JP2018175657A - Ophthalmic apparatus, control method therefor, and program - Google Patents

Abstract

The present invention provides a mechanism capable of reducing an operation load on an examiner by reducing an adjustment load of the position of an optical system related to optical coherence tomography when performing optical coherence tomography by changing the magnification of an eye to be examined. In an ophthalmologic apparatus configured to be able to exchange a plurality of objective lenses 111 and 121 having different magnifications as objective lenses arranged at positions facing the eye E, the objective lenses are arranged at positions facing the eye E. The magnification of the objective lens (the objective lens 111 or the objective lens 121) is acquired, and the movable range of the OCT optical system related to optical coherence tomography of the eye E according to the acquired magnification of the objective lens (OCT focus lens 135- If it is 1, control is performed to change the position of the movable range FR1 or movable range FR2, and if it is the reference mirror 132-3, the movable range GR1 or movable range GR2) is changed. [Selection] Figure 4

Description

  The present invention relates to an ophthalmologic apparatus in which a plurality of objective lenses having different magnifications can be exchanged as an objective lens disposed at a position facing an eye to be examined, a control method thereof, and a computer for executing the control method. It is about the program.

  At present, as an ophthalmologic apparatus for observing or photographing an eye, for example, an anterior segment photographing apparatus, an eye fundus camera, a confocal laser scanning ophthalmoscope (SLO) apparatus, light using multi-wavelength light wave interference There is an optical coherence tomography (OCT) apparatus and the like. Above all, since an OCT apparatus can obtain a tomographic image of a subject with high resolution, it is becoming an indispensable device as a ophthalmologic apparatus in a specialist outpatient department of the retina. It's being used.

  When using an OCT apparatus as an ophthalmologic apparatus, for example, depending on the disease of the eye, imaging a wide area to include the periphery of the fundus or imaging a specific part of the fundus with high resolution, that is, changing the optical magnification Shooting is required. In this regard, for example, Patent Document 1 discloses an ophthalmologic apparatus that changes the optical magnification by attaching and detaching an optical member for zooming between the eye to be examined and the objective lens.

JP, 2011-147612, A

  However, in the ophthalmologic apparatus described in Patent Document 1, since the optical member for magnification change is added to the optical system for optical interference tomography, the optical system for optical interference tomography is also scaled. For this reason, for example, when performing optical coherence tomography of an eye to be examined using an optical member for variable magnification, it is necessary to adjust the position of the optical system related to optical coherence tomography from scratch every time the magnification is performed. And there is a problem that the burden on the operation of the examiner is great.

  The present invention has been made in view of such problems, and reduces the adjustment load of the position of the optical system related to optical coherence tomography in the case where optical coherence tomography is performed by changing the magnification of the eye to be examined. The purpose is to provide a mechanism that can reduce the burden on the examiner's operation.

The ophthalmologic apparatus according to the present invention is an ophthalmologic apparatus in which a plurality of objective lenses having different magnifications are exchangeably configured as an objective lens disposed at a position facing the eye to be examined, and is disposed at a position facing the eye to be examined Control for changing the position of the movable range of the optical system involved in optical coherence tomography of the subject's eye according to the acquisition means for acquiring the magnification of the objective lens and the acquired magnification of the objective lens Control means.
Further, the present invention includes the control method of the above-described ophthalmologic apparatus, and a program for causing a computer to execute the control method.

  According to the present invention, it is possible to reduce the adjustment load of the position of the optical system involved in optical coherence tomography and reduce the operation burden on the examiner when performing magnification of the eye to be examined and performing optical coherence tomography. It becomes possible.

FIG. 1 is a view showing an example of the overall configuration of an ophthalmologic apparatus according to a first embodiment of the present invention. It is a figure which shows the 1st Embodiment of this invention and shows an example of an internal structure of the test | inspection part shown in FIG. 1, and a base part. FIG. 5 shows the first embodiment of the present invention, and shows an example of an internal configuration of a control / processing unit shown in FIG. In the ophthalmologic apparatus concerning the 1st Embodiment of this invention, it is a figure which shows an example of change control of the position of the OCT optical system accompanying the magnification change of an objective lens. FIG. 5 is a view showing a first embodiment of the present invention and showing an example of movement control of the OCT focus lens shown in FIG. 4. FIG. 5 is a view showing a first embodiment of the present invention and showing an example of movement control of a reference mirror shown in FIG. 4; It is a flowchart which shows an example of the process sequence in the control method of the ophthalmologic apparatus which concerns on the 1st Embodiment of this invention. FIG. 2 is a view showing the first embodiment of the present invention and showing an example of a tomographic image of the fundus of the eye to be examined. In the ophthalmologic apparatus which concerns on the 2nd Embodiment of this invention, it is a figure which shows an example of change control of the position of the OCT optical system accompanying the magnification change of an objective lens.

  Hereinafter, embodiments (embodiments) for carrying out the present invention will be described with reference to the drawings.

First Embodiment
First, a first embodiment of the present invention will be described.

<Overall Configuration of Ophthalmic Device 10>
FIG. 1 is a view showing an example of the overall configuration of an ophthalmologic apparatus 10 according to a first embodiment of the present invention. The ophthalmologic apparatus 10 is configured to include an inspection unit 100, a control / processing unit 200, an input unit 300, a display unit 400, a stage unit 500, a base unit 600, and a face receiving unit 700, as shown in FIG. ing.

