JP2013153880A - Image processing system, processing method, and program - Google Patents

Image processing system, processing method, and program Download PDF

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JP2013153880A
JP2013153880A JP2012015931A JP2012015931A JP2013153880A JP 2013153880 A JP2013153880 A JP 2013153880A JP 2012015931 A JP2012015931 A JP 2012015931A JP 2012015931 A JP2012015931 A JP 2012015931A JP 2013153880 A JP2013153880 A JP 2013153880A
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analysis
tomographic image
image
image processing
imaging
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JP2013153880A5 (en
Inventor
Yoshihiko Iwase
好彦 岩瀬
Hiroyuki Arahata
弘之 新畠
Makoto Sato
眞 佐藤
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Canon Inc
キヤノン株式会社
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Abstract

【Task】
Provided is a technique in which a plurality of imaging modes including an imaging mode for myopic eye analysis are provided, and analysis processing is switched and executed according to the imaging mode at the time of imaging a tomographic image.
[Solution]
An image processing system acquires acquisition means for acquiring a tomographic image of the eye to be inspected, and information representing the degree of curvature of the retina from the tomographic image of the eye to be inspected according to an imaging mode at the time of imaging the eye to be inspected. Analyzing means for performing analysis.
[Selection] Figure 1

Description

  The present invention relates to an image processing system, a processing method, and a program.

  2. Description of the Related Art A tomographic imaging apparatus using optical coherence tomography (OCT) using interference by low coherent light is known. By photographing the fundus with such a tomographic imaging apparatus, the state inside the retinal layer can be observed three-dimensionally.

  Imaging using a tomographic imaging apparatus has attracted attention in recent years because it is a useful technique for more accurately diagnosing diseases. As a form of such OCT, for example, TD-OCT (Time domain OCT) in which a broadband light source and a Michelson interferometer are combined is known. In TD-OCT, by scanning the delay of the reference arm, the interference light with the backscattered light of the signal arm can be measured, and depth resolution information can be obtained.

  However, with TD-OCT, it is difficult to acquire images at high speed. Therefore, SD-OCT (Spectral domain OCT) in which an interferogram is acquired with a spectroscope using a broadband light source is known as a method for acquiring an image at a higher speed. Also known is SS-OCT (Swept Source OCT), which uses a high-speed wavelength swept light source as a light source to measure spectral interference with a single channel photodetector.

  Here, in the tomographic images taken with these OCTs, if the retinal morphological changes can be measured, the degree of progression of diseases such as glaucoma and the degree of recovery after treatment can be quantitatively diagnosed. In relation to such a technique, in Patent Document 1, in order to quantitatively measure the change in the shape of the retina, the boundary of each layer of the retina is detected from the tomographic image using a computer, and the layer is determined based on the detection result. A technique for measuring the thickness of the film is disclosed.

JP 2008-073099 A

  In the technique of Patent Document 1 described above, a tomographic image in a range specified on a two-dimensional image is acquired, and a layer boundary is detected to obtain a layer thickness. However, the analysis process is not changed according to the imaging method for analyzing the shape of the retinal layer or the imaging situation of the acquired tomographic image.

  The present invention has been made in view of the above problems, and provides a plurality of imaging modes including an imaging mode for myopic eye analysis, and switches and executes analysis processing according to the imaging mode at the time of imaging a tomographic image. The purpose is to provide the technology.

  In order to solve the above-described problem, an image processing system according to an aspect of the present invention includes an acquisition unit that acquires a tomographic image of an eye to be inspected, and a tomographic image of the eye to be inspected according to an imaging mode when the eye to be inspected is imaged. Analyzing means for performing analysis for acquiring information representing the degree of curvature of the retina.

  According to the present invention, a plurality of imaging modes including an imaging mode for myopic eye analysis are provided, and analysis processing can be switched and executed in accordance with the imaging mode at the time of imaging a tomographic image.

1 is a diagram illustrating an example of a configuration of an image processing system 10 according to an embodiment of the present invention. The figure which shows an example of the tomographic image imaging | photography screen 60. FIG. 3 is a flowchart illustrating an example of a processing flow of the image processing apparatus 30 illustrated in FIG. 1. The figure for demonstrating the outline | summary of a three-dimensional shape analysis process. The figure for demonstrating the outline | summary of a three-dimensional shape analysis process. The figure which shows an example of the tomographic image observation screen. The figure which shows an example of each part of the tomographic image observation screen. The figure which shows an example of each part of the tomographic image observation screen. The figure which shows an example of each part of the tomographic image observation screen. The figure which shows an example of the tomographic image observation screen. The figure which shows an example of each part of the tomographic image observation screen. The figure which shows an example of the tomographic image observation screen. The figure which shows an example of the tomographic image observation screen. The figure which shows an example of each part of the tomographic image observation screen. The figure which shows an example of the tomographic image observation screen. The figure which shows an example of each part of the tomographic image observation screen.

  Embodiments according to the present invention will be described below in detail with reference to the accompanying drawings.

(Embodiment 1)
FIG. 1 is a diagram showing an example of the configuration of an image processing system 10 according to an embodiment of the present invention.

  The image processing system 10 includes an image processing device 30, a tomographic imaging device 20, a fundus imaging device 51, an external storage device 52, a display device 53, and an input device 54.

  The tomographic imaging apparatus 20 is realized by, for example, SD-OCT or SS-OCT, and uses tomographic images showing a three-dimensional shape of the fundus using optical coherence tomography (OCT) using interference by low coherent light. Take a picture. The tomographic imaging apparatus 20 includes a galvanometer mirror 21, a drive control unit 22, a parameter setting unit 23, an internal fixation lamp 24, and a coherence gate stage 25.

  The galvanometer mirror 21 has a function of two-dimensionally scanning the fundus with measurement light (irradiation light), and defines the fundus imaging range of the tomographic imaging apparatus 20. The galvanometer mirror 21 is composed of, for example, two mirrors, an X-scan mirror and a Y-scan mirror, and scans the measurement light onto the surface perpendicular to the optical axis with respect to the fundus of the eye to be examined. .

  The drive control unit 22 controls the drive (scanning) range and speed of the galvanometer mirror 21. Thereby, the imaging range and the number of scanning lines (scanning speed in the plane direction) in the plane direction (direction orthogonal to the optical axis direction of the measurement light) in the fundus are defined.

  The parameter setting unit 23 sets various parameters used for drive control of the galvanometer mirror 21 by the drive control unit 22. Based on this parameter, the tomographic image capturing condition by the tomographic image capturing apparatus 20 is determined. For example, the scanning position of the scanning line, the number of scanning lines, the number of shots, etc. are determined. In addition, the position of the internal fixation lamp, the scanning range (scanning range), the scanning pattern (scanning pattern), the coherence gate position, and the like are also set. The parameter setting is performed based on an instruction from the image processing apparatus 30.

