JP5545629B2 - Ophthalmic imaging equipment - Google Patents

Ophthalmic imaging equipment Download PDF

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Publication number
JP5545629B2
JP5545629B2 JP2010011355A JP2010011355A JP5545629B2 JP 5545629 B2 JP5545629 B2 JP 5545629B2 JP 2010011355 A JP2010011355 A JP 2010011355A JP 2010011355 A JP2010011355 A JP 2010011355A JP 5545629 B2 JP5545629 B2 JP 5545629B2
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light
eye
optical
photographing
fundus
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JP2011147609A (en
JP2011147609A5 (en
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成治 瀧
幸雄 安部
弘敬 中西
俊夫 村田
康寛 古内
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株式会社ニデック
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Priority claimed from US13/009,940 external-priority patent/US7980696B1/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]

Description

  The present invention relates to an ophthalmologic photographing apparatus that obtains a photographed image of a subject's eye.

  A light receiving element that projects at least a part of light emitted from the light source toward a predetermined part of the subject's eye through an inspection window through which the subject's eye looks, and receives reflected light from the predetermined part of the subject's eye There is known an ophthalmologic photographing apparatus having a photographing optical system that receives light and obtains a photographed image of a subject's eye. As such an apparatus, a laser scanning ophthalmoscope (SLO), an optical coherence tomography (OCT), a fundus camera, and the like are known.

  In the apparatus as described above, an optical adapter is attached to the examination window according to the imaging purpose, thereby changing the focal position according to the imaging region (for example, the fundus to the anterior eye), imaging magnification / imaging image. The corner can be changed (see, for example, Patent Document 1).

JP-A-6-245906

  However, in such a device as described above, there is a case where satisfactory photographing cannot be performed because the adapter is not sufficiently attached.

  For example, in OCT, when quantitative measurement (for example, corneal thickness measurement, corner angle measurement) of an anterior segment tomogram is performed using an adapter, the optical system of the apparatus main body and the adapter are not mounted when the adapter is tilted. The scanning range of the measurement light changes due to the optical axis deviation from the lens system, and an error may occur in the result of quantitative measurement.

  In view of the above problems, an object of the present invention is to provide an ophthalmologic photographing apparatus capable of photographing a good image when using an adapter.

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

(1)
A light receiving element that projects at least a part of light emitted from the light source toward a predetermined part of the subject's eye through an inspection window through which the subject's eye looks, and receives reflected light from the predetermined part of the subject's eye In an ophthalmologic photographing apparatus having a photographing optical system that receives a light and obtains a photographed image of a subject's eye,
Comprising a mounting state detecting means for detecting a mounting state of an optical adapter mounted on the inspection window ;
The mounting state detection means includes suitability detection means for detecting whether or not the optical adapter is properly attached to the inspection window.
Informing means for informing the detection result by the suitability detecting means,
It is characterized by providing.
(2)
The light emitted from the light source is divided into measurement light and reference light, and the measurement light is guided to the fundus or anterior eye portion of the subject eye through an inspection window through which the subject's eye looks, and the reference light is a reference optical system inside the apparatus. An interference optical system that causes the light receiving element to receive interference light obtained by combining the measurement light reflected by the fundus or anterior eye portion of the eye to be examined and the reference light, and based on the output signal of the light receiving element An ophthalmologic photographing apparatus capable of photographing a tomographic image of the fundus and anterior eye of the subject eye,
A mounting state detecting means for detecting a mounting state of an optical adapter mounted on the examination window in order to switch the imaging part of the subject's eye by the interference optical system ;
Mode setting means that can be set to a fundus photographing mode for photographing a tomographic image of the fundus and an anterior eye photographing mode for photographing a tomographic image of the anterior eye;
Control means for controlling the optical arrangement of the interference optical system in accordance with the photographing mode set by the mode setting means;
It is characterized by providing.
(3)
The light emitted from the light source is divided into measurement light and reference light, and the measurement light is guided to the fundus or anterior eye portion of the subject eye through an inspection window through which the subject's eye looks, and the reference light is a reference optical system inside the apparatus. An interference optical system that causes the light receiving element to receive interference light obtained by combining the measurement light reflected by the fundus or anterior eye portion of the eye to be examined and the reference light, and based on the output signal of the light receiving element An ophthalmologic photographing apparatus capable of photographing a tomographic image of the fundus and anterior eye of the subject eye,
A mounting state detecting means for detecting a mounting state of an optical adapter mounted on the examination window in order to switch the imaging part of the subject's eye by the interference optical system ;
Mode setting means that can be set to a fundus photographing mode for photographing a tomographic image of the fundus and an anterior eye photographing mode for photographing a tomographic image of the anterior eye;
A housing containing the interference optical system;
An electric drive unit for electrically moving the housing;
Control means for controlling the driving of the electric drive unit according to the photographing mode set by the mode setting means;
It is characterized by providing.
(4)
In the ophthalmologic photographing apparatus according to (2) or (3),
The optical adapter has a lens system for switching the imaging site by the interference optical system from the fundus to the anterior segment,
The mode setting means switches from the fundus photographing mode to the anterior eye photographing mode based on an output signal output from the wearing state detecting means when the wearing of the optical adapter is detected, or the wearing of the optical adapter The display device displays a message prompting the user to switch to the anterior ocular segment photographing mode based on an output signal output from the wearing state detecting means when detecting the image .