  The inspection unit 100 irradiates light to the subject's eye (more specifically, in the present embodiment, the fundus of the subject's eye) based on the control of the control / processing unit 200, and the return light reflected / scattered from the subject's eye Detect and acquire various image signals.

  The control and processing unit 200 generally controls the operation of the ophthalmologic apparatus 10 and performs various processes. For example, the control / processing unit 200 controls the inspection unit 100, the display unit 400, the stage unit 500, and the base unit 600, and performs predetermined image processing and the like on various image signals obtained by the inspection unit 100. Do.

  The input unit 300 inputs various information to the control / processing unit 200. The input unit 300 is configured of, for example, a keyboard, a mouse, and the like operated by an examiner.

  The display unit 400 performs processing of displaying various images, various information, and the like based on the control of the control / processing unit 200.

  The stage unit 500 moves the inspection unit 100 in the X direction, the Y direction, and the Z direction in FIG. 1 via a motor (not shown) based on the control of the control / processing unit 200.

  The base unit 600 supports the inspection unit 100 via the stage unit 500 and supports the face receiving unit 700. Further, the base unit 600 incorporates the spectroscope 610 shown in FIG.

  The face receiving unit 700 receives the face of the subject and fixes the jaw and forehead of the subject, thereby promoting fixation of the eye of the subject.

«Internal configuration of inspection unit 100 and base unit 600»
FIG. 2 shows the first embodiment of the present invention, and shows an example of the internal configuration of the inspection unit 100 and the base unit 600 shown in FIG.

  First, the internal configuration of the inspection unit 100 shown in FIG. 2 will be described.

  In the inspection unit 100 shown in FIG. 2, the objective lens 111 is disposed to face the eye E, and the first dichroic mirror 132-1 and the second dichroic mirror 132-2 are disposed on the optical axis of the objective lens 111. . The light is an optical path L1 of the OCT optical system, an SLO optical system that combines observation of the eye E and acquisition of a two-dimensional image, and fixation by the first dichroic mirror 132-1 and the second dichroic mirror 132-2. The optical path L2 of the target optical system and the optical path L3 of the anterior eye observation optical system are branched for each wavelength band.

  Here, the objective lens 111 is held by a lens barrel 110 that holds the lens. The lens barrel 110 is provided with a mark 112 for detecting attachment / detachment which is, for example, a projection. The objective lens detection unit 131 detects the presence or absence of the lens barrel 110 by, for example, a proximity sensor. The objective lens 121 is a lens used at the time of zooming, and specifically, in the present embodiment, it is an objective lens (second objective lens) having a magnification higher than that of the objective lens 111 (first objective lens). is there. The objective lens 121 is also held by the lens barrel 120, and the lens barrel 120 is provided with a mark 122 for detecting attachment / detachment at a position different from that of the lens barrel 110. Then, the objective lens detection unit 131 detects these attachment / detachment detection marks 112 and 122 to detect which magnification of the objective lens is attached as an objective lens disposed at a position facing the eye E to be examined. can do. As shown in FIG. 2, the ophthalmologic apparatus 10 according to the present embodiment is configured to be able to exchange a plurality of objective lenses 111 and 121 having different magnifications as an objective lens disposed at a position facing the eye E to be examined. .

  Specifically, the optical path L2 of the SLO optical system and the fixation target optical system includes, for example, an SLO optical system for capturing a fundus front image (SLO image) to observe the fundus oculi Ef of the subject eye E; It is an optical path of a fixation target optical system which presents a fixation target to Ef. The optical path L1 of the OCT optical system is, for example, an optical path of the OCT optical system 130 for capturing a tomographic image (OCT image) on the fundus oculi Ef of the eye to be examined E. Further, an optical path L3 of the anterior eye observation optical system is an optical path of the anterior eye observation optical system for capturing an anterior eye portion image in order to observe the anterior eye portion of the subject eye E.

  First, the optical path L2 of the SLO optical system and the fixation target optical system will be described.

  In the light path L2, the relay lens 141, SLO scanning means 142, lenses 135-4 and 135-5, mirror 132-5, third dichroic mirror 132-4, photodiode 153, SLO light source 152, fixation lamp A light source for visual target) 151 is disposed.

  The mirror 132-5 is a prism on which a perforated mirror or a hollow mirror is vapor-deposited, and separates illumination light from the SLO light source 152 and return light from the eye E to be examined. The third dichroic mirror 132-4 separates the illumination light from the SLO light source 152 and the fixation light from the fixation lamp 151 for each wavelength band and outputs the light path L 2.

  The SLO scanning unit 142 scans illumination light from the SLO light source 152 and fixation light from the fixation lamp 151 on the fundus Ef of the eye E. The SLO scanning unit 142 includes an X scanner that scans in the X direction in FIG. 2 and a Y scanner that scans in the Y direction in FIG. In the present embodiment, the X scanner is, for example, a scanner responsible for scanning in the main scanning direction in the SLO scanning unit 142, and needs to perform high-speed scanning, and thus is configured by, for example, a polygon mirror. Further, the Y scanner is, for example, a scanner responsible for scanning in the sub scanning direction in the SLO scanning unit 142, and is constituted by, for example, a galvano mirror.

