JP5970833B2 - Ophthalmic analysis apparatus and program - Google Patents

Ophthalmic analysis apparatus and program Download PDF

Info

Publication number
JP5970833B2
JP5970833B2 JP2012019306A JP2012019306A JP5970833B2 JP 5970833 B2 JP5970833 B2 JP 5970833B2 JP 2012019306 A JP2012019306 A JP 2012019306A JP 2012019306 A JP2012019306 A JP 2012019306A JP 5970833 B2 JP5970833 B2 JP 5970833B2
Authority
JP
Japan
Prior art keywords
image
front image
pointer
position
eye
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Active
Application number
JP2012019306A
Other languages
Japanese (ja)
Other versions
JP2013154119A (en
JP2013154119A5 (en
Inventor
徹哉 加納
徹哉 加納
倫全 佐竹
倫全 佐竹
Original Assignee
株式会社ニデック
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Family has litigation
Application filed by 株式会社ニデック filed Critical 株式会社ニデック
Priority to JP2012019306A priority Critical patent/JP5970833B2/en
Publication of JP2013154119A publication Critical patent/JP2013154119A/en
Publication of JP2013154119A5 publication Critical patent/JP2013154119A5/ja
Application granted granted Critical
Publication of JP5970833B2 publication Critical patent/JP5970833B2/en
First worldwide family litigation filed litigation Critical https://patents.darts-ip.com/?family=49049908&utm_source=google_patent&utm_medium=platform_link&utm_campaign=public_patent_search&patent=JP5970833(B2) "Global patent litigation dataset” by Darts-ip is licensed under a Creative Commons Attribution 4.0 International License.
Application status is Active legal-status Critical
Anticipated expiration legal-status Critical

Links

Images

Description

  The present invention relates to an ophthalmic analysis apparatus and program for analyzing an eye to be examined.

  Conventionally, an eye is photographed by an ophthalmic photographing device (ophthalmic photographing apparatus) such as an optical coherence tomography (OCT), a fundus camera, a laser scanning ophthalmoscope (SLO), etc. Yes. Then, a predetermined area is detected from the photographed photographed image, an analysis process is performed, and an analysis result is acquired. There are two methods for detecting a predetermined area: a method of automatically detecting an edge from a photographed image and a method of manual editing (manual detection) by an examiner. The examiner looks at the analysis result thus obtained to determine visual impairment (abnormality) of the eye to be examined.

  For example, glaucoma is one of visual impairments. As a test for glaucoma, it is said that observation of the optic nerve head (hereinafter simply referred to as the “nipple”) by fundus images is important. In such a nipple measurement, for example, the diameter of the outer edge of the nipple recess called the cup and the diameter (or radius) of the nipple outer edge called the disk are detected (calculated) from the fundus front image by the fundus camera. A technique is known in which the C / D ratio, which is the ratio, and the area ratio between the cup and the disk are obtained, and the state of the eye to be examined is known based on the obtained C / D ratio (or area ratio). (For example, refer to Patent Document 1) The detection of a cup or a disk is performed by automatic detection by edge detection or the like from a captured image or manual editing by an examiner.

JP 2006-280411 A

  Conventionally, it has been difficult to determine the position in image analysis. For example, regarding the analysis of the optic nerve head, it is difficult to determine the position of a region where the boundary of the region such as a cup or a disk is difficult to discriminate.

  In view of the above-described problems of the prior art, an object of the present invention is to provide an ophthalmologic analyzer that can satisfactorily analyze the eye to be examined.

  In order to solve the above problems, the present invention is characterized by having the following configuration.

(1) An ophthalmic analysis apparatus according to the first aspect of the present disclosure is provided.
A front image acquisition means for acquiring a front image of the eye to be examined;
A tomographic image acquisition means for obtaining a tomographic image of the eye to be examined by using interference between the measurement light reflected from the eye to be examined and the reference light;
Display means for displaying an image acquired by the front image acquisition means and the tomographic image acquisition means;
Operation input means;
A pointer that is two-dimensionally movable on the front image based on an operation signal input from the operation input unit is displayed on the display unit, and a predetermined part for calculating a predetermined parameter related to analysis of the eye to be examined Calculation control means for displaying on the display means tomographic images orthogonal to each other with reference to the position of the pointer on the front image, in order to obtain position information;
It is characterized by providing.
(2) An ophthalmic analysis apparatus according to the second aspect of the present disclosure is provided.
A front image acquisition means for acquiring a front image of the eye to be examined;
A tomographic image acquisition means for obtaining a tomographic image of the eye to be examined by using interference between the measurement light reflected from the eye to be examined and the reference light;
Display means for displaying an image acquired by the front image acquisition means and the tomographic image acquisition means;
Operation input means;
A pointer that is two-dimensionally movable on the front image is displayed on the display unit based on an operation signal input from the operation input unit, and is orthogonal to each other with reference to the position of the pointer on the front image. Calculation control means for displaying a tomographic image to be displayed on the display means,
The arithmetic and control unit displays tomographic images orthogonal to each other on the basis of the position of the moved pointer in synchronization with the movement of the pointer on the front image.
(3) An ophthalmic analysis program according to the third aspect of the present disclosure is provided.
Displaying the images acquired by the front image acquiring means and the tomographic image acquiring means on the display means;
A position on a predetermined part for displaying a pointer that can be moved two-dimensionally on a front image on the front image based on an operation signal input from the operation input unit and calculating a predetermined parameter relating to the analysis of the eye to be examined Displaying the tomographic images orthogonal to each other with reference to the position of the pointer on the front image on the display means to obtain information;
A step of calculating a predetermined parameter related to the analysis of the eye to be examined using the acquired position information regarding the predetermined site;
Is executed by a computer.