  According to the present invention, a good image can be taken when the adapter is used.

  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 ophthalmologic photographing apparatus according to 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. Each of the optical systems receives a light projecting optical system that projects at least a part of light emitted from the light source toward a predetermined part of the subject's eye, and receives reflected light from the predetermined part of the subject's eye. And a light receiving optical system that receives light by the element, and is used as a photographing optical system for obtaining a photographed image of the subject's eye. The OCT optical system 200 uses a spectral domain type OCT optical system (of course, a time domain type (TD-OCT) or a swept source domain type (SS-OCT) may be used). The interference optical system 200 and the SLO optical system 300 are built in the housing 100 (see FIG. 2). Further, the housing is moved three-dimensionally with respect to the subject eye E by a well-known alignment moving mechanism (manually or electrically).

  Reference numeral 40 denotes a dichroic mirror as a light splitting member, which reflects measurement light (for example, around λ = 840 nm) emitted from the measurement light source 27 used in the OCT optical system 200 and emits light used in the SLO optical system 300. The laser beam emitted from the unit 61 (light having a wavelength different from that of the light source 27, for example, near λ = 780 nm) is transmitted. 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. The OCT optical system 200 divides the light beam emitted from the light source into a measurement light beam and a reference light beam, guides the measurement light beam to a predetermined part (anterior eye portion or fundus) of the eye to be examined, and guides the reference light beam to the reference optical system. Then, the interference light obtained by combining the measurement light beam reflected from the predetermined part of the eye to be examined and the reference light beam is received by the light receiving element.

  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 optical axis is adjusted in accordance with the refractive error of the eye to be focused for adjusting the end 39b of the optical fiber 38b for emitting the measurement light, the collimating lens 22, and the fundus of the eye to be examined. A focusing lens 24 that can move in the direction, and a scanning unit 23 that is a combination of two galvanometer mirrors that can scan the measurement light in the XY directions on the fundus by driving the scanning drive mechanism 51 are disposed. 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 galvanometer mirror and scanning drive mechanism 51 are disposed in the optical path of the measurement light beam, and change the traveling direction of the measurement light beam in order to scan the measurement light beam in the transverse direction (XY direction) on a predetermined part of the eye to be examined ( Used as an optical scanning unit). The optical scanner uses an acousto-optic device (AOM) that changes the traveling (deflection) direction of light in addition to a mirror.

  The measurement light emitted from the end portion 39b of the optical fiber 38b is collimated by the collimating lens 22, and then 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 and then condensed on the fundus of the eye to be examined via the dichroic mirror 91 and the objective lens 10.

  Then, the measurement light reflected by the fundus is reflected by the dichroic mirror 40 via the objective lens 10 and the dichroic mirror 91, travels toward the OCT optical system 200, and is provided with the two galvanometer mirrors of the scanning unit 23, the focusing lens 24, and the collimator. The light enters the end 39b of the optical fiber 38b through the lens 22. 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 84a 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 (diffraction grating) 81, a condensing lens 82, and a light receiving element 83. It is composed of. 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 converted into parallel light by the collimator lens 80, and then split into frequency components by the grating 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 (A scan signal) 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 roughly 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 fundus reflection light illuminated by the illumination optical system by a light receiving element, and receives light output from the light receiving element. A front image of the fundus of the eye to be examined is obtained based on the signal.

  The light emitting unit 61 includes a first light source (SLO light source) 61a that emits light having an infrared wavelength (for example, λ = 780 nm) and a second light source that emits light having a visible wavelength (for example, λ = 630 nm). (Fixation light source) 61b, mirror 69, and dichroic mirror 101. Note that a light source (laser diode light source, SLD light source, or the like) that emits light with high luminance and high directivity is used for the first light source 61a and the second light source 61b. The infrared light emitted from the first light source 61 a passes through the dichroic mirror 101 and proceeds to the beam splitter 62 via the collimator lens 65. The visible light emitted from the second light source 61b is bent by the mirror 69, then reflected by the dichroic mirror 101, and coaxial with the light emitted from the first light source 61a. The first light source 61a is used to obtain a frontal fundus image for observation, and the second light source 61b is used to guide the line-of-sight direction of the eye to be examined.

  A collimating lens 65, a focusing lens 63 movable in the optical axis direction according to the refractive error of the eye to be examined, and a scanning drive mechanism 52 are provided in an optical path for emitting laser light emitted from the light emitting unit 61 toward the eye E to be examined. A scanning unit 64 composed of a combination of a galvanometer mirror and a polygon mirror capable of scanning the measurement light in the XY directions on the fundus at high speed by driving and the objective lens 10 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 light emitting unit 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 or fixation light beam) emitted from the light emitting unit 61 passes through the beam splitter 62 through the collimating lens 62 and then reaches the scanning unit 64 through the focusing lens 63. The reflection direction is changed by driving the galvanometer mirror and the polygon mirror. Then, the laser light reflected by the scanning unit 64 passes through the dichroic mirror 40 and then is condensed on the fundus of the eye to be examined through the dichroic mirror 91 and the objective lens 10.

