JP6427224B2 - Ophthalmic imaging device - Google Patents

Description

  The present invention relates to an ophthalmologic imaging apparatus.

  An ophthalmologic imaging apparatus is used to acquire an image of an eye to be examined. As an ophthalmologic imaging apparatus, a slit lamp (slit lamp microscope), a fundus camera, a scanning laser ophthalmoscope (SLO), etc. are known.

  Further, in recent years, a device for imaging the fundus oculi and the anterior segment by using optical coherence tomography (OCT) has appeared (see, for example, Patent Document 1). The OCT apparatus is advantageous in that it can acquire high-resolution images and can acquire tomographic images. A tomogram of an eye to be examined is subjected to various analysis processing and used as a diagnostic material (see, for example, Patent Document 2).

JP, 2011-212432, A JP, 2009-66325, A

  The control function is very important in vision. The adjustment function is a function of changing the refractive power of the eye according to the distance of the object to focus. Changes in the refractive power of the eye are contributed by the lens, zonules and ciliary body. The crystalline lens is a convex lens with variable refractive power. Tin zonules are tissues that connect the lens and the ciliary body. The ciliary body is muscle tissue. When looking close, the ciliary muscle contracts and the chin zonule relaxes, causing the lens to become thicker and to increase its refractive power. On the other hand, when looking at a distance, the ciliary muscle relaxes and the chin zonules become tense, thereby thinning the lens and reducing the refractive power.

  Although the regulation function has such a mechanism, it has been difficult in the prior art to determine structurally whether the tissue involved is functioning properly. For example, it has been difficult to grasp whether the muscle tissue ciliary body has sufficient ability to contract and relax.

  In addition, even if the ciliary body functions properly, the flexibility of the crystalline lens is reduced due to a cataract or the like, or the implanted intraocular lens is not properly positioned. , It is not possible to focus properly. In the prior art, it has been difficult to discern whether such adjustment failure is due to the ciliary body, the zonules or the lens or intraocular lens. For example, in the prior art, the cause of regulatory dysfunction is a decrease in ciliary muscle function due to aging or the like, a relaxation of chin zonules, or a decrease in shape change function (flexibility) of the lens It was difficult to determine if it was.

  An object of the present invention is to provide a technique capable of suitably determining the adjustment function of an eye to be examined.

The ophthalmologic imaging apparatus according to the embodiment includes a first optical system that applies a first adjustment stimulus and a second adjustment stimulus to the subject's eye by changing the visible distance of the target by the subject's eye, and a signal from the light source. A second optical system is divided into light and reference light to detect interference light between signal light and reference light passing through the eye, and a tomogram of the eye is formed based on the detection result of interference light The first tomogram acquired by the tomogram forming unit for the to-be-tested eye in a state in which the first adjustment system is applied by the tomogram forming unit and the first optical system, and the second adjustment By comparing the second tomogram acquired by the tomogram forming unit with respect to the eye to be examined in a state in which stimulation is given, change information indicating a change in a predetermined tissue of the eye to be examined accompanying a change in regulation stimulus possess an analyzing unit that obtains, the analysis unit, the first Acquired by the tomogram forming unit when the optical axis of the imaging system is substantially coincident with the axis of the eye to be examined and the optical axis of the second optical system is disposed at a position where it passes through the predetermined tissue The variation information is acquired by comparing the first tomogram with the second tomogram .

  According to the present invention, it is possible to preferably determine the adjustment function of the eye to be examined.

It is a schematic diagram showing an example of composition of an ophthalmology photographing instrument concerning an embodiment. It is a schematic diagram showing an example of composition of an ophthalmology photographing instrument concerning an embodiment. It is a schematic diagram showing an example of composition of an ophthalmology photographing instrument concerning an embodiment. It is a schematic diagram showing an example of composition of an ophthalmology photographing instrument concerning an embodiment. It is a schematic diagram showing an example of composition of an ophthalmology photographing instrument concerning an embodiment. It is a flowchart which shows the operation example of the ophthalmologic imaging device which concerns on embodiment. It is a schematic diagram for explaining the example of operation of the ophthalmologic photographing instrument concerning an embodiment. It is a schematic diagram for explaining the example of operation of the ophthalmologic photographing instrument concerning an embodiment. It is a schematic diagram for explaining the example of operation of the ophthalmologic photographing instrument concerning an embodiment. It is a schematic diagram for explaining the example of operation of the ophthalmologic photographing instrument concerning an embodiment.

  An ophthalmologic imaging apparatus according to an embodiment will be described with reference to the drawings.

[Appearance configuration]
One example of the appearance of the ophthalmologic imaging apparatus according to the embodiment is shown in FIGS. 1 and 2. The ophthalmologic photographing apparatus 2 is placed on the optometry table 1 whose height can be adjusted. A subject 4 is seated on the optometer chair 3. The subject 4 is disposed toward the front surface 2F of the ophthalmologic imaging apparatus 2. The ophthalmologic imaging apparatus 2 includes a pedestal 5 a, a drive mechanism 5 b, a pair of left and right main bodies 5 L and 5 R, and a face receiver 6. Body parts 5L and 5R are supported by posts 5p and 5q, respectively.

  The face receiver 6 has a pair of left and right columns 6a and 6b. The columns 6a and 6b support the forehead rest 6c. The forehead rest 6c is movable in the front-rear direction. The face receiver 6 further includes a jaw holder 6d. The chin rest 6d is moved vertically by the knob 6e.

  The drive mechanism 5b is provided with an XYZ drive mechanism and a rotational drive mechanism. The XYZ drive mechanism drives the columns 5p and 5q in the horizontal direction (X direction), the vertical direction (Y direction), and the front and back direction (Z direction). The XYZ drive mechanism includes, for example, an actuator such as a pulse motor and a power transmission mechanism such as a feed screw. The rotation drive mechanism performs a swing operation and a tilt operation. The swinging motion is to rotate each of the columns 5p and 5q about its axis (that is, in the horizontal direction). The tilt operation is to tilt each of the columns 5p and 5q. The rotational drive mechanism includes, for example, an actuator such as a pulse motor and a power transmission mechanism such as a gear. The main body portions 5L and 5R are moved in the X direction, the Y direction, the Z direction, and the rotational direction by such a drive mechanism portion 5b.

  The pedestal 5 a is provided with a lever 6 h for performing an operation input to the ophthalmologic imaging apparatus 2. A button 6g is provided at the top of the lever 6h. Moreover, although illustration is abbreviate | omitted, the operation part may be provided also in the back side of the ophthalmologic imaging device 2. FIG.

  A support 7 b for supporting the display unit 7 is provided upright on the pedestal 5 a. Various information is displayed on the screen 7 a of the display unit 7. Further, display portions 7L and 7R are provided on the front surfaces of the left and right main body portions 5L and 5R, respectively. For example, anterior eye images of the left eye and the right eye of the subject 4 are displayed on the left and right display portions 7L and 7R, respectively. The display units 7, 7L and 7R are flat panel displays such as liquid crystal displays. Moreover, although illustration is abbreviate | omitted, the display part may be provided also in the back side of the ophthalmologic imaging device 2. FIG.

[Configuration of optical system]
The optical system provided in the left and right body parts 5L and 5R will be described. FIG. 3 is a top view showing an example of an optical system provided in the right main body 5R. The optical system of the left main body 5L is constructed symmetrically with the optical system of the right main body 5R. The code ER indicates the right eye (right eye) of the subject 4.

  The main body 5 </ b> R is provided with a photographing optical system 10, a measurement optical system 30, a target projection optical system 50, an interference optical system 60, and a fixation optical system 80. In the state shown in FIG. 3, the optical axes of the photographing optical system 10, the measurement optical system 30, and the target projection optical system 50, and the optical axes of the interference optical system 60 and the fixation optical system 80 face in different directions. . The angle between these optical axes is indicated by θ. The angle θ may be fixed or variable.

(Photographing optical system 10)
The photographing optical system 10 is used to photograph an anterior segment of the right eye ER. The imaging optical system 10 includes a prism P, an anterior illumination light source 11, an objective lens 12, relay lenses 13 and 14, an imaging lens 15, and an imaging element 16.

  A plurality of anterior eye illumination light sources 11 are disposed around the optical axis of the photographing optical system 10, and output light for illuminating the anterior eye. The light output from the anterior eye illumination light source 11 is emitted to the right eye ER via the prism P and is reflected by the anterior eye. The reflected light is detected by the imaging element 16 via the prism P, the objective lens 12, the relay lens 13, and the imaging lens 15. The reflected light from the anterior segment passes through beam splitters 38, 24 and 43 described later, and is guided to the imaging device 16. The anterior segment image acquired by the imaging element 16 is displayed on, for example, the display unit 7L.