  The internal fixation lamp 24 places a bright spot in the field of view so that eye movement does not occur during tomographic image capturing, and suppresses movement of the viewpoint. The internal fixation lamp 24 includes a display unit 24a and a lens 24b. The display unit 24a is realized, for example, by arranging a plurality of light emitting diodes (LDs) in a matrix. The lighting position of the light emitting diode is changed according to the part to be imaged under the control of the drive control unit 22. Light from the display unit 24a is guided to the eye to be examined through the lens 24b. The light emitted from the display unit 24 a is, for example, 520 nm, and a desired pattern is displayed (lighted) under the control of the drive control unit 22.

  The coherence gate stage 25 is provided to cope with a difference in the axial length of the eye to be examined. More specifically, the optical path length of the reference light (for causing interference with the measurement light) is controlled to adjust the photographing position along the depth direction (optical axis direction) of the fundus. Thereby, the optical path lengths of the reference light and the measurement light can be made to coincide with each other with respect to the subject's eyes having different ocular axial lengths. The coherence gate stage 25 is controlled by the drive control unit 22.

  Here, the coherence gate indicates a position where the optical distance between the measurement light and the reference light in the tomographic imaging apparatus 20 is equal. By controlling the position of the coherence gate, switching can be switched between photographing on the retinal layer side or photographing based on an EDI (Enhanced Depth Imaging) method that is deeper than the retinal layer. When imaging is performed by the EDI method, the position of the coherence gate is set on the deep side of the retinal layer. Therefore, when the retinal layer is captured beyond the upper side of the tomographic image, the retinal layer is included in the tomographic image. It will not be reflected.

  The fundus image capturing apparatus 51 is realized by, for example, a fundus camera or an SLO (Scanning Laser Ophthalmoscope), and captures a (two-dimensional) fundus image of the fundus.

  The external storage device 52 is realized by, for example, an HDD (Hard Disk Drive) or the like, and stores various data. The external storage device 52 holds, for example, information relating to the eye to be examined (patient's name, age, sex, etc.) in association with captured image data, imaging parameters, image analysis parameters, and parameters set by the operator. To do.

  The input device 54 is realized by, for example, a mouse, a keyboard, a touch operation screen, and the like, and inputs various instructions from the operator. For example, the operator gives various instructions and settings to the image processing device 30, the tomographic image capturing device 20, and the fundus image capturing device 51 via the input device 54. The display device 53 is realized by, for example, a liquid crystal display or the like, and displays (presents) various kinds of information for the operator.

  The image processing device 30 is realized by, for example, a personal computer and processes various images. That is, the image processing apparatus 30 has a built-in computer. The computer includes main control means such as a CPU (Central Processing Unit), storage means such as ROM (Read Only Memory), RAM (Random Access Memory), and the like.

  Here, the image processing apparatus 30 includes an image acquisition unit 31, a storage unit 32, an image processing unit 33, an instruction unit 34, and a display control unit 35 as functional configurations. The configuration other than the storage unit 32 is realized, for example, when the CPU reads and executes a program stored in the ROM or the like.

  The image processing unit 33 includes a detection unit 41, a determination unit 43, a retinal layer analysis unit 44, and an alignment unit 47.

  The image acquisition unit 31 acquires a tomographic image captured by the tomographic image capturing device 20 and a fundus image captured by the fundus image capturing device 51, and stores them in the storage unit 32. The storage unit 32 is realized by, for example, a ROM or a RAM.

  The detection unit 41 detects a retinal layer (retinal layer) from the tomographic image stored in the storage unit 32.

  The retinal layer analysis unit 44 analyzes the retinal layer to be analyzed. The retinal layer analysis unit 44 includes an analysis unit 42, an analysis result creation unit 45, and a shape data creation unit 46. The retinal layer to be analyzed is determined (selected) based on an instruction from the operator via the input device 54, for example.

  The determination unit 43 determines whether or not to perform three-dimensional shape analysis processing of the retinal layer according to the imaging mode (imaging mode for myopic eye analysis, imaging mode for non-myopic eye analysis). The three-dimensional shape analysis refers to creating three-dimensional shape data and performing shape analysis of the retinal layer using the shape data.

  The analysis unit 42 performs analysis processing on the retinal layer to be analyzed based on the determination result of the determination unit 43. In the present embodiment, a case where the macular of the myopic eye is analyzed as a three-dimensional shape analysis process will be described. The analysis result creation unit 45 creates various data for presenting the analysis result (information indicating the state of the retinal layer). The shape data creation unit 46 aligns a plurality of tomographic images obtained by photographing, and creates three-dimensional shape data. That is, the three-dimensional shape data is created based on the layer information of the retinal layer.

  The alignment unit 47 aligns the analysis result with the fundus image, aligns the fundus images, and the like. The instruction unit 34 instructs information such as imaging parameters according to the imaging mode set in the tomographic imaging apparatus 20.

  The above is an example of the configuration of the image processing system 10. Note that the functional configuration provided in each of the above-described devices does not necessarily have to be realized as shown in the drawing, and it is sufficient that all or a part thereof is realized in any device in the system. For example, in FIG. 1, the external storage device 52, the display device 53, and the input device 54 are provided outside the image processing device 30, but these configurations may be provided inside the image processing device 30. . For example, the image processing apparatus and the tomographic imaging apparatus 20 may be integrally configured.

  Next, an example of the tomographic image capturing screen 60 displayed on the display device 53 shown in FIG. 1 will be described with reference to FIG. This screen is displayed when a tomographic image is captured.

  The tomographic image capturing screen 60 includes a tomographic image display area 61, a fundus image display area 62, an imaging mode setting combo box 63, and a capture button 64 for instructing imaging. Note that reference numeral 65 in the fundus image display area 62 is a mark indicating a photographing area, and is superimposed on the fundus image. M represents the macular region, D represents the optic nerve head, and V represents a blood vessel.

  In the combo box 63, for example, a setting is made for a shooting mode for myopic eye analysis (for the macula) or a shooting mode for non-myopic eye analysis (for the macula). That is, the combo box 63 has a shooting mode selection function. In this case, a shooting mode for myopic eye analysis is set.

  Here, a tomographic image of the fundus is displayed in the tomographic image display area 61. L1 indicates the inner limiting membrane (ILM), L2 indicates the boundary between the nerve fiber layer (NFL) and the ganglion cell layer (GCL), and L3 indicates the photoreceptor inner and outer segment junction (ISOS) . L4 represents the retinal pigment epithelial layer (RPE), and L5 represents the Bruch's membrane (BM). In the detection part 41 mentioned above, either of each boundary of L1-L5 is detected.