  The laser light (measurement light) reflected from the fundus is reflected by the beam splitter 62 via the objective lens 10, the dichroic mirror 91, 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.

<Alignment index projection optical system>
A projection optical system 150 having an infrared light source 151 and projecting an alignment index onto the subject's eye is disposed outside an inspection window (view window) 160 provided in the apparatus housing 100 and is oblique to the eye E. An index is projected from the front (objective lens 10) (see the external view of the main part in FIG. 2A).

  More specifically, a plurality of infrared light sources 151 are arranged at 45 degree intervals on a concentric circle with the photographing optical axis L1 as the center. For convenience, FIG. 1 shows infrared light sources 151 (0 degrees and 180) arranged symmetrically with respect to a vertical plane passing through the photographing optical axis L1.

  When the adapter 500 is not attached, the light source 151 emits a light beam from an oblique direction toward the anterior eye portion to be examined. When infrared light is emitted from each infrared light source 151, a bright spot arranged in a ring shape is formed in the anterior eye portion of the eye E. The projected index image is displayed on the monitor 75 together with the anterior segment image, and is used when the examiner positions the eye E. Note that the projection optical system 150 is also used as anterior segment illumination for illuminating the anterior segment of the eye E. The anterior segment illumination may be provided with a dedicated light source.

<Anterior segment observation optical system>
An observation optical system 90 arranged for imaging the eye E and obtaining an anterior eye image includes an objective lens 10, a dichroic mirror 91, an imaging lens 95, and a two-dimensional image sensor (two-dimensional light receiving element) 97. The dichroic mirror 91 has a characteristic of reflecting light having a wavelength emitted from the infrared light source 151 and transmitting other light.

  The anterior ocular segment reflected light and the alignment light beam from the infrared light source 151 are reflected by the dichroic mirror 91 via the objective lens 10 and then received by the two-dimensional imaging element 97 via the imaging lens 95. The output of the two-dimensional image sensor 97 is transmitted to the control unit 70, and the anterior segment image captured by the two-dimensional image sensor 97 is displayed on the monitor 75 (see FIG. 3).

  The projection optical system 150 and the observation optical system 90 are also used as a detection optical system that optically detects the mounting state of an anterior eye adapter 500 described later. In addition, the detection optical system in the present embodiment is configured to detect whether the adapter 500 is attached and detached and whether the adapter 500 is properly attached to the inspection window 160.

  FIG. 2B is a view showing a state in which an anterior eye adapter (hereinafter referred to as an adapter) 500 is mounted on the examination window 150. The adapter 500 is attached to the examination window 160 when photographing the anterior eye part, and has a lens system that moves the focus position of the measurement light with respect to the eye to be examined from the fundus to the anterior eye part. As a result, the aforementioned OCT optical system 200 and SLO optical system 300 are switched from the fundus imaging optical system to the anterior segment imaging optical system.

  The inspection window 160 is provided with a groove 162, and a convex portion (not shown) of the adapter 500 and the groove 162 are fitted to each other, and the rotation of the adapter 500 is restricted. The examiner pinches the chuck portions 520 provided on the left and right sides, and attaches the adapter 500 so that the convex portion 522 provided at the tip of the chuck portion 520 fits into the concave portion 165 of the inspection window 520 (see FIG. 4). As a mechanism for attaching the adapter 500, various modifications such as a mechanism using a screw and a mechanism using a magnet can be considered. In the present embodiment, the mechanism as shown in FIG. 4 is used so that the adapter 500 can be attached and detached smoothly.

  FIG. 5 is an optical side view for explaining the internal configuration of the adapter 500. The adapter 500 is a flat plate 515 on which a lens system 510 for shifting the focal position to the apparatus side so that the focus is on the anterior eye part and a mirror surface (light reflecting member) 515a for detecting the mounting state are formed. (See the front view of FIG. 6).

  The lens system 510 is a lens system having a focal length corresponding to an appropriate working distance WD between the adapter 500 and the anterior eye portion to be examined, and the main measurement light scanned in the transverse direction on the anterior eye portion. The light beam and the optical axis L1 are configured to be parallel. The lens system 510 may be configured by a single lens or may be configured by a plurality of lenses.

  When an anterior segment tomogram is taken in the present embodiment, the focusing lens 24 is moved to a predetermined position (for example, + 10D position) in the plus diopter direction, and the focus position of the measurement light by the OCT optical system 200 is the apparatus side. Moved to. That is, the apparatus is in a state in which the measurement light can be focused on the anterior segment by attaching the adapter 500 and adjusting the position of the focusing lens 24 to the plus side. At the time of shooting, the working distance (front-rear distance) of the apparatus with respect to the eye E is adjusted, and then focusing on the anterior eye part is performed.

  The control unit 70 is connected to the display monitor 75 and controls the display image. Further, the control unit 70 moves a memory (storage unit) 72, an operation unit 74 for performing various operations, a scanning drive mechanism 51, a scanning drive mechanism 52, a reference mirror drive mechanism 50, and a focusing lens 63 in the optical axis direction. A first drive mechanism 63a for moving the focusing lens 24 and a second drive mechanism 24a for moving the focusing lens 24 in the optical axis direction are connected. Note that the monitor 75 may be different for alignment observation and captured image observation, and of course, may be one common monitor.