  According to the present invention, it is possible to satisfactorily analyze the eye to be examined.

  DESCRIPTION OF EMBODIMENTS An embodiment for carrying out an apparatus according to the present invention will be described with reference to the drawings. 1-6 is a figure for demonstrating the apparatus and program which concern on this embodiment.

  This apparatus displays the images acquired by the front image acquisition device and the tomographic image acquisition device, displays the pointer 21 movable on the front image 20 based on the operation signal input from the operation input unit, and In order to acquire position information regarding a predetermined part for calculating a predetermined parameter relating to the analysis of the optometry, tomographic images 30 and 40 corresponding to the position of the pointer 21 on the front image are displayed.

  Examples of the predetermined parameters relating to the analysis of the eye to be examined include predetermined parameters relating to the fundus analysis ((C (cup) / D (disc) ratio, R / D ratio relating to the nipple), macular size, lesion length, Area, volume, and area or volume of a thick or thin region). Further, predetermined parameters (pupil diameter, corneal diameter) related to the anterior segment analysis can be considered.

  The apparatus preferably displays position information 31, 41 corresponding to the position of the pointer on the front image on the tomographic image.

  As the front image acquisition device, an infrared front image or a visible front image is acquired. Examples thereof include a fundus camera, an optical scanning laser ophthalmoscope, and optical coherence tomography. A typical tomographic image acquisition device is optical coherence tomography.

  The apparatus advantageously displays tomographic images 30 and 40 whose cut planes are orthogonal to each other with reference to the position of the pointer 21 on the front image 20.

  The apparatus advantageously displays a tomographic image corresponding to the position of the moved pointer 21 in synchronization with the movement of the pointer 21 on the front image.

  In addition, the apparatus displays an image acquired by the front image acquisition device and the tomographic image acquisition device, and displays a pointer 21 movable on the front image 20 based on an operation signal input from the operation input unit. Then, a tomographic image corresponding to the position of the pointer 21 on the front image 20 is displayed. The apparatus displays tomographic images 30 and 40 corresponding to the position of the moved pointer 21 in synchronization with the movement of the pointer 21 on the front image 20.

<Overview>
An ophthalmologic photographing apparatus (optical coherence tomography device) 10 according to the present embodiment includes an interference optical system 100, a front image observation optical system 200, and a display control unit (control unit) 70.

  The interference optical system (OCT optical system) 100 includes a light source 102, an optical scanner 108, and a detector 120, and is used to obtain a three-dimensional image of the fundus region of the eye E. For example, a three-dimensional image including the optic nerve head of the eye E is acquired. The optical scanner 108 is used to scan the light emitted from the measurement light source on the fundus Ef of the eye to be examined. The detector 120 is used to detect an interference state between the measurement light emitted from the measurement light source 102 and the reference light. The optical coherence tomography device 10 is further provided with operation input means (operation unit) 74. The operation unit 74 is operated by an examiner.

  The front image observation optical system 200 is used to acquire a front image of the fundus of the eye to be examined. Examples of the front image observation optical system 200 include an SLO and a fundus camera. Further, the interference optical system 100 may be used as the front image observation optical system 200. In this case, based on the three-dimensional image acquired by the interference optical system 100, the front fundus image of the eye to be examined is acquired. Further, a tomographic image at a cutting position (cut plane) corresponding to the line is obtained by a vertical line, a horizontal line, a circle line, or the like. Examples of scanning patterns for obtaining a three-dimensional image include raster scans, radial scans, concentric circle scans (a plurality of circle scans having different sizes), and the like.

  The control unit 70 displays the front image 20, the first tomographic image 30, and the second tomographic image 40 on the monitor 75 on the monitor 75. The control unit 70 displays the pointer 21 that can be moved on the monitor 75 on the monitor 75 based on the operation signal from the operation input unit 74. The control unit 70 displays a pointer (for example, a cross mark, a dot mark, a pen mark, etc.) 21 superimposed on the front image 20.

  The pointer 21 indicates the intersection of the cutting positions in the vertical direction and the horizontal direction in the front image 20. The control unit 70 extracts the first tomographic image 30 corresponding to the longitudinal cutting position of the pointer 21 from the three-dimensional image data acquired by the interference optical system 100. The control unit 70 extracts the second tomographic image 40 corresponding to the horizontal cutting position of the pointer 21 from the three-dimensional image data acquired by the interference optical system 100. The control unit 70 simultaneously displays the extracted first tomographic image 30 and second tomographic image 40 on the monitor 75 together with the front image 20 acquired by the front image observation optical system 200.

  The control unit 70 superimposes and displays a horizontal line 31 (for example, a line display or an arrow display) 31 corresponding to the horizontal cutting position of the pointer 21 on the first tomographic image 30. In addition, the control unit 70 displays a horizontal line 41 (for example, a line display or an arrow display) corresponding to the horizontal cutting position of the pointer 21 so as to be superimposed on the second tomographic image 40.

  When the front image observation optical system 200 is an SLO or a fundus camera, the control unit 70 and the fundus front image acquired by the front image observation optical system 200 and the fundus front image acquired by the interference optical system 100 (for example, Alignment (matching) with an OCT front image (for example, an integrated image) based on three-dimensional image data. Thereby, the first tomographic image 30 and the second tomographic image 40 are associated with the fundus front image acquired by the front image observation optical system 200.