  The lens 135-4 is driven by, for example, a motor (not shown) for focusing the illumination light by the SLO light source 152 and the fixation light by the fixation lamp 151. The fixation lamp 151 emits fixation light, which is visible light, to the eye to be examined E to present a fixation target based on the fixation light on the fundus oculi Ef of the eye to be examined E, thereby fixing the fixation of the eye to be examined. It is for prompting. The SLO light source 152 generates light of a wavelength around 780 nm, for example.

  The illumination light emitted from the SLO light source 152 is reflected by the third dichroic mirror 132-4, passes through the mirror 132-5, passes through the lenses 135-5 and 135-4, and is scanned by the SLO scanning means 142. It is scanned on the fundus oculi Ef of the optometry E. The return light from the fundus oculi Ef of the eye to be examined E follows the same path as the illumination light, is reflected by the mirror 132-5, and is guided to the photodiode 153. The photodiode 153 detects return light from the fundus oculi Ef of the eye to be examined E, and acquires an SLO image signal.

  The fixation light emitted from the fixation lamp 151 passes through the third dichroic mirror 132-4 and the mirror 132-5, passes through the lenses 135-5 and 135-4, and is transmitted by the SLO scanning unit 142. It is scanned on the fundus oculi Ef of the eye to be examined E. At this time, by causing the fixation lamp 151 to blink in accordance with the movement of the SLO scanning means 142, it becomes possible to form a fixation target of an arbitrary shape at any position on the fundus oculi Ef of the eye E to be examined. The subject can be urged to fixate.

  Subsequently, the optical path L1 of the OCT optical system will be described.

  The optical path L1 of the OCT optical system is an optical path of the OCT optical system 130 which is an optical system for performing optical coherence tomography of the eye E to be examined. More specifically, it is an optical path for obtaining an interference signal for forming a tomographic image (OCT image) of an eye to be examined.

  First, a relay lens 133, an OCT scanning means 134, a shutter 136, an OCT focus lens 135-1, and a lens 135-2 are disposed in the optical path L1 of the OCT optical system. The OCT scanning means 134 is configured to include an XY scanner for scanning light (measurement light) from the OCT light source 101 on the fundus Er of the eye E to be examined. The OCT scanning means 134 is illustrated as a single mirror in the example shown in FIG. 2, but performs scanning in the X direction and the Y direction. The shutter 136 can be inserted into and retracted from the light path L1 by a drive mechanism (not shown). The OCT focus lens 135-1 transmits light (measurement light) from the OCT light source 101 emitted from the fiber end 105-1 of the optical fiber 102-2 connected to the optical coupler 103 to the fundus Ef of the eye E It is a focus adjustment member for focusing. The OCT focus lens 135-1 is driven by a motor (not shown) based on the control of the control / processing unit 200.

  As a result of focusing by the OCT focusing lens 135-1, the return light from the fundus Ef of the eye to be examined E is simultaneously imaged into a spot shape and incident on the fiber end 105-1 of the optical fiber 102-2. . Furthermore, an optical coupler 103, an OCT light source 101, optical fibers 102-1 to 102-4, a lens 135-3, a dispersion compensating glass 137, and a reference mirror 132-3 are disposed in the optical path L1 of the OCT optical system. There is. The optical fibers 102-1 to 102-4 are, for example, single-mode optical fibers connected to and integrated with the optical coupler 103. In addition, a spectroscope 610 configured inside the base unit 600 is connected to the optical fiber 102-4. The Michelson interference system is configured by the above configuration.

  The OCT light source 101 is configured of, for example, SLD (Super Luminescent Diode), which is a typical low coherent light source. The central wavelength of the light of the OCT light source 101 is about 855 nm, and the wavelength band width is about 100 nm. Here, the bandwidth is an important parameter because it affects the resolution in the optical axis direction of the obtained tomographic image. Furthermore, although an example in which SLD is applied as the OCT light source 101 has been described here, any light source that can emit low coherent light may be used, and for example, ASE (Amplified Spontaneous Emission) can be used. Further, in view of measuring the eye E to be examined, near infrared light is suitable for the central wavelength of the light of the OCT light source 101. Further, since the central wavelength of the light of the OCT light source 101 affects the resolution in the lateral direction of the obtained tomographic image, it is desirable that the central wavelength be as short as possible. For both reasons, in the embodiment, the center wavelength of the light of the OCT light source 101 is set to about 855 nm. Further, although the example of applying the Michelson interference system has been described in the present embodiment, for example, a Mach-Zehnder interference system may be used. For example, it is desirable to use a Mach-Zehnder interference system when the light amount difference is large according to the light amount difference between the measurement light and the reference light, and use a Michelson interferometer when the light amount difference is relatively small.

  The optical coupler 103 is a branching member that branches the light emitted from the OCT light source 101 via the optical fiber 102-1 into measurement light and reference light. The measurement light branched by the optical coupler 103 is emitted toward the fundus oculi Ef of the eye to be examined E to be observed through the optical fiber 102-2 and the objective lens. The measurement light irradiated to the fundus Er is reflected and scattered at the fundus Er, and reaches the optical coupler 103 through the same optical path. On the other hand, the reference light passes through the optical fiber 102-3, passes through the lens 135-3 and the dispersion compensation glass 137, and is emitted toward the reference mirror 132-3. The reference light irradiated to the reference mirror 132-3 is reflected by the reference mirror 132-3 and reaches the optical coupler 103 through the same optical path.