  A beam splitter 24 is obliquely disposed between the objective lens 12 and the relay lens 13. The light output from the alignment light source 21 passes through the alignment target aperture 22 and the lens 23, is reflected by the beam splitter 24, and is projected onto the anterior segment of the right eye ER via the objective lens 12 and the prism P. . As in the prior art, based on the alignment target image reflected in the anterior segment image, alignment (alignment) of the imaging optical system 10 with respect to the right eye ER is performed.

(Measurement optical system 30)
The measurement optical system 30 optically measures the optical characteristics of the right eye ER. The measurement optical system 30 of this embodiment measures the refractive power of the right eye ER. The measurement optical system 30 includes a measurement light source 31, a collimator lens 32, a ring light transmitting plate 33, a relay lens 34, a ring diaphragm 35, a holed prism 36, beam splitters 37 and 38, and an objective lens 12. The prism P, the reflection mirror 39, the relay lens 40, the movable lens 41, the reflection mirror 42, the beam splitter 43, the imaging lens 15, and the imaging device 16 are provided.

  The light output from the measurement light source 31 is collimated by the collimating lens 32, is converted into a ring-shaped light flux through the ring light transmitting plate 33, and is transmitted through the relay lens 34 and the ring diaphragm 35. The light is reflected by the free prism 36, is reflected by the beam splitter 37, is reflected by the beam splitter 38, and is irradiated to the right eye ER via the objective lens 12 and the prism P.

  The measuring luminous flux having a ring shape in cross section, which has been irradiated to the right eye to be examined ER, is reflected by the fundus and is emitted from the right eye to be examined ER. At this time, the cross-sectional shape of the measurement light beam is deformed due to the influence of the eyeball optical system (cornea, lens, etc.).

  The measurement light beam emitted from the right eye ER passes through the prism P, the objective lens 12, and the beam splitters 38 and 37, passes through the light transmission plate 36a of the perforated prism 36, is reflected by the reflection mirror 39, and is relayed. The light is reflected by the reflecting mirror 42 and the beam splitter 43 via the moving lens 41, and is detected by the imaging device 16 through the imaging lens 15. By analyzing the size and the shape of the cross section of the detected measurement light beam, the sphericity, the degree of astigmatism, the astigmatic axis and the like of the right eye to be examined ER are acquired. This process is performed in the same manner as in the prior art. That is, the ophthalmologic imaging apparatus 2 functions as a refractometer.

(Target projection optical system 50)
The target projection optical system 50 presents various targets to the right eye ER. The target projection optical system 50 includes a target light source 51, a target plate 52, relay lenses 53 and 54, a reflection mirror 55, a beam splitter 38, an objective lens 12, and a prism P. The target plate 52 includes, for example, a turret plate and a transmission liquid crystal display, and is configured to be able to selectively arrange various targets such as a fixation target and a visual target for visual acuity measurement with respect to the optical path. The light output from the target light source 51 is projected onto the fundus of the right eye ER via the above components of the target projection optical system 50.

  The target light source 51 and the target plate 52 are configured to be movable in the optical axis direction of the target projection optical system 50. Thereby, the visual recognition distance of the visual target by the right eye to be examined ER is changed. That is, the target projection optical system 50 can be used to provide a control stimulus to the right eye ER.

(Interference optical system 60)
The interference optical system 60 is used for optical coherence tomography (OCT) measurement of the right eye ER. The interference optical system 60 includes a light source unit 61, an optical fiber 62, a fiber coupler 63, an optical fiber 64, a collimator lens 65, a galvano scanner 66, a beam splitter 67, a focusing lens 68, and a relay lens 69. , Condensing lens 70, prism P, optical fiber 71, collimating lens 72, beam splitter 73, lens 74, first reference mirror 75, lens 76, and second reference mirror 77 , An optical fiber 78, and a detection unit 79.

  The method of OCT measurement applied in this embodiment is arbitrary. When the swept source method is applied, a wavelength swept light source capable of modulating the output wavelength at high speed is used as the light source unit 61, and a photodetector such as a balanced photodetector is used as the detection unit 79. When the spectral domain method is applied, a broadband light source (low coherent light source) is used as the light source unit 61, and a spectroscope for detecting a spectrum is used as the detection unit 79.

  The galvano scanner 66 includes, for example, two reflection mirrors and an actuator that changes the direction of each reflection mirror. Thereby, the galvano scanner 66 scans the right eye ER with light (signal light) passing through it.

  The condenser lens 70 is insertable into and removable from the optical path of the interference optical system 60. The condenser lens 70 is, for example, disposed in the optical path when acquiring an image of the right eye to be examined ER, and is retracted from the optical path when measuring an intraocular distance (e.g., an eye axial length).

  The first reference mirror 75 is disposed at a conjugate position with respect to the first portion of the right eye ER. The first part indicates the part to be the target of OCT measurement, and is, for example, a cornea, ciliary body, or lens. The first reference mirror 75 and the lens 74 are integrally movable in the optical axis direction.

  The second reference mirror 77 is disposed at a conjugate position with respect to the second portion of the right eye ER. The second part indicates the part to be the target of OCT measurement, and is, for example, the retina, choroid or the like. The second reference mirror 77 and the lens 76 are integrally movable in the optical axis direction.

  The light output from the light source unit 61 is guided to the fiber coupler 63 through the optical fiber 62. The fiber coupler 63 splits this light into two.

  The light (signal light) guided to the optical fiber 64 by the fiber coupler 63 is collimated by the collimator lens 65, changed in the traveling direction by the galvano scanner 66, reflected by the beam splitter 67, and focused by the focusing lens 68, relay The right eye to be examined ER is illuminated via the lens 69 (the condenser lens 70) and the prism P. The backscattered light of the signal light from the right eye ER is guided along the same path in the reverse direction and returns to the fiber coupler 63.

  The light (reference light) guided to the optical fiber 71 by the fiber coupler 63 is collimated by the collimator lens 72 and guided to the beam splitter 73. The component (first reference light) transmitted through the beam splitter 73 is collected by the lens 74, reflected by the first reference mirror 75, converted into a parallel light beam by the lens 74, and returned to the beam splitter 73. On the other hand, the component (second reference light) reflected by the beam splitter 73 is collected by the lens 76, reflected by the second reference mirror 77, converted into a parallel light beam by the lens 76, and returned to the beam splitter 73. come. The first reference light and the second reference light (collectively referred to as reference light) combined by the beam splitter 73 return to the fiber coupler 63 through the collimator lens 72 and the optical fiber 71. The optical path of such reference light is called a reference optical path.

  The fiber coupler 63 causes the signal light passing through the right eye ER to interfere with the reference light passing through the reference light path. The interference light includes information on a portion (e.g. ciliary body) of the right eye to be examined ER conjugate to the first reference mirror 75, and information on a portion (e.g. retina) of the right eye to be examined ER conjugate to the second reference mirror 77. Contains information. The interference light is guided to the detection unit 79 via the optical fiber 78. In the case of the swept source method, the detection unit 79 detects the intensity of the interference light. In the case of the spectral domain method, the detection unit 79 detects the spectral distribution of the interference light.

  Although not shown, the interference optical system 60 is provided with an attenuator and a polarization controller. The attenuator is provided, for example, in the optical fiber 71, and adjusts the light amount of the reference light guided to the optical fiber 71. The polarization controller adjusts the polarization state of the reference light guided to the optical fiber 71 by applying stress from the outside to the looped optical fiber 71, for example. In addition to these, various known devices applicable to OCT measurement can be provided in the interference optical system 60.

(Vision optical system 80)
The fixation optical system 80 presents a fixation target to the right eye ER. The fixation optical system 80 includes a fixation light source 81, a beam splitter 82, a collimating lens lens 83, a focusing lens 68, a relay lens 69, and a prism P. The light output from the fixation light source 81 is reflected by the beam splitter 82, is collimated by the collimator lens 83, passes through the beam splitter 67, and passes through the focusing lens 68, the relay lens 69 and the prism P to the right. It is projected onto the fundus of the subject's eye ER.

  Behind the beam splitter 82 of the fixation optical system 80, an imaging device 90 is provided. The imaging element 90 is used to capture an anterior segment of the right eye ER. In addition, since the optical axis of the imaging optical system 10 and the optical axis of the interference optical system 60 point in different directions, the imaging optical system 10 and the imaging device 90 capture the anterior eye portion of the right eye ER from different directions. Do.