  Next, an example of the processing flow of the image processing apparatus 30 shown in FIG. 1 will be described with reference to FIGS. 3 (a) and 3 (b). First, an overall processing flow at the time of capturing a tomographic image will be described with reference to FIG.

[S101]
First, the image processing apparatus 30 acquires a subject identification number from the outside as information for identifying the eye to be examined. Then, based on the subject identification number, information about the subject eye held by the external storage device 52 is acquired and stored in the storage unit 32.

[S102]
In the image processing device 30, the image acquisition unit 31 acquires a fundus image from the fundus image capturing device 51 as a pre-scan image for confirming a shooting position at the time of shooting, and acquires a tomographic image from the tomographic image capturing device 20.

[S103]
The image processing device 30 sets the shooting mode. The shooting mode is set based on the operator's selection from the shooting mode setting combo box 63 described in FIG. Here, a case where shooting is performed in a shooting mode for myopic eye analysis will be described.

[S104]
The image processing apparatus 30 instructs the tomographic image capturing apparatus 20 in the instructing unit 34 with the capturing parameters corresponding to the capturing mode set from the combo box 63. Thereby, the tomographic imaging apparatus 20 sets the imaging parameters in accordance with the instruction in the parameter setting unit 23. Specifically, it instructs the setting of at least one of the position of the internal fixation lamp, the scanning range (scanning range), the scanning pattern (scanning pattern), and the coherence gate position.

  Here, parameter setting in the photographing mode for myopic eye analysis will be described. In the parameter setting of the position of the internal fixation lamp, the position of the internal fixation lamp 24 is set so that the center of the macula can be photographed. In the image processing apparatus 30, the drive control unit 22 controls the light emitting diode of the display unit 24 a according to the imaging parameter. In addition, as long as the imaging range is sufficiently wide, the apparatus may be controlled so that the center of the macula and the optic nerve head is the center of imaging. Such control is performed in order to photograph a region in which the macular portion appears in order to perform shape analysis of the retinal layer in the myopic eye.

  In the scan range parameter setting, for example, a range of 9 to 15 mm is set as the limit value of the imaging range of the apparatus. This numerical value is merely an example, and may be changed as appropriate according to the specifications of the apparatus. Note that the imaging range is preferably wider in order to be able to detect the location where the shape change has occurred without omission.

  In the scanning pattern parameter setting, for example, raster scanning or radial scanning is set so that the three-dimensional shape of the retinal layer can be photographed.

  In the parameter setting of the position of the coherence gate, the gate position is set so that photographing can be performed by the EDI method. In the highly myopic eye, the degree of curvature of the retinal layer becomes tight, and the retinal layer is photographed beyond the upper side of the tomographic image. In that case, since the retinal layer beyond the top of the tomographic image is reflected in the tomographic image, it is necessary to set such parameters in order to prevent this. In the case of using a deep SS-OCT as the tomographic imaging apparatus 20, a good tomographic image can be obtained even if the position of the retinal layer is moved away from the gate position. good.

[S105]
The image processing apparatus 30 instructs the tomographic imaging apparatus 20 to shoot the eye to be examined using the instruction unit 34. This instruction is performed, for example, when the operator presses the capture button 64 on the tomographic image capturing screen 60 via the input device 54. When this instruction is given, the tomographic imaging apparatus 20 controls the drive control unit 22 based on the imaging parameters set by the parameter setting unit 23. As a result, the galvanometer mirror 21 is operated to take a tomographic image.

  As described above, the galvanometer mirror 21 includes the horizontal X scanner and the vertical Y scanner. Therefore, by changing the orientations of these scanners, tomographic images can be taken along the horizontal direction (X) and the vertical direction (Y) in the apparatus coordinate system. By simultaneously changing the orientations of these scanners, it is possible to scan in a direction in which the horizontal direction and the vertical direction are combined, so that photographing along any direction on the fundus plane is possible. At this time, the image processing device 30 causes the display control unit 35 to display the captured tomographic image on the display device 53. Thereby, the operator can confirm the photographing result.

[S106]
In the image processing device 30, the image processing unit 33 detects / analyzes the retinal layer from the tomographic image stored in the storage unit 32. That is, the retinal layer detection / analysis process is performed on the tomographic image captured in the process of S105.

[S107]
The image processing device 30 determines whether or not the tomographic image capturing is to be terminated. This determination is made based on an instruction from the operator via the input device 54. That is, it is determined whether or not to finish tomographic image capture based on whether or not the operator has instructed termination.

  When the end of shooting is instructed, the image processing apparatus 30 ends this processing. On the other hand, when shooting is continued without ending the process, the image processing apparatus 30 performs the processes subsequent to S102 again.

  When the operator manually corrects the detection result of the retinal layer or the position of the fundus image and the map by the processing of S206 and S209, which will be described later, The imaging parameters changed accordingly are stored in the external storage device 52. At this time, a confirmation dialog as to whether or not to save the changed parameter may be displayed to inquire the operator whether or not to change the shooting parameter.

  Next, the retinal layer detection / analysis process indicated by S106 in FIG. 3A will be described with reference to FIG.

[S201]
When the detection / analysis process of the retinal layer is started, the image processing apparatus 30 detects the retinal layer from the tomographic image in the detection unit 41. This process will be specifically described using a tomographic image (display area 61) shown in FIG. In the case of a macular portion, the detection unit 41 first creates an image by applying the median filter and the Sobel filter to the tomographic image (hereinafter referred to as a median image and a Sobel image). Subsequently, the detection unit 41 creates a profile for each A scan from the created median image and Sobel image. The median image has a luminance value profile, and the Sobel image has a gradient profile. And the detection part 41 detects the peak in the profile produced from the Sobel image. Finally, the median image profiles corresponding to before and after the detected peak and between the peaks are referred to detect the boundary of each region of the retinal layer. That is, L1 (ILM), L2 (boundary between NFL and GCL), L3 (ISOS), L4 (RPE), L5 (BM), etc. are detected. In the present embodiment, the analysis target layer is described as RPE.

[S202]
In the image processing apparatus 30, the determination unit 43 determines whether or not to perform a three-dimensional shape analysis of the retinal layer. More specifically, when photographing is performed in the photographing mode for myopic eye analysis, it is determined that the three-dimensional shape analysis of the retinal layer is performed. In addition, when photographing is performed without using the myopic eye analysis mode (photographing mode for non-myopic eye analysis), it is determined that the three-dimensional shape analysis is not performed. In this case, analysis based on the detection result of the detection unit 41 is performed (analysis without using three-dimensional shape data). Even in the imaging mode for myopic eye analysis, based on the tomographic image, it is determined whether or not the macular portion is reflected in the tomographic image, and if it is not captured (for example, only the optic nerve head is captured). Alternatively, it may be determined that the (three-dimensional) shape analysis of the retinal layer is not performed.