  When the operation unit 74 is operated by the examiner, the control unit 70 changes the display position of the pointer 21 on the front image 20 based on the operation signal input from the operation unit 74. In synchronization with the movement of the pointer 21, the control unit 70 displays a tomographic image (for example, the first tomographic image 30 and the second tomographic image 40) corresponding to the cutting position of the pointer 21 on the monitor 75. For example, in synchronization with the movement of the pointer 21, the corresponding tomographic image is updated as needed in real time. Further, the control unit 70 displays the horizontal line 31 and the horizontal line 41 corresponding to the cutting position of the pointer 21 on the monitor 75 in synchronization with the movement of the pointer 21.

  Further, for example, one of the horizontal line 31 and the vertical line 41 may be moved on the images of the first tomographic image 30 and the second tomographic image 40 by a drag operation on the operation unit 74 or the like. The control unit 70 moves the pointer 21 in synchronization with the movement of the horizontal line 31 and the vertical line 41, and also produces a tomographic image (for example, the first tomographic image 30, the second tomographic image 30) corresponding to the cut position of the moved pointer 21. The tomographic image 40) is displayed on the monitor 75.

  Thereby, a tomographic image at a predetermined position on the fundus front image and the fundus front image can be observed at the same time, and the shape of the fundus region can be confirmed from the front direction and the cross-sectional direction. For this reason, it becomes easy to grasp the fundus oculi shape by observing the cross-sectional direction even for a region that is difficult to discriminate only from the observation in the front direction. Further, the tomographic image is updated as needed in conjunction with the movement of the pointer 21, so that the image can be confirmed smoothly without any extra operation.

  The optical coherence tomography device 10 further includes an information detection means (control unit) 70. The control unit 70 detects area information of a selection area surrounded by a predetermined position designated by the pointer 21 on the fundus. For example, the operation unit 74 is operated by the examiner, and a predetermined position on the fundus is designated based on an operation signal input from the operation unit 74. The control unit 70 detects the area information of the selected area formed by connecting the designated predetermined positions.

  Examples of the selection region include a disc or cup of the optic nerve head. The examiner operates the operation unit 74 to designate a predetermined position corresponding to the disc, and forms the disc line (outer edge portion of the disc) 23 by connecting the designated predetermined position. The examiner operates the operation unit 74 to designate a predetermined position corresponding to the cup, and forms the cup line (the outer edge portion of the cup) 25 by connecting the designated predetermined position. When the operation unit 74 is operated by the examiner and the disc line 23 and the cup line 25 of the optic nerve head are designated, the control unit 70 detects the area information of the disc line 23 and the cup line 25. As described above, the front image and the tomographic image of the optic nerve head can be observed at the same time, so that it is possible to accurately detect a region such as a cup or a disk where it is difficult to determine the boundary of the region.

  The area information includes, for example, the C / D ratio of the disc line 23 and the cup line 25 of the optic papilla. The C / D ratio referred to in the present embodiment refers to the radius of the cup line 25 that forms the outer edge of the nipple recess (cup) formed inside the nipple, and the disk line that forms the outer edge of the nipple (disk). It is obtained as a value (ratio) divided by a radius of 23.

  For example, when calculating the C / D ratio, the inside of the disk line 23 is set as the disk area, and the center of gravity of the disk area is set as the center O. The control unit 70 calculates the length of the disc and the length of the cup in the vertical and horizontal directions passing through the center O, and displays the C / D ratio in the horizontal and vertical directions as area information. The setting of the center O is not limited to the above. For example, a square (rectangular) center O circumscribing the nipple edge (disc line) 23 may be calculated as a nipple center by calculation.

  Note that the area information is not limited to the C / D ratio. Any information regarding the detected area may be used. For example, the C / D ratio of the disc line 23 and the cup line 25 of the optic papilla may be detected by 360 ° with respect to the meridian direction, and the maximum value / minimum value may be displayed as region information. Further, area information, length information, and R / D ratio of the selected region may be used. The R / D ratio is determined as the ratio of the width of the rim region defined as the region between the outer edge of the nipple and the outer edge of the nipple recess and the nipple diameter passing through the nipple center. The R / D ratio here is calculated based on the line segment from the center O to the outer edge of the nipple and the line segment from the center O to the outer edge of the nipple recess.

  In the present embodiment, the analysis including the optic nerve head of the eye to be examined is taken as an example, but the present invention is not limited to this. The present invention can also be applied to analysis of lesions and layer thicknesses. An analysis of a lesioned part or a layer thickness includes obtaining an area or volume in a lesioned part region or a thicker or thinner region. The technique of the above embodiment is not limited to the fundus but can be applied to eyes (for example, it can be used for associating a front image of an anterior segment with a three-dimensional image). Furthermore, the present invention is not limited to the eye, and can be applied to a living body or a test object.

  Note that the present embodiment is not limited to the devices described in the above embodiments. For example, ophthalmic analysis software (program) that performs the functions of the above-described embodiments is supplied to a system or apparatus via a network or various storage media. A computer of the system or apparatus (for example, a CPU) can also read and execute the program.

<Example>
Embodiments according to the present invention will be described below with reference to the drawings. FIG. 1 is a schematic configuration diagram illustrating the configuration of the ophthalmologic photographing apparatus according to the present embodiment. In the present embodiment, the axial direction of the subject's eye (eye E) will be described as the Z direction, the horizontal direction as the X direction, and the vertical direction as the Y direction. The surface direction of the fundus may be considered as the XY direction.