[Control system configuration]
A configuration example of a control system of the ophthalmologic photographing apparatus 2 is shown in FIG. 4 and FIG.

(Control unit 100)
The control system of the ophthalmologic imaging apparatus 2 is configured around the control unit 100. The control unit 100 includes, for example, a processor, a storage device, a communication interface, and the like. The storage device stores computer programs and data for control and calculation. The control unit 100 is provided with a main control unit 110 and a storage unit 120.

(Main control unit 110)
The main control unit 110 controls each part of the ophthalmologic imaging apparatus 2. For example, the main control unit 110 includes the anterior ocular segment illumination light source 11, the imaging element 16, the alignment light source 21, the measurement light source 31, the target light source 51, the light source unit 61, the galvano scanner 66, the detection unit 79, and the fixation shown in FIG. The operation of the light source 81, the imaging device 90, etc. is controlled. Although not shown, the main control unit 110 controls the above-mentioned attenuator and polarization controller.

  The main control unit 110 performs movement control of the optical element. For example, the main control unit 110 controls the measurement drive unit 30A to move the measurement light source 31, the collimator lens 32, and the ring light transmitting plate 33 in the optical axis direction. Measurement drive unit 30A includes an actuator such as a pulse motor and a power transmission mechanism. Further, the main control unit 110 moves the movable lens 41 in the optical axis direction by controlling the lens driving unit 41A. The lens drive unit 41A includes an actuator such as a pulse motor and a power transmission mechanism. Further, the main control unit 110 moves the target light source 51 and the target plate 52 in the optical axis direction by controlling the target driving unit 50A. The target drive unit 50A includes an actuator such as a pulse motor and a power transmission mechanism. Further, the main control unit 110 moves the focusing lens 68 in the optical axis direction by controlling the focusing drive unit 68A. The focusing drive unit 68A includes an actuator such as a pulse motor and a power transmission mechanism. Further, the main control unit 110 controls the insertion and removal drive unit 70A to insert and remove the condenser lens 70 with respect to the light path. The insertion and removal drive unit 70A includes an actuator such as a solenoid and a power transmission mechanism. Further, the main control unit 110 moves the lens 74 and the first reference mirror 75 in the optical axis direction by controlling the reference drive unit 70B. Similarly, the main control unit 110 moves the lens 76 and the second reference mirror 77 in the optical axis direction by controlling the reference drive unit 70C. Each of reference driving units 70B and 70C includes an actuator such as a pulse motor and a power transmission mechanism.

  The main control unit 110 performs movement control of the optical system. For example, the main control unit 110 three-dimensionally moves each of the main body units 5L and 5R by controlling the XYZ drive mechanism 130A provided in the drive mechanism unit 5b. The XYZ drive mechanism 130A includes an actuator such as a pulse motor and a power transmission mechanism. Further, the main control unit 110 controls the rotation drive mechanism 130B to rotationally move the main body 5L around the support 5p and rotate the main body 5R around the support 5q. Further, the main control unit 110 tilts the main body portions 5L and 5R by inclining the columns 5p and 5q by controlling the rotation drive mechanism 130B. The rotation drive mechanism 130B includes an actuator such as a pulse motor and a power transmission mechanism. Further, the main control unit 110 controls the optical axis deflection mechanism 130C to interfere with the direction of the optical axis (first optical axis) of the imaging optical system 10, the measurement optical system 30, and the target projection optical system 50. The directions of the optical axes (second optical axes) of the optical system 60 and the fixation optical system 80 are relatively changed. The optical axis deflection mechanism 130C changes one or both of the direction of the first optical axis and the direction of the second optical axis. Thereby, the angle θ shown in FIG. 3 is changed. The optical axis deflection mechanism 130C includes an actuator such as a pulse motor and a power transmission mechanism.

  Further, the main control unit 110 performs a process of writing data in the storage unit 120 and a process of reading data from the storage unit 120.

(Storage unit 120)
The storage unit 120 stores various data. Examples of data stored in the storage unit 120 include image data of an anterior segment image, image data of an OCT image, measurement data of an eye to be examined, and information on an eye to be examined. The subject's eye information includes information on the subject such as patient ID and name, and information on the subject's eye such as identification information of the left eye / right eye.

(Image Forming Unit 150)
The detection unit 79 detects interference light in OCT measurement and outputs a signal. This signal is input to the image forming unit 150. The image forming unit 150 forms image data of a two-dimensional tomogram of the right eye to be examined ER based on the signal from the detecting unit 79. This image formation processing includes noise removal (noise reduction), filter processing, FFT (Fast Fourier Transform), etc., as in the prior art. The image forming unit 150 includes, for example, a hardware circuit and a processor that executes image forming software. In this specification, "image data" and "image" may be regarded as identical.

(Data processing unit 160)
The data processing unit 160 executes various data processing. For example, the data processing unit 160 performs various image processing and analysis processing on the OCT image and the anterior segment image. Examples thereof include luminance correction and dispersion correction. Further, the data processing unit 160 forms a three-dimensional image based on the two-dimensional tomogram formed by the image forming unit 150. The data processing unit 160 includes a processor that executes data processing software. The data processing unit 160 is an example of an “analysis unit”.

  The data processing unit 160 is provided with an image area specifying unit 161, a change information acquisition unit 162, an optical characteristic information acquisition unit 163, an intraocular distance calculation unit 164, and an anterior eye change information acquisition unit 165. There is.

  The ophthalmologic imaging apparatus 2 applies a control stimulus to the subject's eye. The modulation stimulus is visual information provided to the subject eye to exert any regulation power. The ophthalmologic imaging apparatus 2 applies an adjustment stimulus by the target projection optical system 50. More specifically, by moving the target light source 51 and the target plate 52 by the target driving unit 50A, the focus of the eye to be examined is guided to a predetermined position.

  The inspection of this embodiment is performed as follows. First, OCT measurement is performed in a state in which the first adjustment stimulus is applied to the eye to be examined, and a first tomographic image of the eye to be examined is acquired. In addition, OCT measurement is performed in a state where a second adjustment stimulus different from the first adjustment stimulus is applied, and a second tomographic image of the eye to be examined is acquired. The first and second modulation stimuli correspond to different focus positions. For example, the first adjustment stimulus corresponds to the far focus position, and the second adjustment stimulus corresponds to the near focus position. The data processing unit 160 acquires the change of the predetermined tissue of the eye to be examined accompanying the change of the adjustment stimulus by executing the process described below. Information indicating this change is called change information. The predetermined tissue whose change is to be detected is, for example, a tissue relating to regulatory functions such as ciliary body, lens, zonules.

(Image area identification unit 161)
The image area specifying unit 161 analyzes the first tomographic image, and specifies an image area corresponding to a predetermined tissue. Further, the image area specifying unit 161 analyzes the second tomogram and specifies an image area corresponding to a predetermined tissue. When this process is automatically performed, the image area specifying unit 161 determines the image area of a predetermined tissue and the other image area based on the pixel value (luminance value) of the first tomographic image. This processing includes, for example, threshold processing and pattern matching.

  In addition, it is also possible to perform a part of processing manually. In that case, the main control unit 110 causes the display unit 181 to display a tomographic image. The user observes the displayed tomogram, grasps the image area corresponding to the predetermined tissue, and designates this using the operation unit 182. As an example of the designation method, using a pointing device such as a mouse, a plurality of points are input on the outline of the image area corresponding to the predetermined tissue. The image area specifying unit 161 obtains a closed curve connecting a plurality of input points. The closed curve is, for example, a spline curve or a Bezier curve. The area enclosed by the closed curve is the target image area. As another designation method, a contour can be input using a pointing device.

(Change information acquisition unit 162)
The change information acquisition unit 162 compares the image area (first image area) specified for the first tomogram with the image area (second image area) specified for the second tomogram Thus, the change information indicating the change in the form of the predetermined tissue is acquired.

