that is, a portion where there is no blood flow).

FIG. 4B crosses (for example, orthogonally) the blood flow direction of the blood vessel 330 at a position moved 10 pixels downstream from the blood vessel confluence portion (blood vessel confluence point) 301 shown in FIG. 3 to the downstream side of the blood flow direction of the blood vessel 330. An example of the brightness profile of the line segment having the measurement point 304 and the measurement point 305 at both ends is shown. Also in FIG. 4 (b), the first brightness maximum value a2 regarding the blood flow (layer flow) of the blood flowing from the blood vessel 310 and the second brightness maximum value regarding the blood flow (layer flow) of the blood flowing from the blood vessel 320. The value b2 and the brightness minimum value c2 between these brightness maximum values are shown.

FIG. 4C crosses the blood flow direction of the blood vessel 330 at a position further moved downstream from the line segment having the measurement points 304 and the measurement points 305 shown in FIG. 3 to the downstream side of the blood flow direction of the blood vessel 330 (for example,). An example of a brightness profile of a line segment having a measurement point 306 and a measurement point 307 at both ends in a direction (perpendicular) is shown. Also in FIG. 4 (c), the first brightness maximum value a3 regarding the blood flow (layer flow) of the blood flowing from the blood vessel 310 and the second brightness maximum regarding the blood flow (layer flow) of the blood flowing from the blood vessel 320. The value b3 and the brightness minimum value c3 between these brightness maximum values are shown.

FIG. 4D crosses the blood flow direction of the blood vessel 330 at a position further moved downstream of the blood flow direction of the blood vessel 330 from the line segment having the measurement points 306 and the measurement point 307 at both ends shown in FIG. An example of the brightness profile of the line segment having the measurement points 308 and the measurement points 309 at both ends in the direction (perpendicular) is shown. Also in FIG. 4 (d), the first luminance maximum value a4 relating to the blood flow of the blood flowing from the blood vessel 310, the second luminance maximum value b4 relating to the blood flow of the blood flowing from the blood vessel 320, and these luminance maximum values. A slight luminance minimum value c4 is observed between them, but there is almost no difference. Therefore, in the present embodiment, as a criterion for determining that there is no laminar flow of blood flowing from each of the blood vessel 310 and the blood vessel 320 in the blood vessel 330, the brightness maximum value having the minimum brightness value (in FIG. 4D, the brightness is the brightness). When the maximum value a4) is Ip and the minimum luminance value (in FIG. 4D, the minimum luminance value c4) is Ib, the case where Ib / Ip ≧ 0.95 is adopted. Since a single luminance peak is usually observed in a single blood vessel, the above-mentioned criterion is adopted, in which the luminance maximum value Ip and the luminance minimum value Ib are considered to be substantially the same. In this embodiment, Ib / Ip ≧ 0.95 is adopted as a criterion for determining that there is no laminar flow of blood flowing from each of the blood vessel 310 and the blood vessel 320 in the blood vessel 330, but this is an example even if it gets tired. For example, adopting Ib / Ip ≧ 0.90 or adopting other criteria is applicable to the present invention. That is, the "predetermined value" when Ib / Ip becomes a predetermined value or more can be appropriately changed.

As described above, the analysis means 143 acquires the laminar flow information by analyzing the luminance profile described with reference to FIG.

Here, the description of FIG. 1 is returned to again.
The storage means 144 stores various information, data, programs, and the like necessary for the computer 140 to perform various controls and processes. Further, the storage means 144 stores various information, data, and the like obtained by performing various controls and processes by the computer 140. For example, the storage means 144 stores the laminar flow information measured in the past for each eye E to be inspected. Further, for example, the storage means 144 is assumed to store a normalative database (NDB) which is a database of normal eyes of each race, and laminar flow information of normal eyes is stored as one of the information. It shall be.

The display control means 145 controls to display the laminar flow information obtained by the analysis means 143 on the display unit 170. Further, the display control means 145 displays the OCTA image generated by the generation means 141, various information obtained by the extraction means 142 and the analysis means 143, various information stored in the storage means 144, and the like. It also controls the display on.