  An outline of the apparatus configuration will be described. This apparatus is an optical coherence tomography device (OCT device) 10 for taking a tomographic image of the fundus oculi Ef of the subject's eye E. The OCT device 10 includes an interference optical system (OCT optical system) 100, a front observation optical system 200, a fixation target projection unit 300, and an arithmetic control unit (CPU) 70.

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

<OCT optical system>
The OCT optical system 100 has an apparatus configuration of a so-called ophthalmic optical tomography (OCT: Optical coherence tomography) and takes a tomographic image of the eye E. The OCT optical system 100 splits the light emitted from the measurement light source 102 into measurement light (sample light) and reference light by a coupler (light splitter) 104. The OCT optical system 100 guides the measurement light to the fundus oculi Ef of the eye E by the measurement optical system 106 and guides the reference light to the reference optical system 110. Thereafter, the detector (light receiving element) 120 receives the interference light obtained by combining the measurement light reflected by the fundus oculi Ef and the reference light.

  The detector 120 detects an interference state between the measurement light and the reference light. In the case of Fourier domain OCT, the spectral intensity of the interference light is detected by the detector 120, and a depth profile (A scan signal) in a predetermined range is obtained by Fourier transform on the spectral intensity data. Examples include Spectral-domain OCT (SD-OCT) and Swept-source OCT (SS-OCT). Moreover, Time-domain OCT (TD-OCT) may be used.

  The optical scanner 108 scans light emitted from the measurement light source on the eye fundus. For example, the optical scanner 108 scans the measurement light two-dimensionally (XY direction (transverse direction)) on the fundus. The optical scanner 108 is arranged at a position substantially conjugate with the pupil. The optical scanner 108 is, for example, two galvanometer mirrors, and the reflection angle thereof is arbitrarily adjusted by the drive mechanism 50.

  Thereby, the reflection (advance) direction of the light beam emitted from the light source 102 is changed, and is scanned in an arbitrary direction on the fundus. Thereby, the imaging position on the fundus oculi Ef is changed. The optical scanner 108 may be configured to deflect light. For example, in addition to a reflective mirror (galvano mirror, polygon mirror, resonant scanner), an acousto-optic device (AOM) that changes the traveling (deflection) direction of light is used.

  The reference optical system 110 generates reference light that is combined with reflected light acquired by reflection of measurement light at the fundus oculi Ef. The reference optical system 110 may be a Michelson type or a Mach-Zehnder type. The reference optical system 110 is formed by, for example, a reflection optical system (for example, a reference mirror), and reflects light from the coupler 104 back to the coupler 104 by being reflected by the reflection optical system and guides it to the detector 120. As another example, the reference optical system 110 is formed by a transmission optical system (for example, an optical fiber), and guides the light from the coupler 104 to the detector 120 by transmitting the light without returning.

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

<Front observation optical system>
The front observation optical system (front image observation device) 200 is provided to obtain a front image of the fundus oculi Ef. The observation optical system 200 includes, for example, an optical scanner that two-dimensionally scans the fundus of measurement light (for example, infrared light) emitted from a light source, and a confocal aperture that is disposed at a position substantially conjugate with the fundus. And a second light receiving element for receiving the fundus reflection light, and has a so-called ophthalmic scanning laser ophthalmoscope (SLO) device configuration.

  Note that the configuration of the observation optical system 200 may be a so-called fundus camera type configuration. The OCT optical system 100 may also serve as the observation optical system 200. That is, the front image may be acquired using data that forms a tomographic image obtained two-dimensionally (for example, an integrated image in the depth direction of a three-dimensional image, at each XY position). Integrated value of spectrum data, luminance data at each XY position in a certain depth direction, retina surface layer image, etc.).

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

  For example, the fixation target projection unit 300 has a visible light source that emits visible light, and changes the presentation position of the target two-dimensionally. Thereby, the line-of-sight direction is changed, and as a result, the imaging region is changed. For example, when the fixation target is presented from the same direction as the imaging optical axis, the center of the fundus is set as the imaging site. When the fixation target is presented upward with respect to the imaging optical axis, the upper part of the fundus is set as the imaging region. That is, the imaging region is changed according to the position of the target with respect to the imaging optical axis.

  As the fixation target projection unit 300, for example, a configuration in which the fixation position is adjusted by the lighting positions of LEDs arranged in a matrix, light from a light source is scanned using an optical scanner, and fixation is performed by lighting control of the light source. Various configurations such as a configuration for adjusting the position are conceivable. The projection unit 300 may be an internal fixation lamp type or an external fixation lamp type.

<Control unit>
The control unit 70 controls the entire apparatus such as each member of each configuration 100 to 300. The control unit 70 also serves as an image processing unit that processes the acquired image, an image analysis unit that analyzes the acquired image, and the like. The control unit 70 is realized by a general CPU (Central Processing Unit) or the like. As shown below, the control unit 70 analyzes the fundus oculi Ef based on the tomographic image.

  The control unit 70 obtains a tomographic image by image processing based on the light reception signal output from the detector 120 of the OCT optical system 100, and also detects the front surface based on the light reception signal output from the light receiving element of the front observation optical system 200. Get a statue. Further, the control unit 70 controls the fixation target projection unit 300 to change the fixation position.