  A change in shape is an example of a change in morphology of a predetermined tissue. In that case, the change information acquisition unit 162 calculates a predetermined evaluation value based on each of the first image area and the second image area, and obtains change information by comparing these evaluation values. As a specific example of this process, the change information acquisition unit 162 determines the thickness, size (area, volume, etc.), perimeter length, etc. of a predetermined tissue based on the contours of the first image area and the second image area. Calculate the evaluation value. Then, the change information acquisition unit 162 obtains a value (difference, ratio, etc.) indicating the difference between the evaluation value of the first image area and the evaluation value of the second image area, and uses this as change information. Alternatively, the change of the evaluation value per unit adjustment amount assumed may be determined by dividing the value indicating the difference by the change amount of the adjustment stimulus (that is, the assumed adjustment amount). In addition, the above inspection may be performed a plurality of times to obtain a statistical value such as an average value or variation. This example is valid for the ciliary body and the lens. In addition, when the chin zonule of thread-like tissue is a predetermined tissue, for example, it is possible to obtain a wire model of an image region corresponding to the chin zonule and compare the shapes. In addition, it is also possible to detect two (or more) feature points of a predetermined tissue and obtain a shape change based on the distance between the feature points.

  As another example of the morphological change of the predetermined tissue, there is a change in the density of the tissue constituting the predetermined tissue. This example is applicable to, for example, the ciliary body. The ciliary body is a muscle tissue composed of many muscle fibers. The change information acquisition unit 162 analyzes each of the first image area and the second image area, and identifies a large number of partial areas corresponding to muscle fibers. Then, the number of partial areas present in a predetermined area area in the first image area and the number of partial areas present in the area area in the second image area are acquired. This process is performed, for example, by labeling. Further, the change information acquisition unit 162 obtains a value (difference, ratio, etc.) indicating the difference in the number, and uses this as change information. This change information indicates the change in density of muscle fibers as the muscle tissue contracts or relaxes. The density change per unit adjustment amount assumed may be determined by dividing the value indicating the difference in the number by the change amount of the adjustment stimulus (that is, the assumed adjustment amount). Further, the above inspection may be performed a plurality of times to obtain a statistical value such as an average value or variation of density change.

(Optical property information acquisition unit 163)
The optical characteristic information acquisition unit 163 analyzes the optical characteristic of the subject eye acquired by the measurement optical system 30. The measurement optical system 30 measures the subject eye in a state in which the first adjustment stimulus is applied to obtain a first measurement value, and the subject eye in a state in which the second adjustment stimulus is applied Measure to obtain a second measurement value. These measurements are taken in parallel or at different times with the OCT measurements. The optical property information acquiring unit 163 acquires information indicating a change in the optical property of the eye to be examined accompanying a change in the adjustment stimulus, based on the acquired first measurement value and the second measurement value. This information is referred to as optical characteristic information.

  The measurement optical system 30 of this embodiment functions as a refractometer that measures the refractive power of the eye to be examined. The optical property information acquiring unit 163 acquires optical property information indicating a change in the adjustment amount of the eye to be examined with a change in the adjustment stimulus based on the first measurement value and the second measurement value of the refractive power of the eye to be examined. . This process is to calculate the difference between the first measurement value and the second measurement value. The actual adjustment amount per unit adjustment amount assumed may be determined by dividing the difference between the two measured values by the change amount of the adjustment stimulus (that is, the assumed adjustment amount). In addition, the above inspection may be performed a plurality of times to obtain a statistical value such as an average value or variation.

  Although the eye refractive power is measured in this embodiment, other optical characteristics of the eye to be examined may be measured. For example, the aberration of the subject's eye can be measured. As an example of a configuration for performing aberration measurement, there is a wavefront sensor described in Japanese Patent Application Laid-Open No. 2001-275972 or the like by the present applicant. The wavefront sensor irradiates a light flux from a point light source to the fundus of the eye to be examined, and analyzes the distribution of a plurality of point images obtained by detecting the reflected light with an area sensor via a Hartmann plate, and aberrations of various orders. It is an apparatus which asks for According to such a wavefront sensor, it is possible to measure not only sphericity and astigmatism but also higher-order aberrations. The optical property information acquiring unit 163 acquires optical property information indicating a change in the aberration of the eye to be examined accompanying a change in the adjustment stimulus based on the first measurement value and the second measurement value for each order of aberration.

(Intraocular distance calculation unit 164)
The intraocular distance calculation unit 164 calculates the distance between any part of the subject's eye based on the information obtained by the OCT measurement. This distance is called intraocular distance. Although the calculation method of the intraocular distance is arbitrary, the following two methods will be described in this embodiment.

  The first intraocular distance calculation method is based on the optical path length difference between the first reference light and the second reference light. The first reference light is a reference light passing through the first reference mirror 75, and the second reference light is a reference light passing through the second reference mirror 77. As described above, the first reference mirror 75 is moved in the optical axis direction together with the lens 74 by the reference driving unit 70B, and the second reference mirror 77 is moved in the optical axis direction together with the lens 76 by the reference driving unit 70C. Thereby, the optical path length of the first reference light and the optical path length of the second reference light are changed.

  Since the reference drivers 70B and 70C operate under the control of the main controller 110, the main controller 110 can recognize the amount of change in the optical path length by each of the reference drivers 70B and 70C. For example, when the actuators of the reference drive units 70B and 70C are pulse motors, the main control unit 110 transmits the operation amount of the pulse motor by one pulse (that is, the unit movement amount of the reference mirror by the pulse motor) to the pulse motor The amount of change in optical path length can be calculated based on the number of pulses. The positions of the first reference mirror 75 and the second reference mirror 77, that is, the optical path length of the first reference light and the second reference light based on the control history (pulse transmission history) for the reference drivers 70B and 70C. The optical path length of the reference light can be obtained.

  The reference drivers 70B and 70C are examples of the "optical path length changer". Although the optical path length of the reference light is changed in this embodiment, the optical path length of the signal light may be changed. The change of the optical path length of the signal light can be performed using, for example, movable corner cubes. In addition, it is also possible to configure so that both the optical path length of the reference light and the optical path length of the signal light can be changed.

  In this method, a tomogram of a first part of an eye to be examined and a tomogram of a second part are acquired by OCT measurement. The two OCT measurements are performed in parallel or at different times. In this embodiment, two reference mirrors 75 and 77 are provided, so that OCT measurement of different parts of the eye can be performed in parallel. Note that by providing three or more reference mirrors and an optical system that splits the optical path of the reference light according to the number thereof, it is possible to configure so that OCT measurement of three or more sites can be performed simultaneously. .

  The OCT measurement of the first part is performed such that the backscattered light of the signal light from the first part and the first reference light effectively interfere with each other. In other words, in the OCT measurement of the first portion, the optical path length between the fiber coupler 63 and the first portion (optical path length of signal light) and the optical path between the fiber coupler 63 and the first reference mirror 75 It is performed so that the length (the optical path length of the first reference light) is made to coincide. That is, in the OCT measurement of the first portion, the first reference mirror 75 is disposed at a position substantially conjugate to the first portion.

  Similarly, the OCT measurement of the second site is performed such that the backscattered light of the signal light from the second site and the second reference beam effectively interfere with each other. In other words, the OCT measurement of the second part is the optical path length between the fiber coupler 63 and the second part (the optical path length of the signal light) and the optical path between the fiber coupler 63 and the second reference mirror 77 It is performed so that the length (the optical path length of the second reference light) is made to coincide. That is, in the OCT measurement of the second part, the second reference mirror 77 is disposed at a position substantially conjugate to the second part.

  The intraocular distance calculation unit 164 calculates the optical path length of the first reference light when the tomogram of the first part is acquired and the second reference light when the tomogram of the second part is acquired. The distance between the first part and the second part is calculated based on the optical path length. This process is performed by calculating the difference between the optical path length of the first reference light and the optical path length of the second reference light.

  As an example of this method, the axial length of the eye to be examined can be obtained. In that case, the first part is set on the front of the cornea, and the second part is set on the surface of the fundus. That is, the first reference mirror 75 is disposed at a position conjugate to the anterior surface of the cornea, and the second reference mirror 77 is disposed at a position conjugate to the surface of the fundus. In this example, a corneal tomogram depicting the cornea and a fundus tomogram depicting the fundus are obtained. The intraocular distance calculation unit 164 measures the position of the first reference mirror 75 (that is, the optical path length of the first reference light) in OCT measurement for acquiring a corneal tomographic image and the OCT measurement for acquiring a fundus tomographic image. The axial length of the subject's eye is calculated on the basis of the position of the second reference mirror 77 (ie, the optical path length of the second reference light). Thus, the method can measure relatively large intraocular distances.

