JP2010012109A - Ocular fundus photographic apparatus - Google Patents

Ocular fundus photographic apparatus Download PDF

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Publication number
JP2010012109A
JP2010012109A JP2008176151A JP2008176151A JP2010012109A JP 2010012109 A JP2010012109 A JP 2010012109A JP 2008176151 A JP2008176151 A JP 2008176151A JP 2008176151 A JP2008176151 A JP 2008176151A JP 2010012109 A JP2010012109 A JP 2010012109A
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Prior art keywords
fundus
image
light
eye
optical
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JP2008176151A
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Japanese (ja)
Inventor
Naoki Isogai
直己 磯貝
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Nidek Co Ltd
株式会社ニデック
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Priority to JP2008176151A priority Critical patent/JP2010012109A/en
Publication of JP2010012109A publication Critical patent/JP2010012109A/en
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    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/102Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for optical coherence tomography [OCT]

Abstract

PROBLEM TO BE SOLVED: To preferably observe and photograph the fundus of a subject eye without providing a special mechanism for aligning the subject eye with an apparatus.
A fundus image obtained on the basis of a light reception signal output from a light receiving element has an illumination optical system that irradiates illumination light to the fundus of a subject and a light receiving optical system that receives fundus reflected light by a light receiving element. In a fundus photographing apparatus for continuously displaying moving images as observation images on a monitor, reference image setting means for setting all or part of a predetermined fundus image obtained by a light reception signal as a reference image, a reference image, and a fundus acquired thereafter The positional deviation information acquisition means for comparing the image with the image using image processing and acquiring three-dimensional positional deviation information for the fundus image set as the reference image, and the positional deviation information acquired by the positional deviation information acquisition means And an alignment control means for aligning the fundus image displayed on the monitor or the apparatus with respect to the eye to be examined. [Selection figure] Figure 1

Description

  The present invention relates to a fundus imaging apparatus that observes and images the fundus of a subject's eye.
As an ophthalmologic photographing apparatus for observing and photographing the fundus of a subject eye, a fundus camera and a scanning laser off-salmoscope (SLO apparatus) are known. Also, there is a fundus imaging apparatus (OCT apparatus) that designates an arbitrary position from a fundus front image acquired by such a fundus camera optical system or SLO optical system and acquires a fundus tomographic image using an optical interference optical system. It is known (see Patent Document 1).
JP 2008-29467 A
In the ophthalmologic photographing apparatus described above, for example, a fluorescent photographing in which a fluorescent agent is injected and the fluorescent agent spreads in a blood vessel on the fundus, and a plurality of photographings are performed from the central region of the fundus to the peripheral region, By connecting these, the fundus may be continuously observed and photographed, such as panoramic photography for photographing a wide fundus region. However, when the fundus is continuously observed and photographed in this way, if the eye to be examined moves, the fundus image displayed on the monitor also moves, which makes it difficult to observe or re-shoots. Further, in the fundus camera, an index is projected onto the fundus and a matching state is determined from the state of the index image. However, providing such a mechanism leads to an increase in the cost and size of the apparatus.
In view of the above problems, the present invention provides a fundus imaging apparatus that can preferably observe and photograph the fundus of a subject eye without providing a special mechanism for aligning the subject eye with the device. This is a technical issue.
In order to solve the above problems, the present invention is characterized by having the following configuration.
(1) An illumination optical system for irradiating the fundus of the subject's eye with illumination light and a light receiving optical system for receiving fundus reflected light from the illumination optical system by a light receiving element, and based on a light reception signal output from the light receiving element In a fundus photographing apparatus that continuously displays a moving image of a fundus image of an eye to be examined as an observation image on a monitor, all or part of a predetermined fundus image obtained by a light reception signal output from the light receiving element is set as a reference image Positional deviation information for comparing the reference image and the fundus image acquired thereafter using image processing to obtain three-dimensional positional deviation information for the fundus image set as the reference image Based on the positional deviation information acquired by the acquisition means and the positional deviation information acquisition means, alignment of the apparatus with respect to the eye to be examined or display on the monitor Alignment control means for performing alignment of the fundus image to be performed.
(2) In the fundus imaging apparatus according to (1),
The positional deviation information acquisition means sets at least two target areas that are the same part on the reference image and the fundus image acquired thereafter, and the positional deviation of the target area of the fundus image with respect to the reference image The variation in the amount and the distance between the target areas is acquired as the positional deviation information.