  The memory (storage unit) 72, the display monitor 75, and the control unit (operation unit) 74 are electrically connected to the control unit 70, respectively. The control unit 70 controls the display screen of the monitor 75. The acquired fundus image is output to the monitor 75 as a still image or a moving image and stored in the memory 72. The memory 72 records, for example, various types of information related to photographing such as a photographed tomographic image (for example, a three-dimensional image), a front image, and photographing position information of each tomographic image. The memory 72 stores various analysis programs for analyzing the acquired tomographic image. For example, a macular analysis program for analyzing the macular region of the fundus, a nipple analysis program for analyzing the papilla of the fundus, and a lesion analysis program for analyzing a lesion of the fundus are stored as analysis programs. . The control unit 70 controls each member of the OCT optical system 100, the front observation optical system 200, and the fixation target projection unit 300 based on the operation signal output from the control unit 74. A mouse 74a is connected to the operation unit 74 as an operation member operated by the examiner.

  The monitor 75 may be a display monitor mounted on the apparatus main body, a display monitor of a personal computer, or a combination thereof.

  In the present embodiment, the case where the OCT optical system 100 also serves as the observation optical system 200 will be described as an example. The control unit 70 controls the optical scanner 108 to scan the measurement light two-dimensionally, and obtains a tomographic image and a front image as moving images based on the light reception signal output from the detector 120. The acquired tomographic image and front image are displayed on the monitor 75.

  The control operation of the apparatus having the above configuration will be described. The examiner instructs the subject to gaze at the fixation target of the fixation target projection unit 300, and then observes the anterior ocular segment observation image captured by the anterior ocular segment observation camera (not shown) on the monitor 75. The alignment operation is performed using a joystick (not shown) so that the measurement optical axis is at the center of the pupil of the eye to be examined.

  Then, the control unit 70 controls driving of the optical scanner 108, scans the measurement light on the fundus in a predetermined direction, and receives a light reception signal corresponding to a predetermined scanning area from an output signal output from the detector 120 during the scanning. To obtain a fundus image.

  Hereinafter, an example of a method for acquiring a fundus tomographic image (hereinafter referred to as a tomographic image) and a fundus frontal image (hereinafter referred to as a front image) according to the present embodiment will be described. The control unit 70 processes the spectral data detected by the detector 120 and forms a tomographic image and a front image by image processing. The tomographic image and the front image may be acquired at the same time, may be acquired alternately, or may be acquired sequentially. That is, the spectrum data is used for obtaining at least one of a tomographic image and a front image. Note that the acquired tomographic image and front image are displayed on the monitor 75.

  The examiner operates a photographing switch (not shown) at a desired position to start obtaining a three-dimensional image of a front image and a tomographic image displayed on the monitor 75 and stores them in the memory 72 as a still image. Remembered.

  The control unit 70 controls the OCT optical system 100 and acquires a three-dimensional image corresponding to the set area. And the control part 70 acquires a three-dimensional image at any time by the OCT optical system 100. FIG. The three-dimensional image includes image data in which A scan signals are arranged two-dimensionally in the XY directions, a three-dimensional graphic image, and the like.

  When obtaining a three-dimensional image, the control unit 70 controls the operation of the optical scanner 108 and acquires the three-dimensional image by two-dimensionally scanning the measurement light in the XY directions within a scanning range corresponding to the imaging region. As a scanning pattern for obtaining a three-dimensional image, for example, a raster scan, a radial scan, a concentric scan (a plurality of circle scans having different sizes), and the like can be considered.

<Analysis program>
Hereinafter, an analysis program for analyzing a three-dimensional image acquired by the OCT device 10 will be described. In this embodiment, a nipple analysis program for analyzing the optic disc portion of the fundus will be described.

  When the operator operates the operation unit 74 and starts the nipple analysis program, the control unit 70 displays the fundus front image acquired by the front image observation optical system 200 and the fundus tomographic image acquired by the OCT optical system 100. Is displayed. Further, the control unit 70 superimposes and displays a corresponding display indicating a predetermined position of the fundus region on the fundus front image and the fundus tomographic image (details will be described later).

  FIG. 2 is a diagram illustrating an example of a monitor display when the nipple analysis program is activated. The monitor 75 includes a fundus front image 20, a pointer 21 as a first corresponding display, a first fundus tomographic image (first tomographic image) 30, a synchronization line (lateral line) 31 as a second corresponding display, and a second fundus tomographic image. An image (second tomographic image) 40 and a synchronization line (vertical line) 41 as a third corresponding display are displayed.

  The fundus front image 20 is a fundus front image acquired by the front image observation optical system 200. The pointer 21 is for designating a predetermined position (for example, a disc outer peripheral line or a cup outer peripheral line) on the fundus front image 20. The pointer 21 is moved by operating the operation unit 74.

  The first tomographic image 30 and the second tomographic image 40 are tomographic images extracted from the three-dimensional image acquired in advance by the OCT optical system 100, and correspond to the tomographic image of the fundus region where the pointer 21 is located.

  For example, the first tomographic image 30 shows a tomographic image acquired at a cutting position passing through the center 21a of the pointer 21 in the vertical direction (Y direction). The second tomographic image 40 shows a tomographic image acquired at a cutting position passing through the center 21a of the pointer 21 in the horizontal direction (X direction). That is, the center 21 a of the pointer 21 indicates the intersection of the vertical cutting position and the horizontal cutting position on the fundus front image 20 displayed on the monitor 75.