The display unit 170 displays various images, various information, and the like based on the control of the display control means 145. The display unit 170 is, for example, a display such as a liquid crystal display. The display unit 170 has laminar flow information obtained by the analysis means 143, OCTA images generated by the generation means 141, and various types obtained by the extraction means 142 and the analysis means 143 under the control of the display control means 145. Information, various information stored in the storage means 144, and the like are displayed.

Next, the processing procedure in the control method of the ophthalmic apparatus 100 will be described.
FIG. 5 is a flowchart showing an example of a processing procedure in the control method of the ophthalmic apparatus 100 according to the embodiment of the present invention.

For example, when an instruction to take an image of the eye E to be inspected is given from a user interface (not shown), in step S101, the computer 140 (for example, the generation means 141) reads out an interference signal which is an image pickup signal from the interference light detection unit 130. I do. At this time, in this step, the data related to the interference signal that has been read in advance from the interference light detection unit 130 and stored as stored data in the storage means 144 may be read out.

Subsequently, in step S102, the generation means 141 performs a process of generating the above-mentioned OCTA image (for example, 200 in FIG. 2) based on the interference signal which is the image pickup signal read in step S101.

Subsequently, in step S103, the extraction means 142 determines whether or not the OCTA image generated in step S102 has a blood vessel and whether or not there is a blood vessel confluence portion where at least two blood vessels merge to form one blood vessel. do.

As a result of the determination in step S103, if the OCTA image generated in step S102 has blood vessels and has a blood vessel confluence (S103 / YES), the extraction means 142 includes the blood vessel confluence from the OCTA image. The image region containing the blood vessel confluence is extracted. Examples of the blood vessel confluence-containing image region extracted by the extraction means 142 include the blood vessel confluence-containing image regions 210, 220, and 230 shown in FIG. Then, the process proceeds to step S104.
Proceeding to step S104, the generation means 141 rescans the region of the fundus Er of the eye E to be inspected corresponding to the blood vessel confluence-containing image region extracted by the extraction means 142, and the generation means 141 contains the blood vessel confluence. Generate an OCTA image for the image area. Examples of the OCTA image generated in this step include the OCTA image 300 shown in FIG. Here, in this step, in order to improve the analysis accuracy, in order to generate an OCTA image having a higher resolution than the OCTA image generated in step S102, the fundus Er of the eye fundus E corresponding to the image region containing the blood vessel confluence portion. Rescan the area at specified intervals (eg 5 μm).

Subsequently, in step S105, the analysis means 143 obtains the position coordinates of the blood vessel confluence portion (blood vessel confluence point) from which at least two blood vessels merge to form one blood vessel from the OCTA image generated in step S104. Perform the processing. For example, the position coordinates of the blood vessel confluence portion (blood vessel confluence point) 301 shown in FIG. 3 are acquired. In the present embodiment, the OCTA image 300 is image-processed, and the intersection of the center line of the blood vessel 310 and the center line of the blood vessel 320 is acquired as the blood vessel confluence portion (blood vessel confluence point) 301, for example, the user. It may be acquired based on the position specified by the interface.

Subsequently, in step S106, the analysis means 143 performs a process of acquiring the luminance profile at the blood vessel confluence portion (blood vessel confluence point) for which the position coordinates were acquired in step S106 from the OCTA image generated in step S104. Here, for example, with reference to the blood vessel confluence portion (blood vessel confluence point) 301 shown in FIG. 3, the brightness of the line segment in the direction intersecting the blood flow direction of the blood vessel 330 with the measurement point 302 and the measurement point 303 at both ends. Acquire a profile (luminance profile shown in FIG. 4A).

Subsequently, in step S107, the analysis means 143 determines whether or not there are two or more peaks (maximum luminance values) in the luminance profile acquired in step S106. For example, in the case of the luminance profile shown in FIG. 4A, since there are two or more luminance maximum values including the luminance maximum values a1 and b1, a positive judgment (S107 / YES) is made in this step. ..

As a result of the determination in step S107, if there are two or more peaks (maximum luminance values) in the luminance profile acquired in step S106, the process proceeds to step S108.
Proceeding to step S108, the analysis means 143 analyzes the OCTA image generated in step S104 and obtains laminar flow information relating to the laminar flow of blood flowing from each of the plurality of blood vessels before merging in the blood vessel after merging. Perform the process of acquisition.