  In this manner, the measurement light and the reference light that have reached the optical coupler 103 are combined in the optical coupler 103 to become interference light. Here, interference occurs when the optical path length of the measurement light and the optical path length of the reference light become substantially the same. The reference mirror 132-3 is adjustably held in the direction of the optical axis by a motor and a drive mechanism (not shown) based on the control of the control / processing unit 200, and the reference optical It is possible to match the optical path length. That is, the reference mirror 132-3 configures a reference light adjustment member that adjusts the optical path length of the reference light.

  The optical fiber 102-2 is provided with a polarization adjustment unit 104-1 on the measurement light side, and the optical fiber 102-3 is provided with a polarization adjustment unit 104-2 on the reference light side. These polarization adjusting sections 104-1 and 104-2 have several portions in which the optical fiber is wound in a loop, and twisting the optical fiber by rotating the loop-shaped portion around the longitudinal direction of the optical fiber In addition, it is possible to adjust and match the polarization states of the corresponding measurement light and reference light, respectively.

  Subsequently, the light path L3 of the anterior eye observation optical system will be described.

  In an optical path L3 of the anterior eye observation optical system, a lens 135-6, a split prism 161, a lens 135-7, and a CCD 162 for anterior eye observation for detecting infrared light are disposed. The CCD 162 has sensitivity to the wavelength of light of the illumination light source for anterior eye observation (not shown), specifically, around 970 nm. The split prism 161 is disposed at a position conjugate to the pupil of the subject eye E, and is for detecting the distance in the Z direction (front-rear direction) of the inspection unit 100 with respect to the subject eye E as a split image of the anterior segment. It is.

  Next, the internal configuration of the base unit 600 shown in FIG. 2 will be described.

  Inside the base portion 600, a spectroscope 610 is provided. The spectroscope 610 includes a lens 611, a diffraction grating 612, a lens 613, and a line sensor 614.

  The interference light generated by the optical coupler 103 is guided to the spectroscope 610 via the optical fiber 102-4. Specifically, the interference light emitted from the optical fiber 102-4 becomes parallel light through the lens 611, is separated by the diffraction grating 612, and forms an image on the line sensor 614 by the lens 613. The line sensor 614 detects this interference light to acquire an OCT image signal.

  In the present embodiment, the OCT optical system 130 shows a configuration example for capturing a tomographic image of the fundus oculi Ef of the eye E to be examined, but the present invention is not limited to this. The tomographic image of the anterior segment of the eye E to be examined may be photographed. As described above, in the OCT optical system 130, the light from the OCT light source 101 is divided by the photocoupler 103 into measurement light and reference light. Then, the measurement light is emitted toward the fundus oculi Ef of the eye to be examined E to be observed through the optical fiber 102-2 and the objective lens. Then, the return light of the measurement light from the fundus oculi Ef is multiplexed with the reference light reflected by the reference mirror 132-3 in the optical coupler 103, and is guided to the spectroscope 610 as interference light. The return light described here refers to reflected light or scattered light including information on an interface or the like in the irradiation direction of light to the fundus Ef of the eye to be examined E to be observed. Then, interference light between the return light and the reference light is detected by the spectroscope 610 and analyzed to obtain a tomographic image of the fundus oculi Ef. At this time, in order to obtain a high resolution tomographic image in the ophthalmologic apparatus 10, it is necessary to match the dispersion amounts of the optical system in the optical path of the measurement light and the optical path of the reference light. This is because if the amount of dispersion is different, the tomographic image is blurred and resolution in the depth direction is degraded.

«Internal configuration of control and processing unit 200»
FIG. 3 is a diagram showing the first embodiment of the present invention and showing an example of the internal configuration of the control / processing unit 200 shown in FIG. In FIG. 3, the same components as those shown in FIGS. 1 and 2 are denoted by the same reference numerals.

  As shown in FIG. 3, the control / processing unit 200 includes a central processing unit (CPU) 210, a fixed disk drive (HDD) 220, a main storage unit (memory) 230, a user interface 240, an OCT scanner control unit 250, and an OCT scanner. (X) driver 251, OCT scanner (Y) driver 252, SLO scanner control unit 260, SLO scanner (X) driver 261, SLO scanner (Y) driver 262, motor driver 270, and fixation target control unit 280 Is configured.

  The CPU 210 is connected to the display unit 400, the HDD 220, the memory 230, and the user interface 240. Further, the CPU 210 is connected to an OCT scanner control unit 250, an SLO scanner control unit 260, a motor driver 270, a fixation target control unit 280, a photodiode 153, and a line sensor 614.

  The CPU 210 controls an OCT scanner control unit 250 that generates a scan waveform of the OCT scanning unit 134. Then, the OCT scanner control unit 250 controls the driving of the OCT scanning unit 134 by controlling the OCT scanner (X) driver 251 and the OCT scanner (Y) driver 252 based on the control of the CPU 210.