  Here, the control unit 70 forms a fundus tomographic image by image processing based on the light reception signal output from the light receiving element 83, and forms a fundus front image by image processing based on the light reception signal output from the light receiving element 68. Let it form.

  In addition, this apparatus has a fundus photographing mode for capturing a tomographic image and a front image of the fundus of the eye to be examined without the adapter 500, and an anterior eye photographing for capturing a tomographic image and a front image of the anterior eye of the eye to be examined using the adapter 500. The mode can be set. When the mode switching signal is output, the control unit 70 switches the optical arrangement of the apparatus, the display screen of the monitor, and the like according to the shooting mode.

<Optical detection of adapter 500 attached state>
In this case, at least two of the infrared light sources 151 are also used as a detection light source that emits a detection light beam toward the mirror surface 515a, and the image sensor 97 receives a reflection light beam from the mirror surface 515a. The control unit 70 detects the mounting state of the adapter 500 based on the light reception signal output from the image sensor 97.

  FIG. 7 is a diagram for explaining the operation of the mirror surface 515 a provided on the adapter 500. When the adapter 500 is mounted, light emitted from two light sources arranged in the diagonally downward right direction and the diagonally downward left direction of the infrared light source 151 is an opening (hole) 517 formed in the adapter 500. Is reflected by the mirror surface 515a. The reflected light is reflected by the dichroic mirror 91 via a part of the lens system 510 and the objective lens 10, and then received by the two-dimensional image sensor 97 via the imaging lens 95. Thereby, bright spots (reflected images) KR and KL by the mirror surface 515 a are formed on the image sensor 97.

  FIG. 8 is a diagram illustrating differences in captured images output from the image sensor 97 according to the mounting state of the adapter 500. FIG. 8A shows an image acquired when the adapter 500 is properly attached. FIG. 8B is an image when the adapter 500 is mounted at an angle. FIG. 8C is a diagram when the adapter 500 is not attached.

  Frames (adapter detection frames) FR / FL formed at the lower right corner and the lower left corner of the captured image are regions that are virtually set to detect the mounting state of the adapter 500.

  When the adapter 500 is properly mounted, both the bright spots KR / KL are detected at predetermined positions in the frame FR / FL as shown in FIG. When the adapter 500 is mounted in an inclined state, the mirror surface 515a is inclined with respect to an appropriate position. Therefore, as shown in FIG. 8 (b), at least one of the bright spots KR / KL has a frame FR / Although it is located in the FL, it is detected at a position deviating from the predetermined position. When the adapter 500 is not attached, as shown in FIG. 8C, both the bright spots KR / KL are detected (or not detected) at positions deviating from the frame FR / FL.

  Therefore, the present apparatus detects attachment / detachment of the adapter 500 based on the imaging signal output from the imaging element 97 and also detects whether the adapter 500 is properly attached. (Details will be described later). As the previous stage, first, the detection position of the bright spot KR / KL on the captured image when the adapter 500 is properly attached is stored in the memory 72 in advance. Further, the position and size of the frame FR / FL are set in advance based on the positions of the bright spots KR / KL when the adapter 500 is properly attached and when the adapter 500 is not properly attached. The above steps may be performed, for example, at the timing of device calibration.

<Determination of wearing state>
Hereinafter, a method for detecting whether or not the apparatus is suitable will be described with reference to the flowchart of FIG. First, the control unit 70 extracts the bright spot KR / KL by image processing using the diameter / luminance level of the bright spot KR / KL, and detects the center position of the extracted bright spot KR / KL.

  Next, the control unit 70 determines that the adapter 500 is not attached if either one of the bright spots KR / KL is not inside the frame FR / FL, and if it is inside the frame FR / FL. It is determined that the adapter 500 is attached. Then, the control unit 70 determines that the adapter 500 is properly mounted if both the detection positions of the bright spots KR / KL match the positions stored in the memory 72 in advance, and if they do not match. Then, it is determined that the adapter 500 is mounted at an angle (the mounting is not appropriate).

  Here, the control unit 70 continuously determines the mounting state of the captured image output from the image sensor 97 as needed at a predetermined frame rate as described above. If the determination is the same for five consecutive times, the determination result is confirmed and displayed on the monitor 75 (end of determination processing). On the other hand, if the same determination is not obtained five times in succession, the detection process of the adapter 500 is temporarily terminated without displaying the determination result. In this case, the determination result before the start of the detection process is reflected.

  Here, when the determination result that the adapter 500 is not properly mounted is determined, the control unit 70 outputs a detection signal that the adapter 500 is not properly mounted, and the adapter 500 is mounted based on the detection signal. Is displayed on the monitor 75. In this case, the examiner attaches the adapter 500 again.

  On the other hand, when the determination result that the adapter 500 is properly mounted is confirmed, the control unit 70 outputs a detection signal that the adapter 500 is properly mounted, and the fundus imaging mode is based on the detection signal. A mode switching signal for switching to the anterior ocular segment imaging mode is issued.