  Here, in the present embodiment, the image processing system 10 in which the tomographic imaging apparatus 20 and the image processing apparatus 30 are integrated will be described as performing a series of processes from imaging to analysis. Not limited. That is, the image processing apparatus 30 is only required to perform shape analysis of the retinal layer when a tomographic image in which the macular portion is captured using a scanning pattern for acquiring a three-dimensional shape is input. There is no need for such an integrated system. Therefore, the shape analysis of the retinal layer can be performed on tomographic images taken by devices other than the tomographic image photographing device 20 based on information at the time of photographing. However, when shape analysis is not required, the shape analysis process may be omitted.

[S203]
The image processing apparatus 30 creates three-dimensional shape data in the shape data creation unit 46. The three-dimensional shape data is created in order to perform shape analysis based on the detection result of the retinal layer in the process of S201.

  Here, for example, if the scanning pattern at the time of photographing is a raster scan, a plurality of adjacent tomographic images are aligned. In the alignment of tomographic images, for example, an evaluation function representing the similarity between two tomographic images is defined in advance, and the tomographic image is deformed so that the value of this evaluation function is the best.

  As the evaluation function, for example, a method of evaluating with a pixel value (for example, a method of performing evaluation using a correlation coefficient) can be mentioned. Further, the image deformation process includes a process of performing translation and rotation using affine transformation. The shape data creation unit 46 creates three-dimensional shape data of a layer to be subjected to shape analysis after the alignment processing of a plurality of tomographic images is completed. The three-dimensional shape data may be created by preparing, for example, 512 × 512 × 500 voxel data and assigning a label to a location corresponding to the coordinate value of the layer data in which the retinal layer is detected.

  In addition, if the scanning pattern at the time of imaging is a radial scan, the shape data creation unit 46 similarly performs alignment of the tomographic images and then creates three-dimensional shape data. However, in this case, alignment in the depth direction (Z direction in the tomographic image (display region 61) in FIG. 2) is performed using only region information near the center of the adjacent tomographic image. This is because, in the case of a radial scan, even for adjacent tomographic images, the information at both ends of the tomographic image is sparse compared to the vicinity of the center of the tomographic image, and the shape change is large. Because it is good. As the alignment method, the method described above may be used. The shape data creation unit 46 creates three-dimensional shape data of a layer to be subjected to shape analysis after the alignment process is completed.

  In the case of a radial scan, for example, 512 × 512 × 500 voxel data is prepared, and first, layer data to be subjected to shape analysis of each tomographic image is uniformly rotated into a circle and developed. Thereafter, interpolation processing is performed between the shape data adjacent in the circumferential direction in the developed layer data. The shape data of the part not photographed is created by the interpolation process. As a method of interpolation processing, processing such as linear interpolation and nonlinear interpolation may be applied. Three-dimensional shape data may be created by assigning labels to locations corresponding to coordinate values obtained by interpolating between layer data in which the retinal layer is detected.

  Note that the numerical value of the voxel data shown here is merely an example, and may be changed as appropriate according to the number of A-scans at the time of shooting and the memory status of the apparatus to be executed. In the case of large voxel data, since the resolution is high, the shape data can be expressed accurately, but the execution speed is slow and a large amount of memory is consumed. On the other hand, in the case of small voxel data, the resolution is low, but the execution speed is high and the memory consumption is also small.

[S204]
In the image processing apparatus 30, the analysis unit 42 performs a three-dimensional shape analysis of the retinal layer. Here, as a method of shape analysis, a method for measuring the area and volume of the retinal layer will be described as an example.

  This process will be described with reference to FIG. FIG. 4 schematically shows three-dimensional shape data (RPE), a measurement surface (MS), an area (Area), and a volume (Volume).

  First, area measurement will be described. In the three-dimensional shape data of the RPE created in the process of S203, a flat (planar) measurement surface (MS) is prepared at the location of the layer data located deepest in the Z direction (optical axis direction). Then, the measurement surface (MS) is moved in a shallow direction (Z-axis origin direction) by a certain interval from there. When the measurement surface (MS) is moved in a shallow direction from the deep part of the layer, the measurement surface (MS) crosses the boundary line of the RPE.

  The area (Area) is obtained by measuring an internal planar region surrounded by the boundary line between the measurement surface (MS) and the RPE. More specifically, the area (Area) is obtained by measuring the area of the intersection region between the measurement surface (MS) and the boundary line of the RPE. Thus, the area (Area) is a cross-sectional area of the three-dimensional retinal layer shape data. When the cross-sectional area of the position of the reference portion is measured, the area is small if the retina is tightly curved, and the area is large if the retina is gently curved.

  Further, the volume (Volume) is measured by using the measurement surface (MS) used when measuring the area (Area), and measuring the entire internal region surrounded by the boundary line between the measurement surface (MS) and the RPE. Can be obtained. When measuring the lower volume along the Z direction from the position of the reference portion, the volume increases if the retina curve is tight, and the volume decreases if the retina curve is gentle. Here, the reference position may be, for example, the position of the Bruch film opening with the site as a reference. Alternatively, a certain height such as 100 μm or 500 μm from the deepest position of the RPE may be used as a reference. When measuring the area and volume, the number of voxels contained therein is counted and multiplied by the physical size per voxel.

[S205]
After the shape analysis, the image processing apparatus 30 creates an analysis result (for example, a map, a graph, and numerical information) in the analysis result creation unit 45 based on the three-dimensional shape analysis result.

  Here, a case where a contour map is created as a three-dimensional shape analysis result will be described. The contour map is used when displaying the result of measuring the area and volume.

  FIG. 5A shows an example of a contour map 71. Here, reference numeral 71 indicates the entire contour map, reference numeral 72 indicates contour lines drawn at regular intervals, and reference numeral 73 indicates a position located deepest in the Z direction of the three-dimensional retinal layer shape data. ing.

  When creating the contour map 71, a contour map lookup table is prepared, and color-coded according to the volume with reference to the table. Here, the contour map look-up table may be prepared according to the volume, for example. Thereby, on the map, changes in shape and volume can be grasped at a time.

More specifically, contour lines 72 are drawn at regular intervals with reference numeral 73 in FIG. 5A as the bottom, and the color of the map is set according to the volume. Therefore, it is possible to grasp how the volume increases when the height (depth) of the measurement surface is changed from the position located deepest in the Z direction. Specifically, when 1 mm 3 is set to blue, and 2 mm 3 is set to yellow, the height (depth) of the measurement surface from the position located deepest in the Z direction is 100 μm and blue. The operator can grasp the relationship between the shape and the volume depending on whether the color is 300 μm or blue. Therefore, the operator can grasp the value of the entire volume when the shape of the retinal layer to be measured is measured by checking the color of the outermost contour of the map.