  The CPU 210 also controls the SLO scanner control unit 260 that generates a scan waveform of the SLO scanning unit 142. The SLO scanner control unit 260 controls the driving of the SLO scanning unit 142 by controlling the SLO scanner (X) driver 261 and the SLO scanner (Y) driver 262 based on the control of the CPU 210. Specifically, the SLO scanner control unit 260 controls the driving of the SLO scanning unit 142 via the SLO scanner (X) driver 261 and the SLO scanner (Y) driver 262 to illuminate the fundus Ef of the eye E to be examined. Scan in two dimensions. Thereby, the photodiode 153 can acquire a signal of an SLO image which is a two-dimensional image of the fundus oculi Ef.

  Furthermore, the CPU 210 controls the drive of a motor (not shown) that drives the OCT focus lens 135-1, the lens 135-4, and the reference mirror 132-3 via the motor driver 270.

  Furthermore, the CPU 210 controls a fixation target control unit 280 that performs lighting control of the fixation light 151. Then, the fixation target control unit 280 performs lighting control of the fixation lamp 151 based on the control of the CPU 210. Specifically, in the present embodiment, information on the initial imaging area and the scanning line interval necessary for acquiring the SLO image at the time of previewing is stored in the memory 230 in advance. Then, the fixation target control unit 280 matches the timing at which the SLO scanning unit 142 scans a desired position on the fundus Er with light based on the frame rate and scanning line interval of the initial imaging area or partial area of the SLO image. The fixation lamp 151 is turned on to form an arbitrary fixation target at an arbitrary position on the fundus Er.

  Furthermore, the CPU 210 controls the photodiode 153 that acquires the SLO image signal, acquires the SLO image signal from the photodiode 153, and performs image processing or the like of the SLO image signal.

  Further, the CPU 210 controls the line sensor 614 that acquires an OCT image signal to acquire an OCT image signal from the line sensor 614, and performs image processing of the OCT image signal and the like. Specifically, in the present embodiment, the CPU 210 Fourier-transforms the OCT image signal obtained from the line sensor 614, and converts the obtained signal into luminance or density information to obtain the depth direction of the eye E (Z direction The tomographic image of) is generated. Such a scan method is called an A scan, and a tomographic image obtained is called an A scan image. A plurality of A-scan images can be acquired by performing this A-scan in the predetermined transverse direction of the eye E using the OCT scanning means 134. For example, a tomographic image in the XZ plane can be obtained by scanning the OCT scanning means 134 in the X direction, and a tomographic image in the YZ plane can be obtained by scanning the OCT scanning means 134 in the Y direction. A method of scanning the eye to be examined E in a predetermined transverse direction in this manner is called a B-scan, and a tomographic image obtained is called a B-scan image.

  The memory 230 stores, for example, a program for the CPU 210 to execute processing and various types of information in advance, and stores various types of information and the like obtained by the processing of the CPU 210. For example, the memory 230 may be provided with objective lenses 111 and 121 of different magnifications that can be arranged at positions facing the eye E, various parameters shown in FIG. 4 (and various other parameters shown in FIGS. 5-1 and 5-2). Table information indicating the correspondence with the Furthermore, the memory 230 also stores subject information and the like related to the subject eye E.

Next, a method of photographing a tomographic image by the ophthalmologic apparatus 10 will be described.
The ophthalmologic apparatus 10 can capture a tomographic image of a predetermined region of the fundus oculi Ef of the eye to be examined E by controlling the OCT scanning means 134.

  First, the CPU 210 controls the OCT scanning unit 134 to scan measurement light in the X direction, and acquires an OCT image signal relating to a predetermined number of scans from the imaging range in the X direction on the fundus oculi Ef with the line sensor 614. Then, the CPU 210 performs Fast Fourier Transform (FFT) on the luminance distribution of the OCT image signal of the line sensor 614 obtained at a certain position in the X direction, and displays the linear luminance distribution obtained by FFT on the display unit 400. Convert to density or color information to indicate. In the present embodiment, this corresponds to an A-scan image, and a two-dimensional image in which a plurality of A-scan images are arranged corresponds to a B-scan image. Then, after acquiring a plurality of A-scan images for constructing one B-scan image, the CPU 210 moves the scanning position in the Y-direction and scans the plurality of B-scan images by scanning again in the X-direction. get. Then, the CPU 210 can be used for diagnosing the eye E to be examined by the examiner by displaying on the display unit 400 a plurality of B-scan images or a three-dimensional image constructed from a plurality of B-scan images. Here, an example in which a B-scan image is acquired by scanning in the X direction has been described, but the present embodiment is not limited to this, and a B-scan image is scanned by scanning in the Y direction. It may be acquired. Further, an arbitrary scan pattern may be formed by scanning in both the X direction and the Y direction, and a B-scan image may be acquired.

<Change Control of Position of OCT Optical System 130>
Next, change control of the position of the OCT optical system 130 (specifically, in the present embodiment, the OCT focus lens 135-1 and the reference mirror 132-3) accompanying the change of the magnification of the objective lens will be described.

  FIG. 4 is a view showing an example of the change control of the position of the OCT optical system 130 accompanying the change of the magnification of the objective lens in the ophthalmologic apparatus 10 according to the first embodiment of the present invention. In FIG. 4, the same components as those shown in FIG. 2 are denoted by the same reference numerals. Specifically, FIG. 4 illustrates only a portion of the OCT optical system 130 of FIG.