FIG. 6 is a diagram for explaining the laminar flow information obtained in the analysis process of step S108 of FIG. The OCTA image 600 shown in FIG. 6 is an enlarged image of the OCTA image 300 shown in FIG. 3, and the same reference numerals are given to the same configurations as those shown in FIG. 3 in FIG. In step S108 of FIG. 5, the analysis means 143 has, for example, information on the length 610 of the laminar flow in the blood flow direction of the blood vessel 330 shown in FIG. 6 and the layer of blood flowing from the blood vessel 310 in the blood vessel 330 shown in FIG. Information on the laminar flow ratio, which is the ratio between the flow width 621 and the laminar flow width 622 of the blood flowing from the blood vessel 320, is acquired as laminar flow information. Further, the analysis means 143 calculates, for example, a blood vessel diameter ratio which is a ratio between the blood vessel diameter 623 of the blood vessel 310 and the blood vessel diameter 624 of the blood vessel 320 shown in FIG. Acquire the compared comparison information as tier flow information. The details of step S108 in FIG. 5 will be described later with reference to FIGS. 7 and 8.

When the process of step S108 is completed, when a negative determination is made in step S107 (S107 / NO), or when a negative determination is made in step S103 (S103 / NO), the process proceeds to step S109.
Proceeding to step S109, the display control means 145 controls to display the laminar flow information and the like obtained in the analysis process of step S108 on the display unit 170 together with the OCTA image generated by the generation means 141, if necessary. conduct. Further, the display control means 145 also displays the blood vessel merging portion information including the presence / absence of the blood vessel and the presence / absence of the blood vessel merging portion in step S103, the luminance profile acquired in step S106, the determination result information of step S107, and the like on the display unit 170. Control the display. Then, when the processing of step S109 is completed, the processing of the flowchart shown in FIG. 5 is completed.

Next, two embodiments shown in FIGS. 7 and 8 will be described with respect to the detailed processing procedure in the analysis process of step S108 of FIG.

First, FIG. 7 will be described.
FIG. 7 is a flowchart showing an example of a detailed processing procedure according to the first aspect in the analysis processing of step S108 of FIG. In FIG. 7, the aspect 1 in the analysis process of step S108 is illustrated as step S108-1. Specifically, the first aspect of the analysis process of step S108 is to acquire information on the length of the laminar flow 610 in the blood flow direction of the blood vessel 330 shown in FIG. 6 as the laminar flow information.

When step S108-1 shown in FIG. 7 is started, first, in step S201, the analysis means 143 reads out the position coordinates of the blood vessel confluence portion (blood vessel confluence point) acquired in step S105.

Subsequently, in step S202, the analysis means 143 stores and stores the position coordinates of the blood vessel confluence portion (blood vessel confluence point) read out in step S201 in the storage means 144.

Subsequently, in step S203, the analysis means 143 moves 10 pixels downstream from the previously measured position coordinates (initially the position coordinates of the blood vessel confluence) to the downstream side of the blood vessel 330 in the blood flow direction shown in FIG. 3, and the moved position. Get the brightness profile in coordinates. Here, for example, the luminance profile as shown in FIGS. 4 (b) to 4 (d) is acquired.

Subsequently, in step S204, the analysis means 143 sets the luminance maximum value having the minimum luminance value (for example, the luminance maximum value a4 in FIG. 4D) as Ip from the luminance profile acquired in step S203, and sets the luminance maximum value. The minimum luminance value between them (for example, the minimum luminance value c4 in FIG. 4D) is acquired as Ib.

Subsequently, in step S205, the analysis means 143 determines whether or not Ib / Ip ≧ 0.95. As a result of this determination, if Ib / Ip ≧ 0.95 (that is, Ib / Ip <0.95) (S205 / NO), the blood vessel 310 in the position coordinates obtained in the brightness profile in step S203. It is determined that the laminar flow of blood flowing in from each of the blood vessel 320 and the blood vessel 320 is still observed, and the process returns to step S203 to perform the processing after step S203.

On the other hand, if Ib / Ip ≧ 0.95 as a result of the determination in step S205 (S205 / YES), the process proceeds to step S206.
Proceeding to step S206, the analysis means 143 stores the position coordinates determined that Ib / Ip ≧ 0.95 in the storage means 144. Here, the position coordinates determined that Ib / Ip ≧ 0.95 are the position coordinates of the laminar flow limit point 601 shown in FIG.