  Note that the control unit 70 detects the mounting state as described above at a constant cycle (for example, every second).

  As described above, whether or not the adapter 500 is attached is detected and the detection result is notified, thereby preventing the anterior segment image from being captured when the adapter 500 is not properly attached. Further, in the above configuration, the projection optical system 150 and the observation optical system 90 are used for detecting whether or not the adapter 500 is attached, so that it is not necessary to provide dedicated detection means.

  In the above configuration, the installation position and reflection angle of the mirror surface 515a are set so that the bright spots KR / KL when the adapter 500 is mounted are formed at the end of the image pickup surface of the image pickup element 97. Is preferred. This is because the corneal bright spot by the infrared light source 151 is not erroneously detected as the bright spot KR / KL. In addition, since the size of the bright spot KR / KL is larger than the corneal bright spot by the infrared light source 151, erroneous detection in image processing can be avoided. The shape of the mirror surface 515a is not limited to a circle, and may be a straight line, a rectangle, or the like.

  In the above configuration, at least two or more light sources that project the alignment index on the anterior eye portion of the subject's eye or illuminate the anterior eye portion of the subject's eye are provided, and at least two of the light sources have detection light sources. What is necessary is just to be combined. In addition, although the mounting state is determined using two bright spots, three or more bright spots may be used.

  The configuration for detecting the mounting state of the adapter 500 is not limited to this. In this case, the detection is not limited to the optical method, but may be electrical or magnetic detection. For example, a photo sensor, a pressure sensor, or the like may be provided in the vicinity of the inspection window 520 (for example, the recess 165). When detecting whether or not the mounting is appropriate, for example, two pressure sensors are provided in the vicinity of the inspection window 520, and when a pressing signal is output from the two pressing sensors, it is detected that the mounting is appropriate, and one pressing is performed. If only the pressing signal from the sensor is used, it may be detected that the mounting is not appropriate.

  In addition, as a configuration for notifying the result of detecting whether or not the adapter 500 is properly installed, in addition to the display on the monitor 75, a dedicated lamp may be turned on or a sound may be used. May be.

  In the above configuration, it is configured to detect whether or not the adapter 500 is properly attached to the inspection window 520. However, even if the adapter 500 attached to the inspection window 520 is simply detected to be attached or detached. Good. In this case, for example, the control unit 70 obtains an image pickup signal from the image pickup element 97, and if both detection positions of the bright spots KR / KL coincide with a predetermined position, the controller 70 detects the attachment of the adapter 500. If not, it detects that the adapter 500 is not attached. The detection result is displayed on the monitor 75, and various settings are changed based on the attachment / detachment detection signal.

  In the above configuration, the lens system 510 of the adapter 500 may be a zoom optical system capable of changing the photographing magnification. Further, in the adapter 500 having the zoom optical system, when the mirror surface 515a as described above is provided, the detection position of the bright spot KR / KL on the image sensor 97 is moved according to the change of the zoom magnification. Therefore, the control unit 70 may determine whether or not the zoom magnification to be changed is appropriate based on the position of the bright spot KR / KL.

  In the above description, the adapter for switching the fundus imaging optical system to the anterior ocular segment imaging optical system has been described as an example. Of course, in the adapter for switching the anterior ocular segment imaging optical system to the fundus imaging optical system. Also, the present invention is applicable. In this case, a lens system for moving the focal position to the subject side so that the focus is on the fundus is used for the lens system of the adapter. In addition to the above fundus imaging apparatus, the present invention can be applied to a fundus camera.

  In addition, the present invention can be applied to other adapters mounted on the examination window of the ophthalmologic photographing apparatus for the above-described attachment / detachment detection. For example, a magnification changing adapter having a lens system for changing the photographing magnification of the subject eye image to be photographed, a wide-angle lens adapter for changing the photographing angle of view, and a vision for correcting the diopter of an eye with abnormal refractive error. A degree correction adapter may be considered.

<Automatic adjustment of optical arrangement when switching modes>
Next, the overall operation of this apparatus will be described. The control unit 70 drives and controls the OCT optical system 200 and the SLO optical system 300 to acquire an OCT image and an SLO image, and updates the OCT image and the SLO image on the monitor 75 as needed (see FIGS. 10 and 11). ).

<Fundus photography mode>
First, the fundus imaging mode will be described. In this mode, adapter 500 is not used. The examiner instructs the subject to gaze at a fixation lamp (not shown), and then performs alignment with the fundus. When the SLO fundus image is displayed on the monitor 75, an OCT image is acquired by the OCT optical system 200 based on a preset scanning pattern, and displayed on the monitor 75 as shown in FIG. . In this case, the control unit 70 controls driving of the driving mechanism 50 based on the light reception signal output from the light receiving element 83 and adjusts the optical path difference between the measurement light and the reference light so that a fundus tomographic image is acquired. . In this case, the reference mirror 31 is moved within a predetermined movement range corresponding to the difference in the axial length of the eye to be examined.