  As another example of the method, the anterior chamber depth can be obtained. In that case, the first part is set on the posterior surface of the cornea and the second part is set on the anterior surface of the lens. That is, the first reference mirror 75 is disposed at a position conjugate to the posterior surface of the cornea, and the second reference mirror 77 is disposed at a position conjugated to the anterior surface of the lens. In this example, for example, a corneal tomographic image depicting the cornea and a crystalline tomographic image depicting the crystalline lens are acquired. The intraocular distance calculation unit 164 measures the position of the first reference mirror 75 (that is, the optical path length of the first reference light) in OCT measurement for acquiring a corneal tomogram and the OCT measurement for acquiring a crystalline lens tomogram The anterior chamber depth is calculated on the basis of the position of the second reference mirror 77 (ie, the optical path length of the second reference light).

  The second intraocular distance calculation method is to analyze one tomographic image to obtain an intraocular distance. In this analysis process, first, an image area corresponding to a first part depicted in a tomogram and an image area corresponding to a second part are specified. This process is performed automatically or partially manually as in the image area specifying unit 161. The intraocular distance calculation unit 164 calculates the distance between the two specified image areas. This process is performed based on the scale preset on the tomogram. Also, this process may include a process of counting the number of pixels existing between two image areas.

  As an example of this method, the anterior chamber depth can be obtained. In this example, only one of the first reference mirror 75 and the second reference mirror 77 is used for OCT measurement (we will use the first reference mirror 75). The first reference mirror 75 is disposed in conjugation at an arbitrary position of the anterior segment. For example, the first reference mirror 75 is disposed conjugately at a position between the posterior surface of the cornea and the anterior surface of the lens. The intraocular distance calculation unit 164 calculates the distance between the image area corresponding to the posterior surface of the cornea and the image area corresponding to the anterior surface of the lens in the tomographic image acquired in this manner. Determine the anterior chamber depth.

(Anterior segment change information acquisition unit 165)
The ophthalmologic imaging apparatus 2 has a function of imaging the anterior segment. The anterior segment imaging is performed using the imaging optical system 10 or the imaging device 90. In this embodiment, the subject eye in a state in which the first adjustment stimulus is applied is photographed to obtain a first anterior segment image, and the object eye in a state in which the second adjustment stimulus is applied. To obtain a second anterior segment image. The anterior segment imaging is performed in parallel with or different from the OCT measurement. The anterior segment change information acquisition unit 165 compares the first anterior segment image and the second anterior segment image to obtain information indicating a change in a predetermined tissue of the anterior segment associated with a change in the adjustment stimulus. get. This information is referred to as anterior segment change information.

  An iris is an example of a predetermined tissue of the anterior segment to be analyzed. The anterior eye segment change information acquiring unit 165 first performs an image area corresponding to a predetermined tissue depicted in the first anterior eye image and an image area corresponding to the predetermined tissue depicted in the second anterior eye image And identify. This process is performed automatically or partially manually as in the image area specifying unit 161. Further, the anterior eye part change information acquiring unit 165 obtains a change in form (a change in pupil diameter, a change in iris pattern, and the like) between the two image areas by comparing the two specified image areas. In addition, it is also possible to obtain a change in the direction of the line of sight of the eye to be examined (a change in the axial direction of the eye) or the like based on the change in the elliptic shape (ellipticity and orientation) of the pupil.

(User interface 180)
The user interface 180 is a man-machine interface used to provide information to an examiner or a subject, and for the examiner or subject to perform an operation or information input. The user interface 180 includes a display unit 181 and an operation unit 182.

(Display section 181)
The display unit 181 includes the display units 7, 7L and 7R described above, a display unit provided on the back side of the ophthalmologic imaging apparatus 2, and the like. When a computer is connected to the ophthalmologic photographing apparatus 2, the display unit 181 may include the display of the computer. The display unit 181 displays information under the control of the main control unit 110.

(Operation section 182)
The operation unit 182 is used to operate the ophthalmologic imaging apparatus 2 and input information. The operation unit 182 includes the lever 6 h and the button 6 g described above, the operation unit on the back side of the ophthalmologic imaging apparatus 2, and the like. When a computer is connected to the ophthalmologic imaging apparatus 2, the operation unit 182 may include an operation device and an input device of the computer. The main control unit 110 receives a signal from the operation unit 182 and executes control.

  Note that the display unit 181 and the operation unit 182 do not have to be configured as separate devices. For example, as in a touch panel, it is possible to use a device in which a display function and an operation function are integrated.

[Operation]
The operation of the ophthalmologic imaging apparatus 2 will be described. An example of the operation of the ophthalmologic imaging apparatus 2 is shown in FIG. Here, the case where the examination of the right eye to be examined ER is performed will be described.

(S1: Alignment)
First, the optical system is aligned with the right eye ER. Specifically, first, the main control unit 110 turns on the anterior ocular segment illumination light source 11 and the alignment light source 21 and starts the operation of the imaging device 16. Thereby, an anterior segment image of the right eye to be examined ER on which the alignment target image is projected is obtained. The main control unit 110 causes the display unit 181 to display the anterior segment image. The user aligns the right eye ER by adjusting the position of the optical system while referring to the position of the alignment target image reflected in the anterior segment image in the same manner as in the prior art. The main control unit 110 may analyze the position of the alignment target image and adjust the position of the optical system to automatically perform the alignment.

  When the control stimulus is also applied to the left subject's eye, alignment of the optical system with the left subject's eye is similarly performed.

  An example of the state in which the alignment is completed is shown in FIG. The symbol O1 indicates the optical axis (first optical axis) of the photographing optical system 10, the measurement optical system 30, and the target projection optical system 50. The code O2 indicates the optical axis (second optical axis) of the interference optical system 60 and the fixation optical system 80. The alignment of the right main body 5R is based on the anterior eye image acquired by the imaging optical system 10 so that the main control unit 110 aligns the first optical axis O1 with the axis of the right eye to be examined ER. It is implemented by controlling 130A and the rotational drive mechanism 130B.

  As shown in FIG. 3, the second optical axis O2 is at an angle θ with respect to the first optical axis O1. The alignment of the second optical axis O2 can also be performed in a state where the position of the first optical axis O1 is fixed. This alignment is performed by the main control unit 110 controlling the optical axis deflection mechanism 130C based on, for example, an anterior segment image acquired by the imaging device 90 and / or a live OCT image obtained by repetitive OCT measurement. Be done.

  When the adjustment stimulus is also given to the left eye to be examined EL, the main control unit 110 executes alignment of the first optical axis O1 of the left main body 5L in the same manner as in the case of the right main body 5R. When the OCT measurement of the left eye to be examined EL is also performed, the alignment of the second optical axis (not shown) of the left main body 5L is performed in the same manner as in the case of the right main body 5L.

  The main control unit 110 causes the display unit 181 to display the anterior segment image acquired as described above. A display example of the anterior segment image in a state in which the alignment is completed is shown in FIG. The main control unit 110 causes the display unit 181 to display the anterior segment image G1 acquired by the imaging optical system 10 and the anterior segment image G2 acquired by the imaging device 90 on the display unit 181. Since the first optical axis O1 substantially coincides with the axis of the right eye to be examined ER, the anterior eye part image G1 is an image obtained by photographing the right eye to be examined ER from the front. Further, since the second optical axis O2 is inclined at an angle θ with respect to the first optical axis O1, the anterior eye part image G2 is an image obtained by photographing the right eye ER obliquely.

  An example of the positional relationship between the first optical axis O1 and the second optical axis O2 when the alignment is completed is shown in FIG. FIG. 9 shows a cross section of the right eye ER. The code E1 represents a cornea, the code E2 represents an iris, the code E3 represents a crystalline lens, the code E4 represents a ciliary body, and the code E5 represents a chin band. The first optical axis O1 passes through the apex of the cornea E1, passes between the irises E2 (pupil), and is disposed at a position passing through the apex of the crystalline lens E3. Further, the second optical axis O2 which is inclined at an angle θ with respect to the first optical axis O1 is disposed at a position passing through the ciliary body.

(S2: application of the first regulatory stimulus)
When the alignment is completed, the main control unit 110 applies a first adjustment stimulus to the right eye ER (and the left eye). Specifically, the main control unit 110 turns on the target light source 51 and controls the target driving unit 50A to arrange the target light source 51 and the target target plate 52 at a position corresponding to the first adjustment stimulus. Let The position of the target light source 51 or the like corresponding to the first adjustment stimulus is preset.

(S3: OCT measurement, optical characteristic measurement, anterior segment imaging)
In a state in which the first adjustment stimulus is applied to the right eye to be examined ER (and the left eye to be examined), the main control unit 110 executes OCT measurement, optical characteristic measurement, and anterior segment imaging. Note that at least two of these three operations may be performed in parallel, or all of them may be performed at different timings. At this stage, the condenser lens 70 is disposed in the optical path of the interference optical system 60.