  Further, the operator can grasp the value of the volume corresponding to the height (depth) by confirming the color near the internal contour line. Note that the look-up table used when setting the color of the contour map is not limited to the volume, and may be provided according to the area, and is the most in the Z direction of the retinal layer data from the measurement surface (MS). You may provide according to the height (depth) to the location 73 located in a deep part. Although not shown, numerical values may be displayed together on each contour line so that the height (depth) of the contour line can be understood. As an interval of the distance expressing the contour line, for example, an interval of 100 μm is set along the Z direction. The contour map may be in color or grayscale, but the color is more visible.

  In the contour map, the size of the outer shape changes according to the height (depth) from the position located deepest in the Z direction to the measurement surface (MS). FIG. 5B shows an example of a contour map 74 when the height (depth) of the measurement surface (MS) is changed.

  Next, as a three-dimensional shape analysis, a case where the curvature of the retinal layer is measured will be described using a tomographic image (display region 61) shown in FIG. Here, a case will be described in which the abscissa is the x coordinate and the ordinate is the z coordinate, and the curvature of the boundary line of the layer (RPE) to be analyzed is calculated. The curvature κ can be obtained by calculating “Equation 1” at each point of the boundary line. The sign of the curvature κ indicates whether it is convex upward or downward, and the magnitude of the numerical value indicates how the shape is bent. For this reason, assuming that the convexity on the top is + and the convexity on the bottom is-, in each tomographic image, if the sign of curvature is -region, + region, or -region, the shape is W.

[Formula 1]

  Although the case where the curvature is calculated with the boundary line of the tomographic image has been described here, the curvature calculation is not limited to this, and the three-dimensional curvature may be calculated from the three-dimensional shape data. In this case, after the shape analysis, the image processing apparatus 30 causes the analysis result creation unit 45 to create a curvature map based on the analysis result.

  FIG. 5C shows an example of the curvature map. In this case, the color of the portion where the curvature is tight is expressed darkly, and the color of the portion where the curvature is smooth is expressed lightly. That is, the color density is changed according to the curvature. The color set in the curvature map may be changed between positive and negative with respect to the curvature value 0. Thus, the operator can grasp whether the retina shape is smooth, whether it is convex upward or convex by viewing the map.

[S206]
In the display processing unit 35, the image processing apparatus 30 includes a tomographic image, a detection result of the layer (RPE) detected by the detection unit 41, and results of various shape analyzes (maps, graphs) created by the analysis result creation unit 45. , Numerical information) is displayed on the display device 53.

  FIG. 6 is a diagram showing an example of a tomographic image observation screen 80 displayed on the display device 53 shown in FIG. This screen is displayed after the analysis of the tomographic image is completed (that is, displayed by the process of S206).

  The tomographic image observation screen 80 includes a tomographic image display unit 91 including a tomographic image display region 81 and a fundus image display unit 94 including a fundus image display region 82. The tomographic image observation screen 80 is also provided with a first analysis result display unit 96 including a first analysis result 84 and a second analysis result display unit 98 including second analysis results 85 and 86.

  First, details of the tomographic image display unit 91 including the tomographic image display area 81 will be described. In the tomographic image display area 81, the segmentation results (L1 to L5) obtained by detecting each layer of the retinal layer and the measurement surface (MS) are displayed superimposed on the captured tomographic image. In the display area 81 of the tomographic image, the segmentation result of the retinal layer to be analyzed (in this embodiment, RPE (L4)) is highlighted.

  In the tomographic image display area 81, a hatched area 81a surrounded by the measurement surface (MS) and the analysis target retinal layer (RPE (L4)) is an area and volume measurement target area. At this time, in the hatched area 81a, a color corresponding to the volume measurement result is displayed with a predetermined transparency α. The same color as the look-up table for the contour map may be used as the color to be set. The transparency α is, for example, 0.5.

  The combo box 92 is provided for the operator to select whether to display the tomographic image at an OCT ratio or a 1: 1 ratio. Here, the OCT ratio is a ratio expressed by the resolution in the horizontal direction (X direction) and the resolution in the vertical direction (Y direction) obtained from the number of A scans at the time of imaging. The 1: 1 ratio is a ratio of the physical size per pixel in the horizontal direction and the physical size per pixel in the vertical direction, which is obtained by how many A scans are taken in the range of mm. That is.

  The combo box 93 is provided to switch between two-dimensional display (2D) / 3-dimensional display (3D) when displaying a tomographic image. Here, in the case of 2D display, one slice of the tomographic image is displayed, and in the case of 3D display, the three-dimensional shape of the retinal layer created from the boundary line data of the retinal layer is displayed.

  Specifically, when 3D display is selected in the combo box 93, the tomographic images shown in FIGS. 7A to 7C are displayed in the tomographic image display area 81.

  FIG. 7A shows a mode in which RPE is displayed in 3D with an OCT ratio. In this case, the measurement surface (MS) is also displayed in 3D at the same time.

  Here, below the tomographic image display area 81, check boxes 101 to 104 corresponding to each layer of the retina are displayed. Specifically, check boxes corresponding to ILM, PRE, BM, and MS are displayed, and the operator can instruct switching between display / non-display of each layer by using these check boxes.

  When the measurement surface (MS) is expressed by a surface, the transparency α is larger than 0 and smaller than 1. This is because if the shape of the retinal layer and the measurement surface are overlapped with the transparency set to 1, the state becomes like a lid, and the three-dimensional shape of the retinal layer cannot be seen from above. Alternatively, the measurement surface (MS) may be expressed as a grid instead of a surface. In the case of a lattice shape, the transparency α of the measurement surface (MS) may be 1. For the color of the measurement surface (MS), a color corresponding to the measurement value (area or volume) at a position where the measurement surface (MS) is located may be selected with reference to a lookup table of the contour map.

  Here, the operator can move the position of the measurement surface (MS) via the input device 54. Therefore, when the position of the measurement surface (MS) is changed, the image processing apparatus 30 changes the contour map shape in conjunction with the change, as described in FIGS. 5 (a) and 5 (b). Let

  A text box 105 is an item for designating a numerical value. The operator inputs a numerical value indicating the height (depth) of the measurement surface (MS) from the position located deepest in the Z direction into the text box 105 via the input device 54. For example, when a numerical value such as 100 μm or 300 μm is input, the measurement surface (MS) moves to that location, and the contour map changes accordingly. Thus, the operator can simultaneously grasp the position in the three-dimensional shape and the contour map at that time, and can also grasp the volume value and the area value at that time.