  Thereafter, when a scanning position / pattern desired by the examiner is set and a predetermined trigger signal is output, the control unit 70 acquires a tomographic image based on the set scanning position / pattern, and the acquired image Data is stored in the memory 72. In accordance with this, the control unit 70 stores the fundus front image acquired by the SLO optical system 300 in the memory 72.

<Anterior segment photography mode>
Next, the anterior segment imaging mode will be described. When executing the anterior ocular segment imaging mode, the examiner attaches the adapter 500 to the examination window 160. As described above, the control unit 70 detects whether or not the adapter 500 is attached. When it is detected that the wearing is appropriate and a switching signal for switching from the fundus imaging mode to the anterior segment imaging mode is issued, the control unit 70 causes the OCT optical system 200 and the SLO optical system 300 to operate in the anterior segment imaging mode. The driving mechanism 50, the first driving mechanism 63a, and the second driving mechanism 24a are controlled so as to have a predetermined optical arrangement corresponding to the above, and the position of each optical member is automatically adjusted.

<Optical path length adjustment>
The control unit 70 controls the drive of the drive mechanism 50 based on the mode switching signal, and positions the reference mirror 31 at a predetermined position corresponding to the anterior segment imaging mode. Note that after the movement of the reference mirror 31 is completed, the movement of the reference mirror 31 may be prohibited or the movement range may be limited to a predetermined range.

  The predetermined position of the reference mirror 31 is stored in the memory 72 in advance. Here, the position of the reference mirror is the tomographic image of the anterior segment of the anterior eye in a state where the working distance between the eye to be examined and the apparatus (OCT optical system 200) is adjusted so that the focus of the measurement light is on the anterior segment of the eye E It is preferable that is a position where can be acquired.

  For example, after adjusting the working distance, the optical path difference between the measurement light and the reference light is adjusted so that an anterior tomogram (see cornea C in the figure) is acquired at a predetermined depth position, and the position at that time Is stored in the memory 72. These are obtained by simulation or experiment.

  If it does as mentioned above, it can avoid that an anterior ocular segment tomogram is acquired by the movement of reference mirror 31 in the state where the focus of measurement light is not enough in focus to the anterior segment of eye E. Further, in the automatic optical path length adjustment, it is possible to avoid erroneously detecting the interference light between the reflected light from the lens system 510 of the adapter 500 and the reference light.

  When the predetermined position of the reference mirror 31 is moved, a sensor (an encoder, a potentiometer, or the like) that detects the position of the reference mirror 31 is provided, and the reference mirror is stored at a predetermined position stored in the memory 72 based on a detection signal from the sensor. 31 is moved. In addition, a sensor (for example, a photo sensor) is provided at a position corresponding to a predetermined position within the moving range of the reference mirror 31, and when the sensor detects that the reference mirror 31 is positioned at the predetermined position, The movement may be stopped.

  In the above configuration, the optical path length of the reference light is changed to adjust the optical path difference between the measurement light and the reference light. However, the present invention is not limited to this, and the optical path length of the optical path length of the measurement light is changed. You may make it do. For example, the end portions of the collimator lens 22 and the optical fiber 39b may be moved in the optical axis direction.

  The predetermined position of the reference mirror 31 described above may be set to a position where acquisition of a tomographic image of the lens system 510 by interference light between the measurement light reflected by the lens system 510 and the reference light may be avoided. Good. In this case, the position where the tomographic image of the lens system 510 is acquired is obtained in advance, and the movement range of the reference mirror 31 avoiding this may be set as the predetermined position.

  In this case, when the mode is switched to the anterior ocular segment imaging mode and a drive command signal is output to the drive mechanism 50, the control unit 70 is within a movement range set to avoid acquisition of a tomographic image of the lens system 510. When the reference mirror 31 is moved and the acquisition of the tomographic image is acquired, the movement of the reference mirror 31 is stopped.

<Focus adjustment>
In the OCT optical system 200, the control unit 70 controls the driving of the second drive mechanism 24a, and positions the focusing lens 24 at a predetermined position corresponding to the anterior ocular segment imaging mode. When the focusing lens 24 reaches a predetermined position, the control unit 70 prohibits driving of the second drive mechanism 24a.

  The predetermined position of the focusing lens 24 is stored in the memory 72 in advance. The position of the focusing lens 24 is a position where the focus of the measurement light is focused on the anterior eye part and the principal ray of the measurement light toward the anterior eye part and the optical axis L1 are parallel at a set predetermined proper working distance. Is preferred. The position is stored in the memory 72. These are obtained by simulation or experiment. As a method for positioning the focusing lens 24 at a predetermined position, a method similar to that for the reference mirror 31 can be used.

  In the SLO optical system 300, the control unit 70 controls the driving of the first drive mechanism 63a, and moves the focusing lens 63 to a predetermined position corresponding to the anterior ocular segment imaging mode, as in the OCT optical system 200. Note that the method for setting the moving position of the focusing lens 63 may be set in the same manner as in the case of the OCT optical system 200, and thus the description thereof is omitted.

  When the mode switching signal is issued, the control unit 70 controls the display on the monitor 75 and changes the display screen from the fundus imaging to the anterior eye imaging.