(3) In the fundus imaging apparatus according to (2), the illumination optical system includes a scanning unit that scans the fundus with a laser beam emitted from a light source as the illumination light, and the alignment unit is based on the positional deviation information. The fundus image displayed on the monitor is aligned by performing control to change the scanning range on the fundus to be examined by the scanning unit.
(4) In the fundus imaging apparatus according to (3), the illumination optical system has a focusing lens for focusing on the fundus of the eye to be examined, and the alignment control means controls the focusing lens based on the positional deviation information. It is characterized by being driven in the optical axis direction.
(5) The fundus imaging apparatus according to (4) further receives interference light obtained by combining reference light generated by light emitted from a light source and fundus reflected light from the measurement light emitted to the subject eye fundus. And an interference optical system for obtaining a tomographic image of the fundus of the eye to be examined.
(6) The fundus imaging apparatus according to (5) includes switch means for determining a timing for setting the reference image.
  According to the present invention, the fundus of the eye to be examined can be preferably observed and photographed without providing a special mechanism for aligning the eye to be examined and the apparatus.
Embodiments of the present invention will be described with reference to the drawings. FIG. 1 is a diagram illustrating an optical system and a control system of the fundus imaging apparatus of the present embodiment. In the present embodiment, the depth direction of the eye to be examined is described as the Z direction (the optical axis L1 direction), the horizontal direction is the X direction, and the vertical direction is the Y direction.
In FIG. 1, the optical system uses an interference optical system (hereinafter referred to as an OCT optical system) 200 for non-invasively obtaining a tomographic image of the fundus of the eye to be examined using an optical interference technique, and infrared light. A scanning laser ophthalmoscope (SLO) optical system 300 that acquires an SLO fundus image for illuminating and observing the fundus of the eye to be examined is roughly classified.
  Reference numeral 40 denotes a dichroic mirror as a light splitting member, which reflects measurement light (for example, near λ = 840 nm) emitted from the measurement light source 27 used in the OCT optical system 200 and is used in the SLO optical system 300. 61 has a characteristic of transmitting laser light emitted from 61 (light having a wavelength different from that of the light source 27, for example, near λ = 780 nm). In this case, the dichroic mirror 40 makes the measurement optical axis L2 of the OCT optical system 200 and the measurement optical axis L1 of the SLO optical system 300 coaxial.
  First, the configuration of the OCT optical system 200 provided on the reflection side of the dichroic mirror 40 will be described. Reference numeral 27 denotes an OCT light source that emits low-coherent light used as measurement light and reference light of the OCT optical system 200. For example, an SLD light source is used. For the OCT light source 27, for example, a light source having a center wavelength of 840 nm and a bandwidth of 50 nm is used. Reference numeral 26 denotes a fiber coupler that doubles as a light splitting member and a light coupling member. The light emitted from the OCT light source 27 is split into reference light and measurement light by the fiber coupler 26 via an optical fiber 38a as a light guide. The measurement light goes to the eye E through the optical fiber 38b, and the reference light goes to the reference mirror 31 through the optical fiber 38c.
  In the optical path for emitting the measurement light toward the eye E, the end 39b of the optical fiber 38b for emitting the measurement light, the focusing lens 24 movable in the optical axis direction according to the refractive error of the eye to be examined, and the scanning drive mechanism A scanning unit 23 composed of a combination of two galvanometer mirrors capable of scanning measurement light in the XY directions on the fundus by driving 51 and a relay lens 22 are arranged. The dichroic mirror 40 and the objective lens 10 serve as a light guide optical system that guides OCT measurement light from the OCT optical system 200 to the fundus of the eye to be examined. Note that the scanning unit 23 of the present embodiment has a configuration in which the scanning direction of the measurement light to be scanned on the fundus can be arbitrarily set by arbitrarily adjusting the reflection angle of the measurement light by the two galvanometer mirrors. Yes. Therefore, it is possible to obtain a tomographic image of an arbitrary region of the fundus of the eye to be examined. Note that the end 39b of the optical fiber 38b is disposed so as to be conjugate with the fundus of the eye to be examined. Further, the two galvanometer mirrors of the scanning unit 23 are arranged at a position substantially conjugate with the eye pupil to be examined.