  The OCT measurement will be described. First, the main control unit 211 controls the reference drive unit 70B to arrange the first reference mirror 75 and the lens 74 at a position corresponding to the ciliary body E4. This process is performed, for example, with reference to a live OCT image obtained by repetitive OCT measurement. When the positioning of the first reference mirror 75 is completed, the main control unit 211 controls the light source unit 61 and the galvano scanner 66 to perform OCT measurement of the area of the right eye ER including the ciliary body. The detection unit 79 detects interference light between the signal light passing through the right eye to be examined ER and the reference light passing through the first reference mirror 75. The image forming unit 150 forms a tomogram based on the signal output from the detecting unit 79. The form of the ciliary body E4 in the state where the first regulation stimulus is given is depicted in this tomogram. The main control unit 110 causes the storage unit 120 to store the acquired tomographic image. This tomogram is used as a first tomogram.

  The optical characteristic measurement will be described. First, the main control unit 110 turns on the measurement light source 31. The measurement light beam output from the measurement light source 31 is reflected by the fundus of the right eye to be examined ER and detected by the imaging device 16. The main control unit 110 sends the signal output from the imaging device 16 to the optical characteristic information acquisition unit 163. This signal includes information indicating the size and the shape of the cross section of the measurement light flux detected by the imaging device 16. The optical property information acquisition unit 163 analyzes the signal to calculate the spherical degree, the degree of astigmatism, the axis of astigmatism, and the like of the right eye ER. The main control unit 110 causes the storage unit 120 to store the calculated measurement value of the optical characteristic. This measurement value indicates the optical characteristic value of the right eye ER when the first adjustment stimulus is applied, and is used as the first measurement value.

  An anterior segment imaging will be described. When the anterior ocular segment illumination light source 11 is continuously lit from Step 1, the imaging element 16 inputs a signal to the control unit 100 at a predetermined time interval (frame rate). The main control unit 110 causes the storage unit 120 to store image data based on a signal input at a predetermined timing (which may be any timing while the first adjustment stimulus is applied). This image data shows the form of the anterior segment of the right eye to be examined ER in a state in which the first adjustment stimulus is applied, and is used as image data of a first anterior segment image.

  When the anterior ocular segment illumination light source 11 is not turned on at least immediately before the anterior ocular segment photographing, the main control unit 110 turns on the anterior ocular segment illumination light source 11 to execute the anterior ocular segment photographing, thereby The storage unit 120 stores the obtained image data of the first anterior segment image.

(S4: application of a second regulatory stimulus)
When the OCT measurement, optical characteristic measurement and anterior segment imaging are completed, the main control unit 110 applies a second adjustment stimulus to the right eye ER (and the left eye). Specifically, the main control unit 110 controls the target driving unit 50A so that the target light source 51 and the target plate 52 disposed at the position corresponding to the first adjustment stimulus are Move to the position corresponding to the regulation stimulus. The position of the target light source 51 or the like corresponding to the second adjustment stimulus is set in advance.

(S5: OCT measurement, optical characteristic measurement, anterior segment imaging)
In a state in which the first adjustment stimulus is applied to the right eye to be examined ER (and the left eye to be examined), the main control unit 110 executes OCT measurement, optical characteristic measurement, and anterior segment imaging. This process is performed in the same manner as step 3. Thereby, a second tomographic image, a second measured value, and a second anterior segment image of the right eye to be examined ER in a state in which the second adjustment stimulus is applied are obtained. These pieces of information are stored in the storage unit 120.

(S6: Movement of the optical system)
When the OCT measurement, optical characteristic measurement, and anterior segment imaging in step 5 are completed, the main control unit 110 moves the optical system to a position for intraocular distance measurement. Specifically, the main control unit 110 controls the rotation drive mechanism 130B so that the optical axis (second optical axis O2) of the interference optical system 60 coincides with the axis of the right eye ER (FIG. 10). reference). The rotational movement of the optical system is to rotate the right main body 5R by an angle θ. Further, the main control unit 110 controls the XYZ drive mechanism 130A to adjust the distance of the interference optical system 60 with respect to the right eye ER. Further, the main control unit 110 controls the insertion and removal drive unit 70A to retract the condensing lens 70 from the optical path of the interference optical system 60.

(S7: OCT measurement for intraocular distance measurement)
When the movement of the optical system is completed, the main control unit 211 controls the reference drive unit 70B to operate the first reference mirror 75 and the lens 74 at the first region of the right eye ER (for example, the front surface of the cornea E1). By setting the second reference mirror 77 and the lens 76 at a position corresponding to the second portion of the right eye ER (for example, the surface of the fundus) by controlling the reference driving unit 70C. Arrange it. This process is performed, for example, with reference to a live OCT image obtained by repetitive OCT measurement. In the OCT measurement, the fixation light source 81 causes fixation of the right eye ER.

  When the positioning of the first reference mirror 75 and the second reference mirror 77 is completed, the main control unit 211 controls the light source unit 61 and the galvano scanner 66 to execute OCT measurement of the right eye ER. The detection unit 79 detects interference light between the signal light and the reference light passing through the right eye to be examined ER. In this interference light, an interference component (first interference component) between the signal light passing through the first part of the right eye to be examined ER and the reference light passing through the first reference mirror 75, and the second part An interference component (second interference component) between the signal light passing through and the reference light passing through the second reference mirror 77 is included.

  The image forming unit 150 forms a tomogram based on the signal output from the detecting unit 79. In this operation example, the image forming unit 150 forms a corneal tomographic image in which the front surface of the cornea E1 is visualized based on the first interference component, and a fundus image in which the surface of the fundus is visualized based on the second interference component. Form a tomogram. The main control unit 110 causes the storage unit 120 to store the acquired corneal tomogram and fundus tomogram. The OCT measurement of the first part and the OCT measurement of the second part may be performed at different timings.

  As described above, the optical measurement on the right eye to be examined ER is completed, and the process shifts to data processing. In addition, the order which performs the process shown to the following step 8-step 11 is arbitrary. It is also possible to execute two or more of these processes in parallel.

(S8: Generation of change information)
The data processing unit 160 generates change information indicating a change in a predetermined tissue (for example, ciliary body) of the right eye ER due to a change in the adjustment stimulus. The change information in this operation example indicates the difference between the form of the predetermined tissue in the state in which the first regulatory stimulus is applied and the form of the predetermined tissue in the state in which the second regulatory stimulus is applied.

  The process of step 8 includes a two-stage process as follows. In the first stage, the image area specifying unit 161 analyzes the first tomogram acquired in step 3 to specify the ciliary body area, and analyzes the second tomogram acquired in step 5 And identify the ciliary region. In the second step, the change information acquisition unit 162 compares the ciliary region of the first tomogram with the ciliary region of the second tomogram to determine the form (shape, muscle, Change information indicating changes in fiber density etc.) is acquired. The main control unit 110 stores the acquired change information in the storage unit 120.

(S9: Generation of optical property information)
The data processing unit 160 generates optical property information indicating a change in the optical property of the right eye ER with the change in the adjustment stimulus. In this operation example, the optical characteristic information acquisition unit 163 changes the adjustment stimulus based on the first measurement value of the eye refractive power acquired in step 3 and the second measurement value acquired in step 5 Optical property information indicating a change in the adjustment amount of the right eye ER with the subject is acquired. The main control unit 110 stores the acquired optical characteristic information in the storage unit 120.

(S10: generation of anterior segment change information)
The data processing unit 160 generates anterior segment change information indicating a change in a predetermined tissue of the anterior segment of the right eye ER with the change in the adjustment stimulus. In this operation example, the anterior segment change information acquisition unit 165 generates a right subject based on the first anterior segment image acquired in step 3 and the second anterior segment image acquired in step 5. The anterior segment change information indicating the change in the pupil diameter of the optometry ER, the change in the iris pattern, the change in the gaze direction, and the like is acquired. The main control unit 110 stores the acquired anterior segment change information in the storage unit 120.

(S11: Calculation of intraocular distance)
The data processing unit 160 calculates the intra-ocular distance of the right eye ER. In this operation example, based on the position of the first reference mirror 75 and the position of the second reference mirror 77 when the intraocular distance calculation unit 164 acquires the corneal tomographic image and the fundus tomographic image in step 7, the right The axial length of the subject eye ER, that is, the distance between the front of the cornea and the surface of the fundus is calculated. The main control unit 110 stores the calculated intraocular distance in the storage unit 120.