  The horizontal line 31 is displayed on the first tomographic image 30. A horizontal line 31 indicates a cutting position corresponding to the second tomographic image 40 on the first tomographic image 30. A horizontal line 31 indicates a cutting position of the pointer 21 on the first tomographic image 30 in the X direction. The vertical line 41 is displayed on the second tomographic image 40. A vertical line 41 indicates a cutting position corresponding to the first tomographic image 30 on the second tomographic image 40. A vertical line 41 indicates a cutting position in the Y direction of the pointer 21 on the second tomographic image 40. The horizontal line 31 and the vertical line 41 can also be used as pointers for designating a predetermined position (for example, a disk outer peripheral line or a cup outer peripheral line) on each tomographic image. The horizontal line 31 and the vertical line 41 can be moved by operating the operation unit 74.

  Here, the operation of each correspondence display will be described. For example, when the examiner operates the mouse 74 a of the operation unit 74 and an operation signal is input to the control unit 70, the control unit 70 synchronizes with the input operation signal and the pointer 21 in the fundus front image 20. Change the position of. The control unit 70 moves the position of the pointer 21 and changes the first tomographic image 30 and the second tomographic image 40 displayed on the monitor 75. The control unit 70 extracts a tomographic image corresponding to the position of the pointer 21 (center 21 a) after movement from the three-dimensional image stored in the memory 72 and displays it on the screen of the monitor 75. Accordingly, the control unit 70 moves the horizontal line 31 and the vertical line 41 displayed on each tomographic image.

Since the pointer 21 and each tomographic image are linked to each other, when one of them is changed, the other display is also changed. Further, the horizontal line 31 is linked to the pointer 21 and the tomographic image 40, and as one of these is changed, the other display is changed. In addition, the vertical line 41 is linked to the pointer 21 and the tomographic image 30, and as one of these is changed, the other display is also changed. For this reason, the examiner can change the display of each tomographic image and the corresponding display by operating any of these using the mouse 74a. For example, the examiner can change the display on the first tomographic image 30. , The second tomographic image 40 displayed on the monitor 75 is changed, and accordingly the pointer 21 on the fundus front image 20 is moved in the Y direction. Further, the examiner operates the vertical line 41 on the second tomographic image 40 to change the first tomographic image 30 displayed on the monitor 75, and accordingly, the pointer 21 on the fundus front image 20 is moved. It is moved in the X direction.

  The operation in the nipple analysis program will be described below. The examiner observes the fundus front image and the tomographic image displayed on the screen of the monitor 75 in the nipple analysis program, and designates the disk area and the cup area. For example, a disk area setting icon and a cup area setting icon (not shown) are displayed on the monitor 75, respectively. The examiner selects each icon when setting each area, and sets the area.

  The disk area and cup area are specified as follows. For example, when setting a disk area, the examiner operates the mouse 74a, designates a disk area setting icon, and sets the disk area. The examiner moves the pointer 21 displayed on the fundus front image 20 of the monitor 75 by operating the mouse 74a, and makes a large number of predetermined positions (points) at which the outer periphery of the disk (the RPE layer is not interrupted) by quick operation. Specify.

  In this way, the examiner can designate points while observing not only the fundus front image 20 but also the first tomographic image 30 and the second tomographic image 40. For example, the examiner specifies a point while confirming the positional relationship between the horizontal line 31 and the vertical line 41 in addition to the pointer 21 and a characteristic part (for example, a part corresponding to a disk or a cup) in each tomographic image. To do.

  This makes it possible to specify the point by observing the nipple from both the front direction and the cross-sectional direction, so that the position of the disk can be easily grasped, and the disk area can be specified with high accuracy. The position (coordinates) of the designated point is stored in the memory 72.

  FIG. 3 is a diagram showing an example of a display screen on the monitor 75 at the time of area setting. The designated point is displayed as a designated point (point) 22 on the monitor 75 (see FIG. 3A). Of course, the selected point 22 can be changed or deleted.

  When the disk outer periphery is designated, the examiner instructs the control unit 70 to execute the disk outer periphery formation by operating the mouse 74a. The control unit 70 calculates a disc line (disc outer peripheral line (disc outer edge)) 23 so that each designated point 22 is connected by a smooth curve by a spline curve, and superimposes it on the fundus front image 20. Display. By connecting each point 22 with a spline curve, the disk line 23 can be more closely approximated to an actual boundary line even in a distorted disk area. The control unit 70 uses the inside as a disk area and obtains the position of the center of gravity. The position of the center of gravity is used as the center position when the C / D ratio is subsequently obtained.

Here, each point 22 is connected by a spline curve. However, in addition to this, the disk line 23 may be determined by a known smoothing calculation. In order to correctly calculate the disk line 23 by the above calculation, at least four points are selected on the boundary line of the disk. Further, when a monitor 75 having a touch panel is used, the disc line 23 may be directly drawn by a touch operation on the monitor 75 (the cup line 25 described later may be directly drawn in the same manner). May be.)
Next, the examiner obtains a cup area existing in the outer periphery of the disk. For example, when setting a cup area, the examiner operates the mouse 74a, designates a cup area setting icon, and sets the cup area. As in the disk area setting, the examiner moves the pointer 21 displayed on the fundus front image 20 of the monitor 75 by operating the mouse 74a, and makes a number of predetermined positions (points) that become the cup edge by quick operation. Specify. In order to set the cup edge, as shown in FIG. 3B, the position where the blood vessel is bent in the disc of the fundus front image 20 is designated as a predetermined position (point). The designated point is displayed as a designated point (point) 24 as in the case of setting the disk area.