  FIG. 4A is a diagram showing the position of the OCT optical system 130 when the objective lens 111 with low magnification (short focal length and wide angle of view) is disposed at a position facing the eye E. FIG. 4B shows the position of the OCT optical system 130 when the objective lens 121 having a higher magnification (long focal length and narrow angle of view) than the objective lens 111 is disposed at a position facing the eye E. FIG. More specifically, FIGS. 4A and 4B mainly show the position and reference position of the movable range of the OCT focus lens 135-1 and the reference mirror 132-3 in the OCT optical system 130. There is.

  In FIG. 4, the light emitted from the fiber end 105-1 passes through the lens 135-2 and the OCT focus lens 135-1 and is scanned by the OCT scanning means 134. The light (light flux) deflected by the OCT scanning means 134 is transmitted through the objective lens 111 or the objective lens 121 and condensed on the fundus Ef of the eye E.

  In FIG. 4A, the working distance WD1 is the distance between the eye E and the objective lens 111, which is determined according to the focal length of the low-power objective lens 111. The reference position FP1 is a reference position on the optical axis of the OCT focus lens 135-1 when the low-magnification objective lens 111 is mounted. In this reference position FP1, when the diopter of the eye to be examined E is 0 diopter, the light amount of the return light that is reflected by the fundus Ef and enters the fiber end 105-1 through the reverse optical path becomes maximum. It is a position where the brightness of the tomographic image to be displayed is maximum. The movable range FR1 is a movable range (movable range) of the OCT focus lens 135-1 when the low magnification objective lens 111 is mounted. By moving the OCT focus lens 135-1 within the movable range FR1, it is possible to focus on the subject eye E having different diopter. The reference position GP1 is a reference position of the reference mirror 132-3 when the low-magnification objective lens 111 is mounted. The reference position GP1 can be uniquely determined corresponding to the optical path length of the measurement light determined according to the low magnification working distance WD1. The movable range GR1 is a movable range (movable range) of the reference mirror 132-3 when the low-magnification objective lens 111 is mounted. By moving the reference mirror 132-3 within the movable range GR 1, the position of the tomographic image of the eye to be examined E displayed on the display unit 400 can be adjusted.

  In FIG. 4B, the working distance WD2 is the distance between the eye E to be examined and the objective lens 121, which is determined according to the focal length of the high magnification objective lens 121. The reference position FP2 is a reference position on the optical axis of the OCT focus lens 135-1 when the high-magnification objective lens 121 is mounted. In this reference position FP2, when the diopter of the eye to be examined E is 0 diopter, the light amount of the return light that is reflected by the fundus Ef and enters the fiber end 105-1 through the reverse optical path becomes maximum. It is a position where the brightness of the tomographic image to be displayed is maximum. The movable range FR2 is a movable range (movable range) of the OCT focus lens 135-1 when the high magnification objective lens 121 is attached. By moving the OCT focus lens 135-1 within the movable range FR2, the subject eye E having different diopter can be focused. The reference position GP2 is a reference position of the reference mirror 132-3 when the high magnification objective lens 121 is mounted. The reference position GP2 can be uniquely determined corresponding to the optical path length of the measurement light determined according to the high magnification working distance WD2. The movable range GR2 is a movable range (movable range) of the reference mirror 132-3 when the high-magnification objective lens 121 is mounted. By moving the reference mirror 132-3 within the movable range GR <b> 2, the position of the tomographic image of the eye to be examined E displayed on the display unit 400 can be adjusted.

  In FIG. 4B, a focus correction lens 135-1a is provided as the OCT optical system 130. The focus correction lens 135-1a is inserted into and retracted from the optical path L1 of the OCT optical system under the control of the CPU 210. The focus correction lens 135-1a is a focus correction member provided in the optical path L1 of the OCT optical system 130 so that the reference position of the OCT focus lens 135-1 does not change with respect to a specific diopter of the eye E to be examined. . By providing the focus correction lens 135-1a, it is not necessary to provide a plurality of movable ranges of the OCT focus lens 135-1, and therefore, it is possible to realize the more compact ophthalmic apparatus 10.

  In the present embodiment, objective lenses 111 and 121 of different magnifications that can be disposed at positions facing the eye E, and various parameters (reference positions FP1 and GP1 and movable ranges FR1 and GR1 shown in FIG. 4, reference positions) It is assumed that table information indicating the correspondence between FP2 and GP2 and movable ranges FR2 and GR2 is stored in memory 230 in advance. At this time, the table information stored in the memory 230 may be, for example, previously calculated from design values, or various parameters in each objective lens are recorded in advance for each manufactured ophthalmologic apparatus 10. It may be calculated. Then, the CPU 210 acquires various parameters shown in FIG. 4 corresponding to the magnification of the objective lens from the memory 230 according to the magnification of the objective lens detected by the objective lens detection unit 131, and the OCT focus lens 135-1 And control to change the position of the movable range in the reference mirror 132-3 and the reference position.

  For example, as shown in FIG. 4, when the objective lens disposed at the position facing the eye E is changed from the low power objective lens 111 to the high power objective lens 121, the CPU 210 arranges the objective lens 111. The position of the movable range FR2 of the OCT focus lens 135-1 when the objective lens 121 is disposed is the position of the objective lens (or the eye E to be examined) than the position of the movable range FR1 of the OCT focus lens 135-1 at the time of Control to change the direction away from).