Subsequently, in step S207, the analysis means 143 has the position coordinates of the laminar flow limit point 601 shown in FIG. 6 saved in step S206 and the position of the blood vessel confluence portion (blood vessel confluence point) shown in FIG. 6 saved in step S202. From the coordinates, the laminar flow length 610 (also referred to as laminar flow length l) shown in FIG. 6 is calculated. Here, in the example shown in FIG. 6, the laminar flow length 610 (laminar flow length l) was measured at about 15 μm. When the processing of step S207 is completed, the processing of the flowchart shown in FIG. 7 is completed.

In the processing of the flowchart shown in FIG. 7, an example in which the luminance profile is acquired by moving 10 pixels in step S203 is shown. Can make measurements. Further, although the threshold value is set to 0.95 (95%) in the determination in step S205, the measurement can be performed in the same manner even if any value is used due to the relationship with image noise and the like.

Next, FIG. 8 will be described.
FIG. 8 is a flowchart showing an example of a detailed processing procedure according to the second aspect in the analysis processing of step S108 of FIG. In FIG. 8, the second aspect of the analysis process of step S108 is shown as step S108-2. Specifically, in the second aspect of the analysis process of step S108, as laminar flow information, the width 621 of the laminar flow of blood flowing from the blood vessel 310 and the width 622 of the laminar flow of blood flowing from the blood vessel 320 are shown in FIG. Information on the laminar flow ratio, which is the ratio, is acquired. Further, as a modification of the second aspect in the analysis process of step S108, as laminar flow information, the blood vessel diameter ratio which is the ratio between the blood vessel diameter 623 of the blood vessel 310 and the blood vessel diameter 624 of the blood vessel 320 shown in FIG. 6 and the above-mentioned layer. It obtains comparative information comparing with the flow ratio.

When step S108-1 shown in FIG. 8 is started, first, in step S301, the analysis means 143 reads out the position coordinates of the blood vessel confluence portion (blood vessel confluence point) acquired in step S105.

Subsequently, in step S302, the analysis means 143 moves 10 pixels from the position coordinates of the blood vessel confluence portion (blood vessel confluence point) to the downstream side in the blood flow direction of the blood vessel 330 shown in FIG. To get. Here, for example, the luminance profile shown in FIG. 4B is acquired.

Subsequently, in step S303, the analysis means 143 has a mountain-shaped first luminance distribution width corresponding to the laminar flow of blood flowing in from one of the blood vessels 310 from the luminance profile acquired in step S302 (FIG. 4 (b). ) And the width of the mountain-shaped second luminance distribution corresponding to the laminar flow of blood flowing from the other blood vessel 320 (Fb shown in FIG. 4B) are acquired. Here, the width Fa of the first luminance distribution can be regarded as the width 621 of the laminar flow of blood flowing from the blood vessel 310, and the width Fb of the second luminance distribution is the laminar flow of blood flowing from the blood vessel 320. It shall be regarded as a width 622. Further, for example, in FIG. 4B, it is desirable that the widths Fa and Fb of the respective luminance distributions are full width at half maximum (FWHM). However, since the position and intensity of the luminance minimum value c2 in FIG. 4B are values that are difficult to measure by FWHM, the widths Fa and Fb of the respective luminance distributions are measured with reference to the position of the luminance minimum value c2. There is.

Subsequently, in step S304, the analysis means 143 obtains a laminar flow ratio (Fa / Fb) represented by the ratio of the width Fa of the first luminance distribution and the width Fb of the second luminance distribution acquired in step S303. calculate. After that, the analysis means 143 stores and stores the calculated laminar flow ratio (Fa / Fb) in the storage means 144. When the processing of step S304 is completed, the processing of the flowchart shown in FIG. 8 is completed.

As a modification of the second aspect in the analysis process of step S108, first, the analysis means 143 has a blood vessel diameter Da of the blood vessel 310 before merging (623 shown in FIG. 6) and a blood vessel diameter Db of the blood vessel 320 before merging (FIG. 6). The blood vessel diameter ratio (Da / Db), which is the ratio to 624) shown in 6, is calculated. Then, the analysis means 143 acquires comparative information comparing the above-mentioned laminar flow ratio (Fa / Fb) and blood vessel diameter ratio (Da / Db). By displaying this comparative information, it is possible to provide information that can be used for disease diagnosis of the eye E to be inspected.