(S12: Display of information)
The main control unit 110 reads the information acquired in step 8 to step 11 from the storage unit 120 and causes the display unit 181 to display the information. This is the end of this operation example.

[Operation / effect]
The operation and effects of the ophthalmologic imaging apparatus 2 will be described.

  The ophthalmologic imaging apparatus 2 includes a first optical system, a tomographic image forming unit, and an analysis unit. The first optical system includes a target projection optical system 50 for applying a control stimulus to the subject's eye. The first optical system is an example of a stimulus applying unit that stimulates the subject's eye. The tomographic image forming unit includes an interference optical system 60. The interference optical system 60 corresponds to a second optical system, divides the light from the light source (light source unit 61) into the signal light and the reference light, and the interference light of the signal light and the reference light passed through the eye to be examined To detect. The tomogram forming unit forms a tomogram of the subject's eye based on the detection result of the interference light by the interference optical system 60. The analysis unit is configured to include the data processing unit 160, and the first tomographic image of the eye to be examined in the state in which the first adjustment stimulus is applied and the object in the state in which the second adjustment stimulus is applied. By comparing the second tomogram of the optometry, change information indicating a change in a predetermined tissue of the eye to be examined accompanying a change in the adjustment stimulus is obtained.

  The data processing unit 160 may include an image area specifying unit 161 and a change information acquisition unit 162. The image area specifying unit 161 analyzes each of the first tomogram corresponding to the first adjustment stimulus and the second tomogram corresponding to the second adjustment stimulus, and an image area corresponding to a predetermined tissue of the eye to be examined. Identify The change information acquisition unit 162 compares the image area specified from the first tomogram with the image area specified from the second tomogram to obtain information indicating the change in the form of the predetermined tissue of the eye to be examined. Acquired as the change information.

  The change information acquisition unit 162 can acquire, as the change information, information indicating a change in the shape of the predetermined tissue of the eye to be examined and / or a change in the density of the tissue constituting the predetermined tissue. Thereby, it is possible to grasp how the shape and density of the predetermined tissue change in response to the adjustment stimulus.

  When a ciliary body is applied as a predetermined tissue, it is possible to use the following configuration. The image area specifying unit 161 specifies a ciliary body area corresponding to a ciliary body as the image area. Then, the change information acquisition unit 162 changes the shape of the ciliary body of the subject eye and / or by comparing the ciliary region of the first tomogram with the ciliary region of the second tomogram. Information indicating a change in density of muscle fibers of the ciliary body is acquired as the change information. Thereby, it is possible to grasp how the shape of the ciliary body and the density of muscle fibers change in response to the adjustment stimulus.

  When a ciliary body is applied as a predetermined tissue, the optical axis (first optical axis O1) of the first optical system and the optical axis (second optical axis O2) of the second optical system are in different directions. In the oriented state, it is possible to perform the application of the adjustment stimulus to the eye to be examined and the OCT measurement of the ciliary body. Thereby, it is possible to preferably perform the application of the regulation stimulus and the parallel execution of the OCT measurement of the ciliary body. That is, it is possible to preferably perform OCT measurement from the direction inclined with respect to the eye axis while applying the adjustment stimulus from the front of the eye to be examined.

  When the ciliary body is applied as the predetermined tissue, an optical system moving mechanism that relatively changes the direction of the first optical axis O1 and the direction of the second optical axis O2 can be provided. In this embodiment, the optical axis deflection mechanism 130C corresponds to an optical system moving mechanism. Thereby, it is possible to preferably perform the application of the regulation stimulus and the OCT measurement of the ciliary body. That is, it is possible to preferably perform OCT measurement from a direction suitable for imaging the ciliary body while applying the adjustment stimulus from the front of the eye to be examined.

  The predetermined tissue is not limited to the ciliary body. For example, the lens can be applied as a predetermined tissue. In that case, the following configuration can be used. The image area specifying unit 161 specifies a lens area corresponding to a lens as the image area. And the change information acquisition part 162 acquires the information which shows the change of the shape of a crystalline lens as change information by comparing the lens area of a 1st tomogram, and the lens area of a 2nd tomogram. The change information includes the thickness, size (area, volume, etc.), circumference length, etc. of the lens. Thereby, it is possible to grasp how the shape of the tissue such as the lens changes in response to the adjustment stimulus. In addition, not only a biological lens but also an artificial lens (that is, an intraocular lens) shall be contained in the lens in this embodiment.

  The first optical system may include a pair of left and right optical systems that simultaneously apply a control stimulus to the left eye EL and the right eye ER of the subject. Thereby, the adjustment can be suitably caused as compared with the case where only one subject's eye is subjected to the adjustment stimulus. In addition, when giving an adjustment stimulus to both eyes, it is possible to perform position adjustment of a pair of optical systems on either side so that a to-be-tested eye may converge. At that time, the convergence angle can be configured to be changed according to the adjustment stimulus. As a specific example, a first convergence angle corresponding to a visual recognition distance corresponding to a first adjustment stimulus and a second convergence angle corresponding to a visual recognition distance corresponding to a second adjustment stimulus are acquired in advance, and the adjustment stimulation is It is possible to switch and apply the first convergence angle and the second convergence angle according to the change of.

  The first optical system may include a measurement optical system that optically measures the optical characteristics of the eye to be examined. In this embodiment, the measurement optical system 30 measures the eye to be examined in a state in which the first adjustment stimulus is applied to obtain the first measurement value of the optical property. Furthermore, the measurement optical system measures the subject's eye in a state in which the second adjustment stimulus is applied to obtain a second measurement value of the optical property. The optical property information acquiring unit 163 of the data processing unit 160 acquires optical property information indicating a change in optical property accompanying a change in the adjustment stimulus based on the first measurement value and the second measurement value. Thereby, it is possible to grasp how the optical characteristics of the eye to be examined change in response to the adjustment stimulus.

  The measurement optical system can measure the refractive power of the eye to be examined as the above-mentioned optical characteristic. In that case, the optical property information acquiring unit 163 acquires optical property information indicating a change in the amount of adjustment of the eye to be examined accompanying a change in the adjustment stimulus based on the first measurement value and the second measurement value of the refractive power. be able to. Thereby, it is possible to grasp how the refractive power of the subject's eye changes in response to the adjustment stimulus.

  The measurement optical system can measure the aberration of the eye to be examined as the optical characteristic. In that case, the optical property information acquiring unit 163 may acquire optical property information indicating a change in the aberration of the eye to be examined accompanying a change in the adjustment stimulus based on the first measurement value and the second measurement value of the aberration. it can. Thereby, it is possible to grasp how the aberration of the eye to be examined changes in response to the adjustment stimulus.

  The second optical system may include an optical path length change unit that changes the optical path length of the signal light and / or the reference light. In this embodiment, a reference drive unit 70 B (70 C) for changing the optical path length of the reference light is provided in the interference optical system 60. The tomogram acquisition unit acquires tomograms of the first part and the second part of the eye to be examined. The intraocular distance calculation unit 164 of the data processing unit 160 calculates the optical path length when the tomogram of the first part is acquired and the optical path length when the tomogram of the second part is acquired. The distance between the first part and the second part is calculated. Thereby, the distance between the first part and the second part of the eye to be examined can be determined.

  The anterior surface of the cornea can be applied as the first site and the surface of the fundus can be applied as the second site. In that case, the axial length of the subject's eye can be obtained by the intraocular distance calculation unit 164.

  The intraocular distance calculation unit 164 analyzes the one tomogram of the subject eye acquired by the tomogram acquisition unit to obtain the distance between the first portion and the second portion depicted in the tomogram. Can be calculated. Thereby, the distance between the first part and the second part of the eye to be examined can be determined.

  The posterior surface of the cornea can be applied as the first site and the anterior surface of the lens can be applied as the second site. In that case, the intraocular distance calculation unit 164 obtains the anterior chamber depth of the subject's eye.

  The first optical system may include an imaging optical system for imaging an anterior segment of an eye to be examined. In this embodiment, the imaging optical system 10 and the optical system including the imaging device 90 correspond to the imaging optical system. The imaging optical system includes a first anterior segment image of the subject's eye in a state in which the first accommodation stimulus is applied, and a second front of the subject eye in a state in which the second accommodation stimulus is applied. Acquire an eye image. The data processing unit 160 compares the first anterior segment image with the second anterior segment image to obtain anterior segment change information indicating a change in a predetermined tissue of the anterior segment associated with a change in the adjustment stimulus. get. Thereby, it is possible to grasp how the predetermined tissue of the anterior segment changes in response to the regulation stimulus.