The measurement light emitted from the end 39b of the optical fiber 38b reaches the scanning unit 23 via the focusing lens 24, and the reflection direction is changed by driving the two galvanometer mirrors. Then, the measurement light reflected by the scanning unit 23 is reflected by the dichroic mirror 40 via the relay lens 22 and then condensed on the fundus of the eye to be examined via the objective lens 10.
Then, the measurement light reflected from the fundus is reflected by the dichroic mirror 40 through the objective lens 10, travels to the OCT optical system 200, passes through the relay lens 22, the two galvanometer mirrors of the scanning unit 23, and the focusing lens 24. The light enters the end 39b of the optical fiber 38b. The measurement light incident on the end 39b reaches the end 84a of the optical fiber 38d through the optical fiber 38b, the fiber coupler 26, and the optical fiber 38d.
On the other hand, an end portion 39c of an optical fiber 38c that emits the reference light, a collimator lens 29, and the reference mirror 31 are arranged in the optical path that emits the reference light toward the reference mirror 31. The reference mirror 31 is configured to be movable in the optical axis direction by the reference mirror drive mechanism 50 in order to change the optical path length of the reference light.
The reference light emitted from the end 39c of the optical fiber 38c is converted into a parallel light beam by the collimator lens 29, reflected by the reference mirror 31, collected by the collimator lens 29, and incident on the end 39c of the optical fiber 38c. The reference light incident on the end 39c reaches the fiber coupler 26 through the optical fiber 38c.
  Then, the reference light generated as described above by the light emitted from the light source 27 and the fundus reflection light by the measurement light irradiated on the eye fundus to be examined are combined by the fiber coupler 26 to be interference light, The light is emitted from the end portion 84b through the fiber 38d. A spectroscopic optical system 800 (spectrometer unit) 800 separates interference light into frequency components in order to obtain an interference signal for each frequency, and includes a collimator lens 80, a grating mirror (diffraction grating) 81, a condensing lens 82, and a light receiving element. 83. The light receiving element 83 is a one-dimensional element (line sensor) having sensitivity in the infrared region.
  Here, the interference light emitted from the end portion 84 a is collimated by the collimator lens 80, and then is split into frequency components by the grating mirror 81. Then, the interference light split into frequency components is condensed on the light receiving surface of the light receiving element 83 via the condenser lens 82. Thereby, spectrum information of interference fringes is recorded on the light receiving element 83. Then, the spectrum information is input to the control unit 70 and analyzed using Fourier transform, whereby information in the depth direction of the subject's eye can be measured. Here, the control unit 70 can acquire a tomographic image by causing the scanning unit 23 to scan the measurement light on the fundus in a predetermined transverse direction. For example, a tomographic image on the XZ plane or YZ plane of the fundus of the eye to be examined can be acquired by scanning in the X direction or the Y direction. And a method for obtaining a tomographic image is referred to as a B-scan). The acquired tomographic image is stored in a memory 72 connected to the control unit 70. Furthermore, it is also possible to acquire a three-dimensional image of the fundus of the eye to be examined by two-dimensionally scanning the measurement light in the XY direction. The acquisition of the OCT image in the present embodiment is performed by two galvanometer mirrors provided in the scanning unit 23.
Next, the SLO optical system (confocal optical system) 300 disposed in the transmission direction of the dichroic mirror 40 will be described. The SLO optical system 300 is broadly divided into an illumination optical system that illuminates the fundus of the eye to be examined and a light receiving optical system that receives the reflected light of the eye to be examined illuminated by the illumination optical system by the light receiving element, and is output from the light receiving element. A front image of the fundus of the eye to be examined is obtained based on the received light signal.
Reference numeral 61 denotes an SLO light source that emits highly coherent light. For example, a laser diode light source of λ = 780 nm is used. In the optical path for emitting the laser light emitted from the SLO light source 61 toward the eye E to be examined, the focusing lens 63 that can move in the optical axis direction according to the refractive error of the eye to be examined, and the scanning drive mechanism 52 drive the fundus. A scanning unit 64, a relay lens 65, and an objective lens 10, which are a combination of a galvanometer mirror and a polygon mirror capable of scanning measurement light at high speed in the XY directions, are arranged. Further, the reflection surfaces of the galvanometer mirror and the polygon mirror of the scanning unit 64 are arranged at a position substantially conjugate with the eye pupil to be examined.