  The controller 70 displays a plurality of anterior segment imaging scanning patterns (for example, a corneal line scan, a corneal cross scan, a corner line scan, etc.) prepared in accordance with the imaging region in a selectable manner. The display of the range is switched from the view angle unit (for example, 40 °) to the distance unit (for example, 6.0 mm). Further, the control unit 70 displays that the movement of the focusing lenses 24 and 63 is prohibited, prohibits the driving of the first drive mechanism 63a and the second drive mechanism 24a, and actually moves each lens. Ban. Thereby, the positions of the lenses 24 and 63 are fixed at predetermined positions.

  In addition, the examiner instructs the subject to gaze at a fixation lamp (not shown), and then performs alignment with the anterior segment. Here, the examiner moves the apparatus housing 100 in the front-rear direction so as to focus on the SLO image on the monitor 75, and adjusts the working distance of the housing 100 with respect to the eye to be examined. The examiner may adjust the working distance so that the OCT image is correctly displayed.

  In some cases, it may be necessary to secure a working distance between the device and the eye E so that the anterior eye portion is in focus (for example, a treatment such as increasing the thickness of a forehead provided in the device). In this case, an electric drive unit that electrically moves the housing 100 is provided, and the control unit 70 controls driving of the electric drive unit based on the above-described mode switching signal, and performs predetermined front-rear operations corresponding to anterior segment imaging. You may make it move the housing | casing 100 toward a position.

  As described above, when the alignment with respect to the anterior segment is completed, an anterior segment tomogram is acquired by the OCT optical system 200 based on a preset scanning pattern and displayed on the monitor 75 as a moving image (FIG. 11). reference).

  Thereafter, when the scanning position / pattern desired by the examiner is set and a predetermined trigger signal is output, the control unit 70 controls the driving of the scanning drive mechanism 51 based on the set scanning position / pattern, An anterior ocular segment tomographic image is acquired, and the acquired image data is stored in the memory 72. In accordance with this, the control unit 70 stores the anterior ocular segment front image acquired by the SLO optical system 300 in the memory 72.

  As described above, the anterior segment imaging can be performed smoothly by changing the settings corresponding to the anterior segment imaging mode based on the detection signal for detecting attachment / detachment of the adapter 500.

  The control unit 70 determines a tomographic image captured in the fundus imaging mode as a fundus image and a tomographic image captured in the anterior segment imaging mode as an anterior eye image, and associates the determination result with the tomographic image. It is preferably stored in the memory 72.

  If the adapter 500 is removed from the apparatus after the anterior segment image is captured as described above, both the bright spots KR / KL detected at the predetermined positions disappear from the imaging surface of the image sensor 97. . Here, in the determination of the mounting state of the adapter 500 described above, when it is determined that both of the bright spots KR / KL detected at the predetermined position disappear from the inside of the frame FR / FL and the adapter 500 is not mounted. The separation of the adapter 500 from the examination window 160 is detected, and a switching signal for switching from the anterior ocular segment imaging mode to the fundus imaging mode is issued.

  When the switching signal is issued, the control unit 70 controls the driving mechanism 50, the first driving mechanism 63a, and the second driving mechanism 24a so that the OCT optical system 200 and the SLO optical system 300 have an optical arrangement corresponding to the fundus imaging mode. The drive is controlled and the position of each optical member is automatically adjusted. In this case, the reference mirror 31 and the focusing lenses 24 and 63 are moved to predetermined origin positions.

  Further, when the switching signal described above is issued, the control unit 70 controls the display on the monitor 75 and changes the display screen from imaging for the anterior segment to imaging for the fundus.

  More specifically, the control unit 70 displays each of a plurality of fundus photographing scan patterns (for example, line scan, cross scan, radial scan, etc.) so that it can be selected and displays the scan range as a distance. The unit is switched from the unit (for example, 6.0 mm) to the angle of view unit (for example, 40 °). Further, the control unit 70 displays that the movement of the focusing lenses 24 and 63 is permitted, and actually permits the movement of the lenses.

  In addition, when performing change control corresponding to an anterior ocular segment imaging mode based on a detection signal generated when the adapter 500 is attached, the present invention is not limited to the above method. For example, the control unit 70 displays on the monitor 75 a message that prompts the user to switch to the anterior ocular segment imaging mode (for example, asks whether or not to shift to the anterior ocular segment imaging mode). The above-described change control may be performed based on the selection signal.

  In the above configuration, the optical arrangement of at least one of the OCT optical system 200 and the SLO optical system 300 based on the mode switching signal for switching from the fundus imaging mode to the anterior ocular segment imaging mode, even if the adapter 500 is not detected. The control is not limited to this as long as the control is adjusted. For example, adjustment control is automatically performed based on a switching signal output from a predetermined mode switch.

  In the above configuration, the optical arrangement is adjusted based on the mode switching signal. However, the optical arrangement is adjusted based on the drive command signal when shooting in the anterior segment imaging mode. I just need it. For example, the adjustment may be started based on an operation signal from the operation unit 74 after the transition to the anterior ocular segment photographing mode. In addition, an alignment detection optical system that detects the working distance of the apparatus with respect to the eye to be examined is provided, and when it is detected that the proper working distance has been reached based on the detection signal, automatic adjustment of the reference mirror 31 for obtaining a tomographic image May be performed.