  At this time, when only the fundus front image 20 is observed, it is difficult to determine the position where the blood vessel is bent (blood vessel bending position), and the pointer 21 cannot be moved to specify with high accuracy. However, since the position where the blood vessel is bent can be observed from the first tomographic image 30 and the second tomographic image 40, the blood vessel bending position T can be easily determined by observing each tomographic image. Therefore, by moving the horizontal line 31 and the vertical line 41 on the first tomographic image 30 and the second tomographic image 40, the blood vessel bending position T can be designated with high accuracy. Thereby, each point 21b of the cup edge can be designated with high accuracy. The position (coordinates) of the designated point is stored in the memory 72.

  When the cup edge can be specified by the plurality of points 24, the examiner instructs the control unit 70 to execute the cup edge formation by operating the mouse 74a. The control unit 70 calculates the cup line (cup edge line (cup outer edge part)) 25 so that each designated point 24 is connected by a smooth curve by a spline curve, and superimposes it on the fundus front image 20. Display. As described above, the disk line 23 and the cup line 25 are formed on the fundus front image 20 displayed on the monitor 75.

  Next, the control unit 70 detects area information based on the calculated data of the disk line 23 and the cup line 25. For example, as the area information, information on the C / D ratio is calculated. Hereinafter, a method for calculating the C / D ratio will be described. FIG. 4 is a schematic diagram for calculating the C / D ratio between the disk line 23 and the cup line 25. As shown in FIG. 4, the control unit 70 obtains the center of gravity position O from the obtained disk line 23, and calculates the lengths (Dx and Dy) of the vertical and horizontal disks passing through the center of gravity position O. Similarly, the control unit 70 calculates the lengths (Cx and Cy) of the cups in the vertical direction and the horizontal direction passing through the barycentric position O. The control unit 70 obtains the C / D ratio in the vertical direction and the horizontal direction from the obtained disc length (Dx and Dy) and cup length (Cx and Cy). The control unit 70 displays the calculated C / D ratio on the monitor 75 (see FIG. 5).

  As described above, the frontal fundus image and the tomographic image can be observed at the same time, and by specifying the predetermined area, it is possible to detect the part with high accuracy even for the part where the boundary of the region such as a cup or a disk is difficult to distinguish. Can do. In addition, it is possible to accurately detect the cup and the disk even in a fundus front image acquired by another ophthalmologic photographing apparatus that does not have color contrast.

  In the present embodiment, the calculated C / D ratio may be compared with the C / D ratio in a normal eye, and the comparison result may be displayed. As a result, the examiner can know how much the photographed eye is a normal eye or a diseased eye, and can easily perform his / her own diagnosis or the like.

  In the present embodiment, when calculating a cup line, a plurality of points are designated while observing an image. However, the present invention is not limited to this. A cup line may be automatically set when a disk (disk line) is selected. FIG. 6 is a diagram illustrating the setting of the cup position. In this case, for example, when the disk line is set, the line CL is drawn at a position translated from the line DL connecting the disk position D1 and the disk position D2 forming the disk line upward by 150 μm. Then, the intersection of the line CL and the ILM (retinal pigment epithelium) is set as the cup positions C1 and C2, thereby setting the cup line.

It is a schematic block diagram explaining the structure of the ophthalmologic imaging apparatus which concerns on a present Example. It is a figure which shows an example of the monitor display at the time of nipple analysis program starting. It is a figure which shows an example of the display screen in the monitor at the time of area | region setting. It is a schematic diagram for calculating the C / D ratio of the disk line and the cup line. It is a figure which shows an example of the display screen at the time of displaying the calculated C / D ratio on a monitor. It is a figure explaining the setting of a cup position.

10 Optical coherence tomography device (OCT device)
21 Pointer 31 Horizontal Line 41 Vertical Line 70 Arithmetic Control Unit 72 Memory 74 Operation Unit 75 Monitor 100 Interference Optical System (OCT Optical System)
200 Front observation optical system 300 Fixation target projection unit

Claims (5)

  1. A front image acquisition means for acquiring a front image of the eye to be examined;
    A tomographic image acquisition means for obtaining a tomographic image of the eye to be examined by using interference between the measurement light reflected from the eye to be examined and the reference light;
    Display means for displaying an image acquired by the front image acquisition means and the tomographic image acquisition means;
    Operation input means;
    A pointer that is two-dimensionally movable on the front image based on an operation signal input from the operation input unit is displayed on the display unit, and a predetermined part for calculating a predetermined parameter related to analysis of the eye to be examined Calculation control means for displaying on the display means tomographic images orthogonal to each other with reference to the position of the pointer on the front image, in order to obtain position information;
    An ophthalmic analysis apparatus comprising:
  2. The ophthalmic analysis apparatus according to claim 1,
    The arithmetic control unit is an ophthalmologic analyzer that displays position information corresponding to a position of a pointer on the front image on the tomographic image.
  3. In any of the ophthalmic analysis system according to claim 1-2,
    The arithmetic control means includes
    An ophthalmologic analyzer that displays tomographic images orthogonal to each other on the basis of the position of the moved pointer in synchronization with the movement of the pointer on the front image.
  4. A front image acquisition means for acquiring a front image of the eye to be examined;
    A tomographic image acquisition means for obtaining a tomographic image of the eye to be examined by using interference between the measurement light reflected from the eye to be examined and the reference light;
    Display means for displaying an image acquired by the front image acquisition means and the tomographic image acquisition means;
    Operation input means;
    A pointer that is two-dimensionally movable on the front image is displayed on the display unit based on an operation signal input from the operation input unit, and is orthogonal to each other with reference to the position of the pointer on the front image. Calculation control means for displaying a tomographic image to be displayed on the display means,
    The arithmetic control unit displays on the display unit tomographic images orthogonal to each other with reference to the position of the moved pointer in synchronization with the movement of the pointer on the front image. .
  5. Displaying the images acquired by the front image acquiring means and the tomographic image acquiring means on the display means;
    A position on a predetermined part for displaying a pointer that can be moved two-dimensionally on a front image on the front image based on an operation signal input from the operation input unit and calculating a predetermined parameter relating to the analysis of the eye to be examined Displaying the tomographic images orthogonal to each other with reference to the position of the pointer on the front image on the display means to obtain information;
    A step of calculating a predetermined parameter related to the analysis of the eye to be examined using the acquired position information regarding the predetermined site;
    An ophthalmic analysis program characterized by causing a computer to execute.
JP2012019306A 2012-01-31 2012-01-31 Ophthalmic analysis apparatus and program Active JP5970833B2 (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
JP2012019306A JP5970833B2 (en) 2012-01-31 2012-01-31 Ophthalmic analysis apparatus and program