As another example, a volume value may be input to the text box 105. In this case, when a numerical value such as 1 mm 3 or 2 mm 3 is input, the operator can simultaneously grasp the position of the measurement surface (MS) in the three-dimensional shape corresponding to the volume and the contour map at that time. . Furthermore, the operator can also grasp the height (depth) of the measurement surface (MS) from the position located deepest in the Z direction at that time.

  Subsequently, FIG. 7B shows a display mode when the measurement surface (MS) is not displayed. Other display items are the same as those in FIG. In the case of FIG. 7B, the check box 102 is selected and only PRE is displayed. Thus, only the three-dimensional shape of the fundus can be displayed.

  Here, in FIG. 7B, 3D display of RPE is performed with an OCT ratio, whereas FIG. 7C shows a mode in which 3D display of RPE is performed with a 1: 1 ratio. Show. That is, the 1: 1 ratio is selected in the combo box 92.

  In this embodiment, since RPE is described as an analysis target, when 2D / 3D display is switched using the combo box 93, the RPE shape is displayed in 2D / 3D, but the present invention is not limited to this. For example, when the analysis target is a Bruch film (BM), the Bruch film (BM) shape is displayed in 2D / 3D.

  Here, in the display area 81 of the tomographic image, a display schematically showing which position the measurement surface is measuring may be performed. The display mode in this case will be described with reference to FIGS. 8 (a) to 8 (d).

  FIG. 8A shows an aspect in which an object 110 indicating which position on the measurement plane is measured in the tomographic image being displayed is displayed superimposed on the tomographic image. Reference sign MS ′ represents a measurement surface (schematic measurement surface) on the object 110. The three-dimensional shape of the retinal layer is rotated up and down and left and right according to instructions from the operator via the input device 54. Therefore, a positional relationship index is presented by the object 110 and the schematic measurement surface MS 'so that the operator can grasp the positional relationship between the measurement surface (MS) and the retinal layer.

  When the operator changes the positional relationship between the object 110 and the schematic measurement surface MS 'via the input device 54, the display of the three-dimensional shape of the retinal layer is also changed accordingly. In this case, since the region of the retinal layer to be analyzed is also changed, the first analysis result 84 and the second analysis results 85 and 86 are also changed in conjunction with each other.

  Here, several display modes of the object 110 will be described as examples. For example, as shown in FIGS. 8B and 8C, a tomographic image corresponding to each cross-sectional position may be displayed. In this case, the object 110 displays a tomographic image at a vertical position and a horizontal position that cross the center position when considered in three dimensions. Alternatively, as shown in FIG. 8D, English abbreviations such as S and I indicating upper and lower (inferior) may be displayed.

  Next, details of the fundus image display unit 94 including the fundus image display area 82 shown in FIG. 6 will be described. In the fundus image display area 82, the photographing position and the scanning pattern mark 83 are superimposed on the fundus image. Further, the fundus image display unit 94 is provided with a combo box 95 for switching the display format of the fundus image. In this case, an SLO image is displayed as a fundus image.

  Here, a case where the display format of the fundus image is switched from the combo box 95 will be described with reference to FIGS. 9A and 9B. Here, as the display format of the fundus image, “SLO image + map” is displayed simultaneously, and “fundus photo (second fundus image) + SLO image (first fundus image) + map” is displayed simultaneously. Will be described as an example. Note that the SLO image (first fundus image) may be a two-dimensional fundus image captured simultaneously with the tomographic image. For example, the SLO image (first fundus image) is an integrated image generated by integrating the tomographic images in the depth direction. There may be. In addition, the fundus photograph (second fundus image) may be a two-dimensional fundus image captured at a timing different from that of the tomographic image, and examples thereof include a contrast examination image.

  FIG. 9A shows a display mode when “SLO image + map” is selected from the combo box 95. Reference numeral 201 denotes an SLO image, and reference numeral 200 denotes a map. The alignment between the SLO image 201 and the map 200 is performed by the alignment unit 47 described with reference to FIG. These alignments are performed by setting the position and size of the map based on the position of the fixation lamp at the time of photographing and the scanning range.

  When the result of superimposing the map 200 on the SLO image 201 is displayed as a fundus image, the transparency α of the SLO image 201 is displayed as 1, and the transparency α of the map 200 is smaller than 1, for example, displayed as 0.5. To do. These parameters of transparency α are parameters that are set when the operator selects the target data for the first time. These parameters can be appropriately changed by the operator via the input device 54. The parameter changed by the operator is stored in the external storage device 52, for example. When the same target data is opened after the next time, display is performed according to the parameters set by the previous operator.

  Next, FIG. 9B shows a display mode when “fundus photo + SLO image + map” is selected from the combo box 95. Reference numeral 202 denotes a fundus photograph (second fundus image).

  In this case, the SLO image 201 is used to display the map 200 superimposed on the fundus photograph 202 (that is, to display the map 200 superimposed on the second fundus image). The reason is that the fundus photo 202 is taken at a timing different from that of the tomographic image, and the photographing position and photographing range cannot be understood from the map 200 alone. Therefore, using the SLO image 201, the fundus photo 202 and the map 200 can be aligned. The alignment between the fundus photograph 202 and the SLO image 201 is performed by the alignment unit 47 described with reference to FIG.

  The alignment method may be performed using, for example, blood vessel characteristics. As a blood vessel detection method, since a blood vessel has a thin linear structure, first, the blood vessel is extracted using a filter that emphasizes the linear structure. As a filter that emphasizes the linear structure, a filter that calculates the difference between the average value of the image density value in the structural element and the average value in the local region surrounding the structural element when the line segment is the structural element. Use it. Of course, the present invention is not limited to this, and a differential filter such as a Sobel filter may be used. Further, the eigenvalue of the Hessian matrix may be calculated for each pixel of the density value image, and a line-shaped region may be extracted from a combination of two eigenvalues obtained as a result. Furthermore, a top hat calculation using a line segment as a structural element may be used. The alignment unit 47 aligns the fundus photo 202 and the SLO image 201 using the blood vessel position information detected by these methods.

  Since the SLO image 201 and the map 200 can be aligned by the above-described method, as a result, the fundus photo 202 and the map 200 can also be aligned. When the result of superimposing the map 200 on the fundus photograph 202 is displayed in the display area 82 of the fundus image display unit 94, the transparency α of the fundus photograph 202 is displayed as 1. Further, the transparency α of the SLO image 201 and the transparency α of the map 200 are made smaller than 1, for example, 0.5. Of course, the value of the transparency α of the SLO image 201 and the map 200 need not be the same. For example, the value of the transparency α of the SLO image 201 may be zero.