  In addition, with regard to the automatic adjustment of the optical arrangement at the time of switching the mode, the focal position of the measurement light is not changed by inserting / removing the lens system inside the apparatus, but not by an apparatus that obtains a tomographic image of the fundus and anterior eye by attaching the adapter 500. The present invention can also be applied to an apparatus having a configuration that switches between the eye and the fundus.

It is a figure which shows the optical system and control system of the ophthalmologic imaging device of this embodiment. It is an external appearance perspective view which shows the state of the inspection window vicinity at the time of the non-mounting | wearing of the adapter and the time of mounting | wearing. It is a figure which shows the anterior ocular segment observation screen on a monitor. It is sectional drawing when an adapter is mounted | worn with the test | inspection window. It is an optical side view explaining the internal structure of an adapter. It is a front view when the flat plate provided in the adapter is seen from the objective lens side. It is a figure explaining the effect | action of the mirror surface provided in the adapter. It is a figure shown about the difference in the picked-up image output from an image sensor according to the mounting state of the adapter 500. FIG. It is a flowchart explaining the detection method of mounting suitability. It is a figure when a fundus front image and a fundus tomographic image are displayed on a monitor. It is a figure in case a front eye part front image and an anterior eye tomogram are displayed on a monitor.

23 Scanning Unit 24 Focusing Lens 24a Drive Mechanism 31 Reference Mirror (Optical Path Length Variable Member)
DESCRIPTION OF SYMBOLS 50 Drive mechanism 51 Scan drive mechanism 70 Control part 75 Monitor 90 Anterior ocular segment observation optical system 97 Image pick-up element 151 Infrared light source 200 Interference optical system (OCT optical system)
300 SLO optical system 500 Adapter 510 Lens system 515a Mirror surface 520 Inspection window

Claims (4)

  1. A light receiving element that projects at least a part of light emitted from the light source toward a predetermined part of the subject's eye through an inspection window through which the subject's eye looks, and receives reflected light from the predetermined part of the subject's eye In an ophthalmologic photographing apparatus having a photographing optical system that receives a light and obtains a photographed image of a subject's eye,
    Comprising a mounting state detecting means for detecting a mounting state of an optical adapter mounted on the inspection window ;
    The mounting state detection means includes suitability detection means for detecting whether or not the optical adapter is properly attached to the inspection window.
    Informing means for informing the detection result by the suitability detecting means,
    An ophthalmologic photographing apparatus comprising:
  2. The light emitted from the light source is divided into measurement light and reference light, and the measurement light is guided to the fundus or anterior eye portion of the subject eye through an inspection window through which the subject's eye looks, and the reference light is a reference optical system inside the apparatus. An interference optical system that causes the light receiving element to receive interference light obtained by combining the measurement light reflected by the fundus or anterior eye portion of the eye to be examined and the reference light, and based on the output signal of the light receiving element An ophthalmologic photographing apparatus capable of photographing a tomographic image of the fundus and anterior eye of the subject eye,
    A mounting state detecting means for detecting a mounting state of an optical adapter mounted on the examination window in order to switch the imaging part of the subject's eye by the interference optical system ;
    Mode setting means that can be set to a fundus photographing mode for photographing a tomographic image of the fundus and an anterior eye photographing mode for photographing a tomographic image of the anterior eye;
    Control means for controlling the optical arrangement of the interference optical system in accordance with the photographing mode set by the mode setting means;
    An ophthalmologic photographing apparatus comprising:
  3. The light emitted from the light source is divided into measurement light and reference light, and the measurement light is guided to the fundus or anterior eye portion of the subject eye through an inspection window through which the subject's eye looks, and the reference light is a reference optical system inside the apparatus. An interference optical system that causes the light receiving element to receive interference light obtained by combining the measurement light reflected by the fundus or anterior eye portion of the eye to be examined and the reference light, and based on the output signal of the light receiving element An ophthalmologic photographing apparatus capable of photographing a tomographic image of the fundus and anterior eye of the subject eye,
    A mounting state detecting means for detecting a mounting state of an optical adapter mounted on the examination window in order to switch the imaging part of the subject's eye by the interference optical system ;
    Mode setting means that can be set to a fundus photographing mode for photographing a tomographic image of the fundus and an anterior eye photographing mode for photographing a tomographic image of the anterior eye;
    A housing containing the interference optical system;
    An electric drive unit for electrically moving the housing;
    Control means for controlling the driving of the electric drive unit according to the photographing mode set by the mode setting means;
    An ophthalmologic photographing apparatus comprising:
  4. The ophthalmologic photographing apparatus according to claim 2 or 3,
    The optical adapter has a lens system for switching the imaging site by the interference optical system from the fundus to the anterior segment,
    The mode setting means switches from the fundus photographing mode to the anterior eye photographing mode based on an output signal output from the wearing state detecting means when the wearing of the optical adapter is detected, or the wearing of the optical adapter An ophthalmologic photographing apparatus which displays on the monitor that the user is prompted to switch to the anterior ocular segment photographing mode based on an output signal output from the wearing state detecting means when detecting the eye .
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