A beam splitter 62 is disposed between the SLO light source 61 and the focusing lens 63. In the reflection direction of the beam splitter 62, a condensing lens 66 for constituting a confocal optical system, a confocal aperture 67 placed at a conjugate position to the fundus, and an SLO light receiving element 68 are provided. Yes.
Here, the laser light (measurement light) emitted from the SLO light source 61 passes through the beam splitter 62, reaches the scanning unit 64 via the focusing lens 63, and is reflected in the reflection direction by driving the galvanometer mirror and the polygon mirror. be changed. The laser light reflected by the scanning unit 64 is transmitted through the dichroic mirror 40 via the relay lens 65 and then condensed on the fundus of the eye to be examined via the objective lens 10.
  Then, the laser light reflected from the fundus is reflected by the beam splitter 62 through the objective lens 10, the relay lens 65, the galvano mirror and polygon mirror of the scanning unit 64, and the focusing lens 63. Thereafter, the light is condensed by the condenser lens 66 and then detected by the light receiving element 68 through the confocal aperture 67. Then, the light reception signal detected by the light receiving element 68 is input to the control unit 70. The control unit 70 acquires a front image of the fundus of the eye to be examined based on the light reception signal obtained by the light receiving element 68. The acquired front image is stored in the memory 72. The acquisition of the SLO image is performed by vertical scanning (sub-scanning) of laser light by a galvanometer mirror provided in the scanning unit 64 and horizontal scanning (main scanning) of laser light by a polygon mirror.
  The control unit 70 is connected to the display monitor 75 and controls the display image. Further, the control unit 70 includes a memory 72, an operation switch group 74 (a measurement start switch 74a, a measurement position setting switch 74b, an imaging start switch 74c, an autocoherence switch 74d, and an auto tracking start switch 74f), a reference mirror driving mechanism 50, A lens driving mechanism 63a for moving the focusing lens 63 in the optical axis direction, a lens driving mechanism 24a for moving the focusing lens 24 in the optical axis direction, and the like are connected. The lens driving mechanisms 24 a and 63 a are configured to be driven simultaneously by manual operation of a focus knob (not shown) and a control signal from the control unit 70.
  Next, a method of acquiring a tomographic image (B scan image) on the XZ plane by B scan will be described. FIG. 2 is a diagram illustrating an operation when sequentially acquiring an OCT image (right side) by B-scan and an SLO image (left side) by two-dimensional scan. Here, the control unit 70 turns on the irradiation light irradiated on the fundus of the eye to be inspected via the OCT optical system 200 in order to obtain the fundus image of the eye to be examined by alternately turning on the OCT light source 27 and the SLO light source 61. Switching is performed between the irradiated measurement light and the laser light irradiated via the SLO optical system. Therefore, an interference signal detected by the light receiving element 83 disposed in the OCT optical system 200 and a light reception signal detected by the light receiving element 68 disposed in the SLO optical system 300 are sequentially input to the control unit 70.
  Here, the control unit 70 divides the upper and lower end areas (hatched portions in FIG. 2) of the scanning area for one frame of the SLO image that hardly affect the image acquisition for the time required for the OCT image acquisition. The SLO light source 61 is turned OFF while it is located in that area. Then, while the SLO light source 61 is OFF, the OCT light source 27 is turned ON and an OCT image is acquired by B scan.
  In this case, the number of scanning lines in the vertical direction in SLO image acquisition corresponding to the time required for OCT image acquisition is obtained, and the obtained scanning line segments are set equally from the upper and lower ends of the SLO image acquisition area. While the laser light is being scanned by the galvanometer mirror of the scanning unit 64, the control for turning off the SLO light source 61 and turning on the OCT light source 27 instead is performed only while the laser beam is positioned at the set scanning line portion. While the OCT light source 27 is turned on, an OCT image for at least one frame is acquired. The control unit 70 continuously performs such control, and displays the alternately obtained SLO images and OCT images as moving images on the display monitor 75 at the same time. Note that the scanning range of the irradiation light on the fundus by the scanning unit 64 having a galvanometer mirror and a polygon mirror can scan a range sufficiently wider than the image area displayed on the monitor 75. In the present embodiment, the scanning unit 64 does not always scan the maximum scanning range, but scans about the scanning area required for display on the display monitor 75.