  When the eye to be examined is a diseased eye, the alignment process by the alignment unit 47 may fail. In determining the alignment failure, when calculating the similarity between images, the maximum similarity does not exceed the threshold. Alternatively, even if the threshold value is exceeded, it can be determined that the registration process has failed when the alignment process ends at an anatomically unnatural place. In this case, the SLO image 201 and the map 200 may be displayed with the initial parameter position (for example, the center of the image) and the initial transparency set in advance. Then, a message indicating that the alignment process has failed is displayed to prompt the operator to correct the position via the input device 54.

  Here, when the operator performs position correction or parameter change of the transparency α, when the operator moves, enlarges / reduces, or rotates the SLO image 201, the map 200 on the SLO image 201 is simultaneously displayed. , Move, enlarge / reduce, rotate. That is, the SLO image 201 and the map 200 operate as one and the same image. However, regarding the transparency α, the SLO image 201 and the map 200 are set independently. The parameters changed by the operator via the input device 54 are stored in the external storage device 52, and are displayed according to the set parameters from the next time.

  In this manner, in the fundus image display area 82 of the fundus image display unit 94, in addition to the two-dimensional fundus image, a display in which a map or the like is superimposed on the fundus image is performed. 9A and 9B illustrate the case where the contour map is superimposed and displayed in association with the corresponding position on the fundus image, the present invention is not limited to this. That is, a curvature map or a layer thickness map may be displayed.

  Further, when changing the analysis target layer, the operator selects the segmentation results (L1 to L5) from the tomographic image of the display area 61 shown in FIG. Just do it. When the analysis target layer is switched, the image processing apparatus 30 causes the display control unit 35 to return the segmentation result layer that has been highlighted so far to the normal display and highlight the new analysis target layer. Thereby, the analysis result of an arbitrary layer can be displayed.

  Next, details of the first analysis result display unit 96 including the first analysis result 84 shown in FIG. 6 will be described.

  In the first analysis result 84, the shape analysis map created by the analysis result creation unit 45 is displayed. In the combo box 97, the map type of the first analysis result 84 can be selected. In this case, the shape analysis map shown as the first analysis result 84 is a contour map.

  The type of shape analysis map shown as the first analysis result 84 and the type of shape analysis map superimposed and displayed on the fundus image described in FIGS. 9A and 9B are the combo box 97. It can be changed in conjunction by specifying the type from. Furthermore, the display of the second analysis result display unit 98 described below is also changed in conjunction.

  Here, an example of the tomographic image observation screen 80 when the curvature result is displayed as the analysis result in FIG. 10 will be described.

  When the display of the analysis result is switched from the analysis result of the area and volume to the curvature analysis result, the tomographic image display unit 91, the fundus image display unit 94, the first analysis result display unit 96, and the second analysis result display unit 98 are displayed. The result displayed on is the content shown in FIG.

  Specifically, in the tomographic image display area 81, segmented results (L1 to L5) obtained by detecting each layer of the retinal layer are superimposed on the captured tomographic image. Further, a curvature map is displayed as the first analysis result 84, and a curvature graph is displayed as the second analysis result 88. In the fundus image display area 82, an image in which an SLO image (first fundus image) 201, a fundus photograph (second fundus image) 202, and a curvature map 203 are superimposed and displayed is displayed.

  Next, details of the second analysis result display unit 98 including the second analysis results 85 and 86 shown in FIG. 6 will be described.

  In the second analysis result 85, the shape analysis graph created by the analysis result creation unit 45 is displayed. In this case, the graph which measured the area and the volume is shown, the horizontal axis shows the height (depth), and the vertical axis shows the volume. A solid line denoted by reference numeral 87 indicates a volume.

  In the second analysis result 86, the shape analysis result is displayed as a table. The table displays the area and volume when the height of a certain reference value (for example, 100 μm, 500 μm, etc.) is displayed, and the height (position of the Bruch film opening) when a certain part is used as a reference The corresponding area and volume are displayed.

  Here, the case where the results of the area and the volume are displayed in one graph (second analysis result 85) will be described with reference to FIG. In this case, the horizontal axis indicates the height (depth), the vertical axis on the left side of the graph indicates the volume, and the vertical axis on the right side of the graph indicates the area. A broken line 89 is a graph showing the area, and a solid line 87 is a graph showing the volume.

[S207]
In the image processing apparatus 30, the analysis unit 42 performs shape analysis based on the detection result of the retinal layer. In this analysis processing, analysis using the detection result of the retinal layer is performed without creating three-dimensional shape data or the like. For example, analysis of the layer thickness is performed.

[S208]
In the image processing apparatus 30, the analysis result creation unit 45 creates an analysis result (for example, a map, a graph, or numerical information) based on the analysis result.

[S209]
The image processing apparatus 30 uses the tomographic image, the detection result of the layer (RPE, ILM, etc.) detected by the detection unit 41, and the analysis result (map, graph, numerical information) created by the analysis result creation unit 45. It is displayed on the display device 53.

  FIG. 12 is a diagram illustrating an example of the tomographic image observation screen 80 displayed on the display device 53 by the process of S209.

  In this case, a layer thickness map is shown as the first analysis result 302, and a layer thickness graph is shown as the second analysis result 301. That is, as the first analysis result 302 and the second analysis result 301, analysis results using the detection result of the retinal layer are displayed.

  Also in this case, the parameter changed by the operator via the input device 54 is stored in the external storage device 52 as in the process of S206, and is displayed according to the set parameter from the next time.

  As described above, according to the first embodiment, a plurality of imaging modes including an imaging mode for myopic eye analysis can be provided, and the analysis processing can be switched and executed in accordance with the imaging mode at the time of imaging a tomographic image.

  More specifically, at least a shooting mode for myopic eye analysis and a shooting mode for non-myopic eye analysis are provided as the plurality of shooting modes. In the imaging mode for myopic eye analysis, a tomographic image suitable for performing a three-dimensional shape analysis (analysis of a macular portion in a myopic eye) can be performed.

  Then, for the tomographic image captured in the imaging mode for myopic eye analysis, three-dimensional shape data is created, and three-dimensional shape analysis is executed based on the shape data. For tomographic images taken in other imaging modes, analysis processing based on the detection result of the retinal layer is executed without creating three-dimensional shape data.

(Embodiment 2)
Next, Embodiment 2 will be described. Embodiment 2 demonstrates the case where 2D display and 3D display of a tomographic image are displayed simultaneously. More specifically, in the second embodiment, a case where a tomographic image, three-dimensional shape data, and an analysis result are displayed side by side will be described. In the second embodiment, a tomographic image taken by radial scanning will be described as an example of a tomographic image.

  An example of the tomographic image observation screen 400 according to the second embodiment will be described with reference to FIG.