Further, in the present embodiment, the display control means 145 displays the laminar flow information of the eye to be inspected E stored in the storage means 144 in the past together with the laminar flow information of the eye to be inspected E acquired by the analysis means 143. It also controls the display on 170. By performing this display control, it becomes possible to perform follow-up observation (functional deterioration, etc.) of the eye E to be inspected. When performing this follow-up, it is desirable to observe the same conditions, methods, and the same locations.

Further, in the present embodiment, the display control means 145 displays the laminar flow information of the normal eye stored in the storage means 144 together with the laminar flow information of the eye to be inspected E acquired by the analysis means 143 on the display unit 170. It also controls. By performing this display control, it becomes possible to diagnose a disease (lifestyle-related disease, etc.) of the eye E to be inspected while comparing it with a normal eye. When performing comparative observation with this normal eye, it is desirable to observe the same conditions, methods, and the same location.

As described above, in the ophthalmic apparatus 100 according to the present embodiment, an OCTA image including the blood vessel of the eye E to be inspected is generated (S102 in FIG. 5), and at least two blood vessels 310 and 320 are included in the OCTA image. An image region containing a blood vessel confluence including a blood vessel confluence that merges into one blood vessel 330 is extracted (S103 in FIG. 5), an image related to the blood vessel confluence-containing image region is analyzed, and the blood vessel 310 in the blood vessel 330. The laminar flow information related to the laminar flow of the blood flowing in from each of the and 320 is acquired (S108 in FIG. 5), and the control is performed to display the laminar flow information on the display unit 170 (S109 in FIG. 5). ..
According to this configuration, since the laminar flow information of the blood flowing in the blood vessel of the subject E is acquired and displayed, the blood flow state of the subject E can be grasped, and as a result, the subject's blood flow state can be grasped. It is possible to provide the user with information that can be used for disease diagnosis of the eye E to be inspected while minimizing the burden.

(Other embodiments)
In the above-described embodiment of the present invention, in order to improve the analysis accuracy, rescanning is performed in step S104 of FIG. 5 to generate an OCTA image having a higher resolution than the OCTA image generated in step S102, and the rescanning is performed. Although it was a form in which an analysis process was performed on an OCTA image obtained by scanning, the present invention is not limited to this form. For example, if the image quality of the OCTA image generated in step S102 of FIG. 5 is considered to be sufficient, the extraction means 142 extracts from the OCTA image generated in step S102 in step S103 without performing the processing of step S104. A form in which an analysis process is performed on an image in an image region containing a blood vessel confluence is also applicable to the present invention. In step S104 of FIG. 5, in order to generate a higher resolution OCTA image, the spot diameter of the light beam by the wavelength sweep light source 110 at the time of rescanning may be changed. Further, at the time of rescanning, it is desirable to scan the blood vessel 330 after merging perpendicularly to the blood flow direction.

The above-described embodiment of the present invention has shown a mode in which laminar flow information of blood flowing in a blood vessel of an eye E to be inspected is acquired using an OCTA image relating to a plane of the fundus of the eye, but the present invention is limited to this mode. is not it. For example, a form of acquiring laminar flow information of blood flowing in the blood vessel of the eye E to be examined by using an OCTA tomographic image (OCTA-B scan image) is also applicable to the present invention. Further, the laminar flow information of the blood flowing in the blood vessel of the eye E to be inspected may be acquired from the numerical value (graph or the like) instead of the image by using the original data (before and after signal processing) of the OCTA tomographic image.

Further, in the above-described embodiment of the present invention, the blood vessel confluence portion (blood vessel confluence point) 301 is defined by the intersection of the center line of the blood vessel 310 and the center line of the blood vessel 320, but the present invention is limited to this embodiment. Other forms, such as the intersection of blood vessel walls, are also applicable. Furthermore, the apparatus, control method and program according to the embodiment of the present invention are not necessarily limited to the apparatus related to ophthalmology and the control method and program thereof. As the blood vessel-containing image, in addition to the image relating to the eye to be inspected, a blood vessel image contained in the breast, heart, or the like of the subject can be targeted. Blood vessel images of various parts of the subject can be taken, for example, by using ultrasonic waves or photoacoustic waves.