The operation of the apparatus having the above configuration will be described. Here, the control unit 70 drives and controls the OCT optical system 200 and the SLO optical system 300 to acquire each image of the OCT image and the SLO image for each frame, and controls the display of the monitor 75 to the monitor 75. The displayed OCT image and SLO image are updated as needed. Note that the first OCT image acquisition position not depending on the examiner's setting is, for example, a predetermined area in the horizontal direction from the center position of the SLO image.
First, the examiner instructs the subject to gaze a fixation lamp (not shown), and then observes the anterior ocular segment observation image captured by the anterior ocular segment observation camera (not shown) on the monitor 75. An alignment operation is performed using a joystick (not shown) so that the measurement optical axis L1 is placed at the center of the pupil. The alignment with respect to the optical axis direction is performed so that the front image (SLO fundus image) of the fundus to be examined displayed on the monitor 75 is displayed brightest and clearly. Further, by operating the focus knob, the focusing lens 63 is moved in the optical axis direction so that the SLO fundus image is displayed on the monitor 75 with good contrast. The focusing lens 24 is also moved simultaneously by operating the focus knob, and the focus adjustment of the OCT image is also performed.
When the automatic tracking switch 74f is used in a state where the alignment is performed by such manual operation and the SLO fundus image is displayed in a state suitable for the monitor 75, the control unit 70 causes the fundus image displayed on the monitor 75 to be displayed. The tracking control of the apparatus is performed on the eye E so that the movement does not appear as much as possible.
When the focus of the SLO image displayed on the same screen is in an appropriate state, the examiner sets the position of the tomographic image that the examiner wants to photograph from the SLO image on the display monitor 75 observed in real time. The examiner operates the measurement position setting switch 74b to display a line LS representing the measurement position (acquisition position) electrically displayed on the SLO image on the screen as shown in FIG. 4 with respect to the SLO fundus image. Move it and set the measurement position. If the line LS is set to be in the X direction, a tomographic image on the XZ plane is taken, and if the line LS is set to be in the Y direction, a tomographic image on the YZ plane is taken. It has become. Further, the line LS may be set to an arbitrary shape (for example, an oblique direction or a circle).
  Then, the control unit 70 performs an XZ plane tomographic image capturing operation by B-scan based on the set measurement position. That is, the control unit 70 drives the scanning unit 23 to measure the measurement light so that a tomographic image of the fundus oculi at the position of the line LS is obtained based on the display position of the line LS set on the SLO image on the screen. To scan. Since the relationship between the display position of the line LS (coordinate position on the monitor) and the scanning position of the measurement light by the scanning unit 23 is determined in advance, the control unit 70 performs scanning corresponding to the set display position of the line LS. The two galvanometer mirrors of the scanning unit 23 are appropriately driven and controlled so that the measurement light is scanned over the range.
  Here, when the line LS is moved with respect to the SLO fundus image by the examiner, the control unit 70 sets the measurement position at any time, and acquires the tomographic image at the corresponding measurement position. Then, the acquired tomographic image is displayed on the display screen of the monitor 75 as needed. Thus, the tomographic image desired by the examiner is displayed on the monitor 75, and when the imaging start switch 74 c is pressed by the examiner, the desired tomographic image and the front image are stored in the memory 72.
Hereinafter, an auto tracking method according to the present embodiment will be described with reference to a flowchart shown in FIG.
When the auto tracking switch 74f is pressed, the control unit 70 causes the memory 72 to store the fundus image displayed on the monitor 75 as the reference image K at the timing when the switch is pressed. Next, the control unit 70 compares the reference image K with image processing using fundus images sequentially acquired thereafter. The comparison between the images may be performed for each frame after the reference image K is stored, or a fundus image obtained for each predetermined number of frames may be used.
5 and 6 are diagrams illustrating an example in which the reference image K is compared with the fundus image acquired thereafter. Here, the fundus oculi image 100a shown in FIG. 5 shows an example in which the eye to be examined has moved and moved in the left-right direction on the paper surface with respect to the reference image K. A fundus image 100b shown in FIG. 6 shows a state in which the focus (or working distance in the Z-axis direction) is different from the reference image K and the image is enlarged.