  According to the ophthalmologic photographing apparatus 2 configured as described above, it is possible to determine whether the tissue involved in the adjustment function of the eye to be examined is functioning properly based on the structural change of the eye to be examined. For example, it can be grasped whether the ciliary body which is muscle tissue has sufficient ability to contract and relax. In addition, it can be comprehensively judged whether the ciliary body is functioning properly, the flexibility of the crystalline lens is reduced due to a cataract or the like, and whether the implanted intraocular lens is disposed at an appropriate position. Therefore, it is possible to identify the cause that the regulation function is not working properly.

  As described above, according to the ophthalmologic photographing apparatus 2, it is possible to suitably determine the adjustment function of the eye to be examined.

  The usage form of the ophthalmologic imaging device 2 according to the embodiment will be described. By using the ophthalmologic imaging apparatus 2 for the treatment regarding the adjustment function and the follow-up of the operation, it is possible to comprehensively judge the change of the adjustment function due to the treatment, the operation and the time course. In addition, it is possible to obtain time-series changes of the adjustment function.

  The ophthalmologic imaging apparatus 2 is used to measure the effects of rehabilitation and training. In that case, the target projection optical system 50 can present a target for a subjective eye examination such as a Landolt's ring to the subject's eye. Then, it is possible to acquire time-series changes in the measurement result of the subjective eye examination and the measurement result of the adjustment function.

  The ophthalmologic imaging apparatus 2 is used to evaluate the accommodating intraocular lens. The accommodating intraocular lens is an intraocular lens having an adjusting function. As an example of evaluation of the accommodating intraocular lens, it can be evaluated whether the implanted accommodating intraocular lens is functioning properly according to the movement of the ciliary body or the like. Also, before implanting an intraocular lens, it can be determined whether the ciliary body or the like of the subject's eye has sufficient ability to implant an accommodating intraocular lens.

  The configuration described above is merely an example for implementing the present invention. Therefore, any modification (omission, substitution, addition, etc.) within the scope of the present invention can be appropriately applied. The following modifications are included in the scope of the present invention.

  The wavelength of light output from the light source unit 61 is arbitrarily set. For example, in consideration of measurement of axial length using OCT, a light source unit 61 capable of outputting light of a wavelength of 1.1 μm or less can be used. Note that it is possible to separately provide a light source for OCT measurement for acquiring a tomographic image and a light source for OCT measurement for measuring an intraocular distance.

  In the above embodiment, a configuration is adopted in which the target eye is used to apply the control stimulus to the subject's eye, but the method for applying the stimulus to the subject's eye and the content of the stimulus are not limited thereto. For example, electrical stimulation, ultrasonic stimulation or light stimulation can be applied to the subject's eye. Electrical stimulation is applied, for example, by bringing an electrode into contact with the stimulation site. Ultrasonic stimulation is applied, for example, by irradiating the stimulation site with ultrasonic waves using an ultrasonic transducer. Light stimulation is applied using a light source.

  The site of the eye to which the stimulus is applied is not limited to the site (lens, zonules, ciliary body) related to the regulatory function. For example, a stimulus can be applied to the retina.

  Such an ophthalmologic imaging apparatus includes a stimulus applying unit, a tomogram forming unit, and an analysis unit. The stimulus applying unit stimulates the eye to be examined. The stimulation includes presentation of a target, electrical stimulation, ultrasonic stimulation, light stimulation and the like. The stimulus applying unit includes a unit for presenting a target to the subject's eye, a unit for applying an electrical stimulus to the subject's eye, a unit for applying an ultrasonic stimulus to the subject's eye, and a unit for applying a light stimulus to the subject's eye. The tomographic image forming unit includes an optical system that divides the light from the light source into the signal light and the reference light, and detects the interference light of the signal light and the reference light passing through the eye to be examined. Furthermore, the tomogram forming unit forms a tomogram of the subject's eye based on the detection result of the interference light. The analysis unit is configured to receive the first tomographic image acquired by the tomogram forming unit with respect to the subject's eye in a state in which the first stimulus is given by the stimulus applying unit, and the subject eye in a state in which the second stimulus is given By comparing with the second tomogram acquired by the tomogram formation unit, the change information indicating the change of the predetermined tissue of the eye to be examined accompanying the change of the stimulus is acquired. According to such an ophthalmologic imaging apparatus, it is possible to determine a change in the eye to be examined accompanying a change in stimulation.

  In the above embodiment, change information is acquired based on a tomogram of the eye to be examined, but data detected by an interference optical system in OCT measurement, information from this detection data to a tomogram, or tomogram It is possible to obtain change information based on the information obtained from. For example, in the above embodiment, acquiring change information from the signal output from the detection unit 79 of the interference optical system 60, information acquired by the image forming unit 150 that has received this signal (from signal to tomogram) It is possible to obtain change information from the information in (1), and further to obtain change information from information generated by the data processing unit 160 from a tomogram. Moreover, the structure which acquires change information based on the phase information acquired by phase detection type | mold OCT can also be applied. In that case, a slight change (change below the wavelength) of the eye to be examined accompanying a change in stimulation can be grasped.

  Although the said embodiment demonstrated especially in detail about the case where two information corresponding to two stimulation provision states were compared in detail, it is not limited to this. For example, change information can be obtained from three or more pieces of information corresponding to three or more stimulus application states. That is, acquiring the i-th information (tomographic image etc.) on the subject's eye in a state in which the i-th stimulus (i = 1 to K) is given, and acquiring change information based on the K pieces of information Is possible. In addition, change information can be acquired from three or more pieces of information corresponding to two or more stimulus application states. For example, it is possible to acquire change information based on the information of the eye to be examined repeatedly acquired in the period including the transition from the first stimulus application state to the second stimulus application state. For example, repeatedly acquiring tomograms at a predetermined repetition frequency in a period including transition from the first stimulation state to the second stimulation state, and acquiring change information based on a moving image obtained thereby It is possible.

2 ophthalmologic photographing apparatus 5L, 5R body 10 photographing optical system 30 measurement optical system 30A measurement drive unit 50 target projection optical system 50A target drive unit 60 interference optical system 61 light source unit 66 galvano scanner 70B, 70C reference drive unit 75 1 reference mirror 77 second reference mirror 79 detection unit 80 fixation optical system 100 control unit 110 main control unit 120 storage unit 130A XYZ drive mechanism 130B rotational drive mechanism 130C optical axis deflection mechanism 150 image forming unit 160 data processing unit 161 Image area specification unit 162 Change information acquisition unit 163 Optical property information acquisition unit 164 Intraocular distance calculation unit 165 Front eye change information acquisition unit 181 Display unit 182 Operation unit O1 First optical axis O2 Second optical axis EL Left cover Optometry ER Right eye

Claims (5)

A first optical system that applies a first control stimulus and a second control stimulus to the subject's eye by changing the visual distance of the target by the subject's eye;
The second embodiment includes a second optical system that divides light from a light source into signal light and reference light and detects interference light between signal light and reference light that has passed through the eye to be examined, and based on the detection result of interference light A tomogram forming unit for forming a tomogram of
The first tomogram acquired by the tomogram forming unit and the second adjustment stimulus are applied to the eye to be examined in a state in which the first adjustment stimulus is applied by the first optical system An analysis unit that acquires change information indicating a change in a predetermined tissue of the subject's eye with a change in the adjustment stimulus by comparing the second tomogram acquired by the tomogram forming part with the subject's eye in the state; Yes, and
The analysis unit is disposed at a position where the optical axis of the first optical system substantially coincides with the axis of the eye to be examined and the optical axis of the second optical system passes the predetermined tissue. Acquiring the change information by comparing the first tomogram acquired by the tomogram forming unit with the second tomogram at a time
An ophthalmologic photographing apparatus characterized in that . The ophthalmologic photographing apparatus according to claim 1, further comprising an optical system moving mechanism that relatively changes the direction of the optical axis of the first optical system and the direction of the optical axis of the second optical system. . The ophthalmologic photographing apparatus according to claim 1 or 2, wherein the predetermined tissue includes a ciliary body . Wherein the predetermined tissue ophthalmologic photographing apparatus according to claim 1 or claim 2, characterized in that it comprises a lens. Wherein the predetermined tissue ophthalmologic photographing apparatus according to claim 1 or claim 2, characterized in that it comprises a routine zonule.

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