Further, in the above-described embodiment of the present invention, an example in which an OCTA image is applied as a blood vessel-containing image containing a blood vessel of the eye E to be inspected has been described, but the present invention is not limited to this embodiment. For example, as a blood vessel-containing image containing a blood vessel of the eye E to be inspected, a form in which a fundus image obtained by a fluorescent fundus angiography or an SLO image (Scanning Laser Ophthalmoscope) is applied is also applicable to the present invention.
FIG. 9 is a diagram showing an embodiment of the present invention and showing an example in which a fundus image obtained by a fluorescence fundus angiography method is applied as a blood vessel-containing image including a blood vessel of the eye E to be inspected. In the case of the example shown in FIG. 9, the image region 910 containing the blood vessel confluence is extracted from the fundus image 900 obtained by the fluorescent fundus imaging method, and the above-mentioned analysis process is performed.

The present invention supplies a program that realizes one or more functions of the above-described embodiment to a system or device via a network or storage medium, and one or more processors in the computer of the system or device reads and executes the program. It can also be realized by the processing to be performed. It can also be realized by a circuit (for example, ASIC) that realizes one or more functions.
This program and a computer-readable storage medium that stores the program are included in the present invention.

It should be noted that the above-described embodiments of the present invention are merely examples of embodiment of the present invention, and the technical scope of the present invention should not be construed in a limited manner by these. Is. That is, the present invention can be implemented in various forms without departing from the technical idea or its main features.

100: Ophthalmic apparatus, 110: Wavelength sweep light source, 120: Optical signal branch / combine unit, 130 Interference light detection unit, 140: Computer, 141: Generation means, 142: Extraction means, 143: Analysis means, 144: Storage means 145: Display control means, 150: Measurement arm, 160: Reference arm, 170: Display unit, E: Eye to be inspected, Ef: Bottom of the eye

Claims (15)