As shown in FIG. 5, first, the control unit 70 takes a plurality of target areas 101 on the reference image K for comparing the images. For example, the target area is set to have a size that allows a retina portion and a blood vessel portion to enter, so that feature points can be easily recognized. In the present embodiment, the target area 101 is arranged in a concentric circle centered on the target area 101a at the center of the reference image K displayed on the monitor, and is set at an equal distance from the center at equal intervals. A total of five target areas of the target areas 101b to 101e are set.
  Next, the control unit 70 determines the target areas 101a ′ to 101e ′ on the fundus image 100a to be the same target area set in the reference image K using the image processing technique for the target fundus image 100a. . Specifically, for example, the control unit 70 compares (pixel difference) the target areas 101a to 101e set in the reference image K with the target areas 101a ′ to 101e ′ of the newly obtained fundus image 100a. And the control part 70 should just search for the position where the sum total of the difference with each area | region 101a-101e becomes the smallest, shifting the area | region position of each object area | region 101a'-101e 'on the fundus image 100a. Using such a method, the target areas 101a ′ to 101e ′ on the fundus image 100a are determined. The control unit 70 uses the overall center positions of the target areas 101a to 101e on the reference image K and the positions of the target areas 101a ′ to 101e ′ on the fundus image 100a as position parameters, and the position of the fundus image 100a with respect to the reference image K By obtaining the amount of deviation of the parameters, the amount of deviation of the fundus image 100a acquired thereafter with respect to the reference image K, in other words, the change in the imaging range (scanning range) due to the movement of the eye E to be examined is known. Can do. The control unit 70 performs control to change the scanning range of the scanning unit 64 based on the obtained positional deviation amount so that the deviation amount is eliminated (so as to be small).
  Note that the change control of the scanning range of the scanning unit 64 based on such a deviation amount is similarly applied to the scanning unit 23. Therefore, even if the eye E moves slightly, the SLO image and the OCT image are always displayed on the monitor 75 at the same position by such control. In this embodiment, the scanning range is changed based on the positional deviation amount. However, the present invention is not limited to this, and the alignment of the apparatus with respect to the eye E so that the deviation amount obtained by the positional parameter is offset. Alternatively, the fundus image displayed on the monitor may be aligned. For example, the scanning range of the scanning unit 64 may be set sufficiently larger than the fundus area displayed on the monitor 75, and the display area of the fundus image displayed on the monitor 75 may be changed in software according to the amount of deviation. . In addition, the scanning range of the scanning unit 64 and the scanning unit 23 is not changed based on the positional deviation, but the OCT optical system 200 and the SLO optical system 300 as a whole are integrally three-dimensionally using driving means such as a motor (not shown). It can also be made to drive automatically.
Also in FIG. 6, the target areas 101 a ′ to 101 e ′ are set for the fundus image 100 b using the method described above. The length information between the target areas of the reference image K and the fundus image 100b can be used as a size parameter, and this can be handled as information for the front-rear direction deviation or focus deviation with respect to the eye E. Specifically, the lengths h1 to h4 (h1 ′) between the centers from the target area 101a (101a ′) at the center of the reference image K (fundus image 100) to the target areas 101b to 101e (101b ′ to 101e ′). ˜h4 ′) is averaged (or summed), and this is used as a size parameter. The focusing lenses 24 and 63 are moved in the optical axis direction so that the size parameter of the fundus image 100b becomes equal to the size parameter obtained from the reference image K, thereby adjusting the focus deviation. Note that the OCT optical system 200 and the SLO optical system 300 as a whole may be moved back and forth in the axial direction by a driving unit (not shown) as a shift in the Z-axis direction (front-rear direction) without driving the focusing lens.
By continuously performing such control, even if the eye E moves, it is possible to continue to appropriately photograph the same part in both the SLO image and the OCT image. If only the OCT image needs to be tracked, the tracking operation is not performed on the SLO image, and the scanning unit 23 of the OCT optical system 200 may be driven and controlled based on the acquired SLO image.
In the above embodiment, the focusing optical member is separately disposed in the OCT optical system 200 and the SLO optical system 300. However, the light source, the optical scanning system, the OCT optical system and the SLO optical system, The present invention can be applied even if the focusing lens moved in the optical axis direction is shared by the OCT optical system and the SLO optical system.
Furthermore, in the present embodiment, five target areas are set for one fundus image. However, the present invention is not limited to this, and at least two target areas may be set. In addition, the target region only needs to be selected in the reference image and the fundus image acquired thereafter, and feature regions such as the nipple and blood vessels are extracted in advance by image processing and set as the target region. It is also possible to do.