  In addition, the CPU 210 is also changing the size of the movable range FR2 to be larger than the size of the movable range FR1. By changing the size of the movable range in this way, focusing on the entire curved imaging region becomes possible in optical coherence tomography using the low magnification (wide angle of view) objective lens 111, and high magnification ( In optical coherence tomography using an objective lens 121 having a narrow angle of view), higher-speed focusing operation becomes possible.

  Further, for example, as shown in FIG. 4, when the objective lens disposed at the position facing the eye E to be examined is changed from the low power objective lens 111 to the high power objective lens 121, the CPU 210 performs the objective lens 111. The position of the movable range GR2 of the reference mirror 132-3 when the objective lens 121 is disposed is set to the position of the objective lens (or the eye E) than the position of the movable range GR1 of the reference mirror 132-3 when the Control to change the direction away from).

<Processing Procedure of Control Method of Ophthalmologic Apparatus 10>
FIG. 6 is a flowchart showing an example of the processing procedure in the control method of the ophthalmologic apparatus 10 according to the first embodiment of the present invention. In addition, in description of FIG. 6, in order to simplify description, as an objective lens which can be arrange | positioned in the position which opposes the to-be-tested eye E, the objective lens 111 of low magnification (wide angle of view) and high magnification (narrow angle of view) ) And the objective lens 121 of.

  First, when the objective lens is replaced, in step S1, the objective lens detection unit 131 performs processing to detect the replaced objective lens. Here, in the present embodiment, the objective lens detection unit 131 detects the marks 112 and 122 for attachment / detachment detection provided at different positions of the lens barrel incorporating the objective lens, respectively. And 121 are detected. The replacement of the objective lens is performed by attaching a lens barrel incorporating the objective lens to an objective lens attachment portion (not shown) of the ophthalmologic apparatus 10. At this time, as a mounting mechanism of the objective lens mounting portion (not shown), for example, a known mounting mechanism such as a bayonet type can be used.

  Subsequently, in step S2, the CPU 210 acquires objective lens information including the magnification of the objective lens from the objective lens detection unit 131. Then, the CPU 210 acquires various parameters corresponding to the objective lens information from the memory 230. As various parameters acquired here, for example, the working distance WD1 or WD2, the reference position FP1 or FP2 of the OCT focus lens 135-1 and the movement of the OCT focus lens 135-1 corresponding to each objective lens shown in FIG. The possible range is FR1 or FR2, the reference position GP1 or GP2 of the reference mirror 132-3, or the movable range GR1 or GR2 of the reference mirror 132-3. The CPU 210 that performs the process of step S2 constitutes an acquisition unit.

  Subsequently, in step S3, the CPU 210 changes the objective lens in step S1 based on the objective lens information acquired in step S2 to a high magnification (narrow angle of view) from the objective lens 111 of low magnification (wide angle of view). It is determined whether or not the replacement of the objective lens 121 is required.

As a result of the determination in step S3, if the replacement of the objective lens in step S1 is the replacement of the low magnification (wide angle of view) objective lens 111 to the high magnification (narrow angle of field) objective lens 121 (S3 /) YES), go to step S4.
At step S4, the CPU 210 performs control to adjust the working distance automatically.

On the other hand, if it is determined in step S3 that the replacement of the objective lens in step S1 is not replacement of the low magnification (wide angle of view) objective lens 111 to the high magnification (narrow angle of field) objective lens 121 (S3 / NO), go to step S5. That is, when the high magnification (narrow angle of view) objective lens 121 is replaced with the low magnification (wide angle of view) objective lens 111, the process proceeds to step S5.
In step S5, the CPU 210 performs manual adjustment control of the working distance based on the operation of the examiner, without automatically adjusting the working distance. In this case, when the objective lens 121 with high magnification (narrow angle of view) is replaced with the objective lens 111 with low magnification (wide angle of view) and the working distance is changed from a long side to a short side, the inspection unit 100 Is operated in the direction toward the subject. That is, in this case, by performing the manual operation by the examiner, it is possible to move the inspection unit 100 while the examiner surely confirms the subject.

If the process of step S4 is completed, or if the process of step S5 is completed, the process proceeds to step S6.
At step S6, the CPU 210 determines various parameters (reference position FP1 or FP2, movable range) related to the OCT focus lens 135-1 corresponding to the objective lens exchanged at step S1 acquired from the memory 230 at step S2. The reference position of the OCT focus lens 135-1 and its movable range are set according to FR1 or FR2). In this step, when the objective lens replaced in step S1 is the objective lens 111, the CPU 210 sets the movable range of the OCT focus lens 135-1 to the position of the movable range FR1 shown in FIG. When the objective lens replaced in step S1 is the objective lens 121, change control is performed to move the movable range of the OCT focus lens 135-1 to the position of the movable range FR2 shown in FIG. 4B. Further, in this step, when the objective lens replaced in step S1 is the objective lens 111, the CPU 210 sets the reference position of the OCT focus lens 135-1 to the position of the reference position FP1 shown in FIG. When the objective lens replaced in step S1 is the objective lens 121, change control is performed to set the reference position of the OCT focus lens 135-1 to the position of the reference position FP2 shown in FIG. 4B. As shown in FIG. 4, when the objective lens 111 of low magnification (wide angle of view) is replaced with the objective lens 121 of high magnification (narrow angle of field), the movable range and reference of the OCT focus lens 135-1 When the position moves in a direction away from the eye E to be examined and the objective lens 121 of high magnification (narrow angle of view) is replaced with the objective lens 111 of low magnification (wide angle of view), the OCT focus lens 135-1 The movable range and the reference position move in a direction approaching the eye E. Moreover, CPU210 which performs the process of this step comprises a control means.