  The tomographic image observation screen 400 includes a first tomographic image display unit 410 including a two-dimensional tomographic image display region 411 and a second tomographic image display unit 430 including a three-dimensional tomographic image display region 431. Provided. Furthermore, the tomographic image observation screen 400 is also provided with a first analysis result display unit 440 including the first analysis result 442 and a second analysis result display unit 420 including the second analysis results 421 and 422.

  Here, the first analysis result display unit 440 and the second analysis result display unit 420 are the same as those in FIGS. 6 and 9A described in the first embodiment, and thus the description thereof is omitted. . The second tomographic image display unit 430 is also the same as that in FIGS. 7A to 7C describing the first embodiment, and a description thereof will be omitted. Here, the first tomographic image display unit 410 will be described mainly.

  The first tomographic image display unit 410 displays a two-dimensional tomographic image display area 411, a slider bar 412 for changing the viewpoint position (slice position) of the tomographic image, and the slice number of the tomographic image. An area 413 is provided.

  Here, the relationship between the viewpoint direction 503 in a three-dimensional shape and the tomographic image (display region 411) shown in FIG. 13 will be described with reference to FIG. Reference numeral 500 indicates an outline of the fundus when the three-dimensional shape of the tomographic image is viewed from the top in the deep direction (Z direction), and a radial straight line indicated by reference numeral 501 indicates the imaging slice position of the tomographic image. A broken line indicated by reference numeral 502 indicates a slice position corresponding to the tomographic image (display area 411) being displayed in the imaging slice position 501 and is perpendicular to the viewpoint direction 503. In other words, the tomographic image at the position indicated by the broken line 502 becomes a tomographic image displayed in the display area 411 of the tomographic image.

  Next, a case where the operator operates the tomographic image observation screen 80 described with reference to FIG. 13 via the input device 54 will be described.

  Assume that the operator moves the position of the slider bar 412 from the center to the end via the input device 54. Then, in conjunction with the operation, the image processing apparatus 30 changes the viewpoint position of the three-dimensional tomographic image (three-dimensional shape data) being displayed in the display area 431. In addition, the slice position of the two-dimensional tomographic image being displayed in the display area 411 is changed to the viewpoint position corresponding to the tomographic image specified by the slider bar 412.

  When the slider bar 412 is operated, the position of the bar is not continuously changed, but the position is continuously changed. Therefore, the position of the three-dimensional shape data of the tomographic image being displayed also changes continuously. Specifically, the image processing apparatus 30 displays the three-dimensional shape data of the tomographic image being displayed so as to rotate with respect to the center in the vertical direction.

  FIG. 15 shows an example of a screen display of a two-dimensional tomographic image in the display area 411 and a three-dimensional tomographic image (three-dimensional shape data) in the display area 431 when the position of the slider bar 412 is moved to the end. Show. In this case, the relationship between the viewpoint direction 507 in the three-dimensional shape and the two-dimensional tomographic image (display region 411) is as shown in FIG.

  When the position of the slider bar 412 is manipulated, the image processing apparatus 30 changes the slice position of the two-dimensional tomographic image being displayed in the display area 411 and the three-dimensional tomographic image (3 corresponding to the slice position). The viewpoint position of the (dimensional shape data) is changed. In addition, in accordance with the operation of the slider bar 412 for changing the slice position of the two-dimensional tomographic image, not only the viewpoint position of the three-dimensional shape data is changed, but also the reverse is possible. That is, when the operator changes the viewpoint position of the three-dimensional shape data via the input device 54, the slice position of the two-dimensional tomographic image and the position of the slider bar 412 are changed correspondingly. Anyway.

  As described above, according to the second embodiment, a two-dimensional tomographic image and a three-dimensional tomographic image are displayed at the same time, and their display modes can be changed in conjunction with each other according to an operation from the operator. it can.

  The above is an example of a typical embodiment of the present invention, but the present invention is not limited to the embodiment described above and shown in the drawings, and can be appropriately modified and implemented within the scope not changing the gist thereof. .

  For example, in some of the screens described in the first and second embodiments, check boxes, combo boxes, and the like are arranged. However, radio buttons, list boxes, buttons, and the like may be changed as appropriate according to applications. good. For example, the configuration described as a combo box in the above description may be realized as a list box.

(Other embodiments)
The present invention is also realized by executing the following processing. That is, software (program) that realizes the functions of the above-described embodiments is supplied to a system or apparatus via a network or various storage media, and a computer (or CPU, MPU, etc.) of the system or apparatus reads the program. It is a process to be executed.

Claims (10)

  1. Obtaining means for obtaining a tomographic image of the eye to be examined;
    An image processing system comprising: an analysis unit configured to perform analysis for obtaining information indicating a degree of curvature of the retina from a tomographic image of the eye according to an imaging mode when imaging the eye. .
  2. The analysis means includes
    The image processing system according to claim 1, wherein information representing the degree of curvature is acquired from three-dimensional shape data generated based on predetermined layer information of the retina.
  3. A selection means for selecting a predetermined layer from the retinal layer;
    The analysis means includes
    The image processing system according to claim 1, wherein three-dimensional shape data of the selected layer is generated.
  4. A photographing mode selection means for selecting any one of a plurality of photographing modes when photographing the eye to be examined;
    According to the shooting mode selected by the shooting mode selection means, at least one of the position of the fixation lamp, the scanning range of the irradiation light, the scanning pattern of the irradiation light, and the shooting position along the optical axis direction of the irradiation light It changes. The image processing system of any one of Claim 1 to 3 characterized by the above-mentioned.
  5. The acquisition means is OCT,
    The image processing system according to claim 4, wherein when the imaging mode for the myopia analysis is selected by the imaging mode selection unit, imaging is performed so that a macular portion is included in the tomographic image.
  6. The analysis means includes
    The image processing system according to claim 4 or 5, wherein a three-dimensional shape analysis is performed when a photographing mode for myopic eye analysis is selected by the photographing mode selection means.
  7. The analysis means includes
    When a photographing mode for myopic eye analysis is selected by the photographing mode selection means, it is determined whether or not a macular portion is photographed in the tomographic image, and if the macular portion is not photographed in the tomographic image, The image processing system according to claim 4, wherein three-dimensional shape analysis is not performed.
  8. The analysis means includes
    6. It is determined whether or not a macular portion is photographed in the tomographic image, and if the macular portion is not photographed in the tomographic image, three-dimensional shape analysis is not performed. The image processing system according to any one of the above.
  9. An image processing system processing method comprising:
    An obtaining unit obtaining a tomographic image of the eye to be examined; and
    Analyzing means for obtaining information representing a degree of curvature of the retina from a tomographic image of the eye to be examined according to a photographing mode when photographing the eye to be examined. Method.
  10.   The program for making a computer perform the process by the image processing system of any one of Claim 1 to 8.
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