  Furthermore, in this embodiment, the auto tracking function is started by using a predetermined switch. However, the present invention is not limited to this, and the alignment and focus of the apparatus with respect to the eye to be examined are within a certain range. It is also possible to detect that it has been stored by image processing of the control unit, and automatically start the tracking function based on the detection result. As the image processing, the obtained fundus image is differentiated to obtain contrast information, and the suitability of the focus can be determined based on this. In the present embodiment, the entire fundus image displayed on the monitor is stored as reference information. However, the present invention is not limited to this, and only a necessary area (target region) on the fundus image is used as reference information. Can also be stored.
In the present embodiment, the acquired fundus image during measurement / observation is used as a reference image and a fundus image for comparison. However, the present invention is not limited to this. For example, by using past fundus image data of the same subject as a reference image and performing the above-described image processing and drive control, the same part can be efficiently remeasured and observed.
In the present embodiment, the fundus photographing apparatus having the SLO optical system and the OCT optical system has been described as an example. However, the present invention is not limited to this, and the fundus photographing apparatus for photographing other fundus such as a fundus camera is used. Is also applicable.
It is the figure which showed the optical system and control system of the fundus imaging apparatus of this embodiment. It is the figure which showed the method of acquiring an SLO image and an OCT image sequentially. It is the flowchart which showed the flow of control for performing tracking. It is the figure which showed the display screen for selecting an OCT image from an SLO image. It is the schematic diagram which showed the method of comparing a reference | standard image and a fundus image. It is the schematic diagram which showed the method of comparing a reference | standard image and a fundus image.
Explanation of symbols
23 Scanning Unit 64 Scanning Unit 70 Controlling Unit 72 Memory 74 Operation Switch Group 75 Display Monitor 200 OCT Optical System 300 SLO Optical System

Claims (6)

  1. An illumination optical system that irradiates the fundus of the subject's eye with illumination light, and a light receiving optical system that receives the fundus reflected light from the illumination optical system with a light receiving element, and is obtained based on a light reception signal output from the light receiving element. In a fundus photographing apparatus that continuously displays a moving image of a fundus image of an optometry as an observation image on a monitor, a reference image that sets all or part of a predetermined fundus image obtained by a light reception signal output from the light receiving element as a reference image A positional deviation information acquiring unit that compares the reference image with the fundus image acquired thereafter using image processing and acquires three-dimensional positional deviation information with respect to the fundus image set as the reference image; Based on the positional deviation information acquired by the positional deviation information acquisition means, the apparatus is aligned with the eye to be examined or displayed on the monitor Fundus photographing apparatus characterized by comprising an alignment control means for performing alignment of the bottom image.
  2. The fundus imaging apparatus according to claim 1,
    The positional deviation information acquisition means sets at least two target areas that are the same part on the reference image and the fundus image acquired thereafter, and the positional deviation of the target area of the fundus image with respect to the reference image A fundus photographing apparatus characterized in that a variation in the amount and the distance between the target regions is acquired as the positional deviation information.
  3. 3. The fundus imaging apparatus according to claim 2, wherein the illumination optical system includes a scanning unit that scans a laser beam emitted from a light source as the illumination light on the fundus, and the alignment unit is configured to scan the scanning unit based on the positional deviation information. A fundus imaging apparatus for performing alignment of a fundus image displayed on the monitor by performing control for changing a scanning range on the fundus of the eye to be examined.
  4. 4. The fundus imaging apparatus according to claim 3, wherein the illumination optical system includes a focusing lens for focusing on the fundus of the eye to be examined, and the alignment control unit moves the focusing lens in an optical axis direction based on the positional deviation information. A fundus photographing apparatus, wherein the fundus photographing apparatus is driven.
  5. The fundus imaging apparatus according to claim 4 further receives interference light obtained by combining reference light generated by light emitted from a light source and fundus reflected light by the measurement light irradiated on the eye fundus to be examined. A fundus imaging apparatus having an interference optical system for obtaining a tomographic image of the fundus of the eye to be examined.
  6. 6. The fundus imaging apparatus according to claim 5, further comprising switch means for determining timing for setting the reference image.
JP2008176151A 2008-07-04 2008-07-04 Ocular fundus photographic apparatus Pending JP2010012109A (en)

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