A generation means for generating an OCTA image, which is a blood vessel-containing image including a blood vessel of an eye to be inspected,
An extraction means for extracting an image region including a blood vessel confluence portion in which at least two blood vessels merge to form one blood vessel from the OCTA image.
An acquisition means for acquiring a plurality of luminance profiles in a direction intersecting the blood flow direction of the one blood vessel from the image region including the blood vessel confluence portion.
An analysis means for analyzing the plurality of luminance profiles and acquiring laminar flow information related to the laminar flow of blood flowing from each of the two blood vessels in the one blood vessel.
It has a display control means for controlling the display of the laminar flow information on the display unit.
The analysis means is an ophthalmic apparatus, characterized in that, as the laminar flow information, information including information on the length of the laminar flow in the blood flow direction of the one blood vessel is acquired . A generation means for generating an OCTA image, which is a blood vessel-containing image including a blood vessel of an eye to be inspected,
An extraction means for extracting an image region including a blood vessel confluence portion in which at least two blood vessels merge to form one blood vessel from the OCTA image.
An acquisition means for acquiring a plurality of luminance profiles in a direction intersecting the blood flow direction of the one blood vessel from the image region including the blood vessel confluence portion.
An analysis means for analyzing the plurality of luminance profiles and acquiring laminar flow information related to the laminar flow of blood flowing from each of the two blood vessels in the one blood vessel.
A display control means for controlling the display of the laminar flow information on the display unit.
Have,
The analysis means uses the laminar flow information as laminar flow of blood flowing from one of the two blood vessels and blood flowing from the other of the two blood vessels in the one blood vessel. An ophthalmic apparatus characterized by acquiring information including information on a laminar flow ratio, which is a ratio to a laminar flow. From the brightness profile, the analysis means has a first brightness maximum value corresponding to a laminar flow of blood flowing from one of the two blood vessels and an inflow from the other of the two blood vessels. The second luminance maximum value corresponding to the stratified flow of blood and the luminance minimum value between the first luminance maximum value and the second luminance maximal value are acquired, and the first luminance maximal value is acquired. The ophthalmic apparatus according to claim 1, wherein the information on the length of the layer flow is acquired by using the second maximum luminance value and the minimum luminance value. The analysis means of the laminar flow according to the value of the ratio of the luminance maximum value to the luminance minimum value of the first luminance maximum value and the second luminance maximum value, whichever has the smaller luminance value. The ophthalmic apparatus according to claim 3, wherein the information on the length is acquired. The analysis means calculates the value of the ratio of the brightness minimum value to the brightness maximum value as the value of the ratio, and the position where the brightness profile is acquired and the blood vessel confluence portion where the value of the ratio is equal to or more than a predetermined value. The ophthalmic apparatus according to claim 4, wherein the information on the length of the laminar flow is acquired according to the position and the length of the laminar flow. From the brightness profile, the analysis means has the width of the mountain-shaped first brightness distribution corresponding to the laminar flow of blood flowing from one of the two blood vessels and the other of the two blood vessels. The width of the mountain-shaped second luminance distribution corresponding to the laminar flow of blood flowing from the blood vessel of the blood vessel is obtained, and the value of the ratio between the width of the first luminance distribution and the width of the second luminance distribution is set. The ophthalmic apparatus according to claim 2 , wherein the information on the laminar flow ratio is acquired accordingly. The analysis means is
The blood vessel diameter of each of the two blood vessels is obtained, and the blood vessel diameter ratio, which is the ratio of the respective blood vessel diameters, is calculated.
The ophthalmologic apparatus according to claim 2 or 6 , wherein as the laminar flow information, information including comparative information comparing the laminar flow ratio and the blood vessel diameter ratio is acquired. The generation means further generates an OCTA image including the blood vessel confluence portion of the eye to be inspected corresponding to the image region as an image relating to the image region.
The method according to any one of claims 1 to 7 , wherein the analysis means analyzes an OCTA image including the blood vessel confluence portion generated by the generation means to acquire the laminar flow information. Ophthalmic device. Further having a storage means for storing the past laminar flow information of the eye to be inspected,
Claims 1 to 8 are characterized in that the display control means controls to display the past laminar flow information stored in the storage means on the display unit together with the laminar flow information acquired by the analysis means. The ophthalmic apparatus according to any one of the above. Further having a storage means for storing the laminar flow information of a normal eye,
The display control means is characterized in that it controls to display the laminar flow information of a normal eye stored in the storage means on the display unit together with the laminar flow information acquired by the analysis means. 9. The ophthalmic apparatus according to any one of 9. A generation step to generate an OCTA image, which is a blood vessel-containing image containing blood vessels,
An extraction step of extracting an image region including a blood vessel confluence portion in which at least two blood vessels merge to form one blood vessel from the OCTA image.
An acquisition step of acquiring a plurality of luminance profiles in a direction intersecting the blood flow direction of the one blood vessel from the image region including the blood vessel confluence portion.
An analysis step of analyzing the plurality of luminance profiles to acquire laminar flow information relating to the laminar flow of blood flowing from each of the two blood vessels in the one blood vessel.
It has a display control step that controls the display of the laminar flow information on the display unit.
A method for controlling an apparatus, which comprises acquiring information including information on the length of the laminar flow in the blood flow direction of the one blood vessel as the laminar flow information in the analysis step . A generation step to generate an OCTA image, which is a blood vessel-containing image containing blood vessels,
An extraction step of extracting an image region including a blood vessel confluence portion in which at least two blood vessels merge to form one blood vessel from the OCTA image.
An acquisition step of acquiring a plurality of luminance profiles in a direction intersecting the blood flow direction of the one blood vessel from the image region including the blood vessel confluence portion.
An analysis step of analyzing the plurality of luminance profiles to acquire laminar flow information related to the laminar flow of blood flowing from each of the two blood vessels in the one blood vessel.
A display control step that controls the display of the laminar flow information on the display unit.
Have,
In the analysis step, as the laminar flow information, the laminar flow of blood flowing from one of the two blood vessels and the blood flowing from the other of the two blood vessels in the one blood vessel. A method for controlling a device, which comprises acquiring information including information on a laminar flow ratio, which is a ratio to a laminar flow. The control method of the apparatus according to claim 11 or 12, wherein the OCTA image is an image including a blood vessel of an eye to be inspected. A program for causing a computer to execute each step of the device control method according to claim 11 or 12 . The program according to claim 14, wherein the OCTA image is an image including a blood vessel of an eye to be inspected.

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