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
JP2012019306A JP5970833B2 (en) 2012-01-31 2012-01-31 Ophthalmic analysis apparatus and program

Publications (3)

Publication Number Publication Date
JP2013154119A JP2013154119A (en) 2013-08-15
JP2013154119A5 JP2013154119A5 (en) 2015-03-12
JP5970833B2 true JP5970833B2 (en) 2016-08-17

Family

ID=49049908

Family Applications (1)

Application Number Title Priority Date Filing Date
JP2012019306A Active JP5970833B2 (en) 2012-01-31 2012-01-31 Ophthalmic analysis apparatus and program

Country Status (1)

Country Link
JP (1) JP5970833B2 (en)

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2016101298A (en) * 2014-11-28 2016-06-02 株式会社トプコン Ophthalmological photographing apparatus

Family Cites Families (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
ES2374069T3 (en) * 2006-01-19 2012-02-13 Optovue, Inc. Method of examination of the eye by tomography of optical coherence.
JP5085086B2 (en) * 2006-10-04 2012-11-28 株式会社トプコン Fundus observation apparatus, fundus image display apparatus, and program

Also Published As

Publication number Publication date
JP2013154119A (en) 2013-08-15

Similar Documents

Publication Publication Date Title
EP1961374B1 (en) Fundus oculi observation device and fundus oculi image processing device
JP5085086B2 (en) Fundus observation apparatus, fundus image display apparatus, and program
EP2301423B1 (en) Optical image measuring device
US7370966B2 (en) Opthalmologic apparatus
US8593514B2 (en) Ophthalmic photographing apparatus
JP5192394B2 (en) Examining the eye by optical coherence tomography
EP1864608A1 (en) A fundus observation device, an ophthalmologic image processing unit, an ophthalmologic image processing method
JP5079240B2 (en) Retinal function measuring device
US9980643B2 (en) Ophthalmologic apparatus
JP5404078B2 (en) Optical image measuring device
CN101268928B (en) Fundus oculi observation device and ophthalmic image display device
US8096658B2 (en) Fundus oculi observation device and program for controlling the same
US9681803B2 (en) Method of observing a three-dimensional image of examinee&#39;s eye
US8419186B2 (en) Fundus observation apparatus
JP4969925B2 (en) Fundus observation device
JP2008237238A (en) Optical image measurement instrument, image processor, and program
US20120184846A1 (en) Imaging and visualization systems, instruments, and methods using optical coherence tomography
JP2008267892A (en) Optical image measuring device and program for controlling same
JP2013116366A (en) Ophthalmologic information processing apparatus and ophthalmologic examination apparatus
JP5231802B2 (en) Ophthalmic imaging equipment
US20070236660A1 (en) Fundus Observation Device
EP2425763B1 (en) Eyeground observation device
JP5735790B2 (en) Ophthalmic imaging equipment
US8804127B2 (en) Image acquisition apparatus, image acquisition system, and method of controlling the same
KR101506526B1 (en) Ophthalmologic apparatus and control method therefor

Legal Events

Date Code Title Description
A521 Written amendment

Free format text: JAPANESE INTERMEDIATE CODE: A523

Effective date: 20150123

A621 Written request for application examination

Free format text: JAPANESE INTERMEDIATE CODE: A621

Effective date: 20150123

A977 Report on retrieval

Free format text: JAPANESE INTERMEDIATE CODE: A971007

Effective date: 20151118

A131 Notification of reasons for refusal

Free format text: JAPANESE INTERMEDIATE CODE: A131

Effective date: 20151124

A521 Written amendment

Free format text: JAPANESE INTERMEDIATE CODE: A523

Effective date: 20160122

TRDD Decision of grant or rejection written
A01 Written decision to grant a patent or to grant a registration (utility model)

Free format text: JAPANESE INTERMEDIATE CODE: A01

Effective date: 20160614

A61 First payment of annual fees (during grant procedure)

Free format text: JAPANESE INTERMEDIATE CODE: A61

Effective date: 20160627

R150 Certificate of patent or registration of utility model

Ref document number: 5970833

Country of ref document: JP

Free format text: JAPANESE INTERMEDIATE CODE: R150

R157 Certificate of patent or utility model (correction)

Free format text: JAPANESE INTERMEDIATE CODE: R157

R157 Certificate of patent or utility model (correction)

Free format text: JAPANESE INTERMEDIATE CODE: R157

R250 Receipt of annual fees

Free format text: JAPANESE INTERMEDIATE CODE: R250