  Subsequently, in step S7, the CPU 210 performs control to move the OCT focus lens 135-1 to the position (for example, the reference position) set in step S6.

  Subsequently, in step S8, the CPU 210 acquires various parameters (reference position GP1 or GP2, movable range) related to the reference mirror 132-3 corresponding to the objective lens exchanged in step S1 acquired from the memory 230 in step S2. The reference position of the reference mirror 132-3 and its movable range are set according to GR1 or GR2). In this step, when the objective lens replaced in step S1 is the objective lens 111, the CPU 210 sets the movable range of the reference mirror 132-3 to the position of the movable range GR1 shown in FIG. When the objective lens replaced in S1 is the objective lens 121, change control is performed to set the movable range of the reference mirror 132-3 to the position of the movable range GR2 shown in FIG. 4B. Further, in this step, when the objective lens exchanged in step S1 is the objective lens 111, the CPU 210 sets the reference position of the reference mirror 132-3 to the position of the reference position GP1 shown in FIG. When the objective lens replaced in S1 is the objective lens 121, change control is performed to set the reference position of the reference mirror 132-3 to the position of the reference position GP2 shown in FIG. 4 (b). As shown in FIG. 4, when the objective lens 111 of low magnification (wide angle of view) is replaced with the objective lens 121 of high magnification (narrow angle of field), the movable range and reference position of the reference mirror 132-3 Moves in a direction away from the eye E to be examined, and can be moved from the high power (narrow angle of view) objective lens 121 to the low power (wide angle of view) objective lens 111, the reference mirror 132-3 can be moved The range and the reference position move in the direction approaching the eye E. In more detail, when the objective lens 111 of low magnification (wide angle of view) is replaced with the objective lens 121 of high magnification (narrow angle of field), as shown in FIG. 4, the reference mirror 132-3 can be moved The movement amounts of the range and the reference position move away from the fiber end 105-2 by ΔG = WD 2-WD 1 in accordance with the change from the working distance WD 1 to the working distance WD 2. Moreover, CPU210 which performs the process of this step comprises a control means.

  Subsequently, in step S9, the CPU 210 performs control to move the reference mirror 132-3 to the position (for example, reference position) set in step S8.

  Subsequently, in step S10, the CPU 210 performs control of emitting light from the OCT light source 101, acquires an OCT image signal from the line sensor 614, and generates a tomographic image (OCT image) of the fundus oculi Ef of the eye E to be examined. Process to acquire.

  When the process of step S10 ends, the process of the flowchart of FIG. 6 ends.

  By performing the process of FIG. 6, even when the objective lens having a different magnification is replaced, it is easy to match the working distance and the optical path lengths of the measurement light and the reference light by the OCT focus lens 135-1 and the reference mirror 132-3. Become. Thereby, when performing magnification of the eye E to be examined and performing optical coherence tomography, it is possible to reduce the adjustment load of the position of the OCT optical system 130 involved in optical coherence tomography, and to reduce the operation load of the examiner It becomes possible.

<< Moving Control Example of OCT Focus Lens 135-1 and Reference Mirror 132-3 >>
Next, an example of movement control of the OCT focus lens 135-1 and the reference mirror 132-3 will be described.

First, an example of movement control of the OCT focus lens 135-1 will be described.
FIGS. 5-1 is a figure which shows the 1st Embodiment of this invention, and shows the example of movement control of the OCT focus lens 135-1 shown in FIG. Specifically, FIG. 5-1 is a diagram showing an example of movement control of the OCT focus lens 135-1 in step S7 of FIG. In FIG. 5-1, the same components as those shown in FIG. 4 are denoted by the same reference numerals.

  5-1 (a) is a figure which shows the position of the OCT focus lens 135-1 when the objective lens 111 of low magnification (wide angle of view) is arrange | positioned in the position facing the to-be-tested eye E. FIG. 5-1 (b) shows the position of the OCT focus lens 135-1 when the objective lens 121 having a higher magnification (narrow angle of view) than the objective lens 111 is disposed at a position facing the eye E. FIG.

  First, in FIG. 5A, when the objective lens 111 with low magnification (wide angle of view) is disposed, the position of the OCT focus lens 135-1 is the reference position FP1 shown in the position FP11 (FIG. 4A). Shall have been When the low magnification (wide angle of view) objective lens 111 is replaced with a high magnification (narrow angle of view) objective lens 121, the CPU 210 performs three types of OCT shown in (1) to (3) below. The movement control of the focus lens 135-1 can be performed.

(1) As a first movement control of the OCT focus lens 135-1, the CPU 210 moves the OCT focus lens 135-1 away from the objective lens (or the eye E) by the movement amount ΔF1 shown in FIG. 5-1. It can control to move. At this time, the movement amount ΔF1 is, for example, a value that can be calculated by design, and the position of the OCT focus lens 135-1 shown in FIG. 5-1 according to the position FP11 of the OCT focus lens 135-1 shown in FIG. The FP 21 is stored in advance in the memory 230. In the first movement control, the CPU 210 corresponds to the position FP21 of the OCT focus lens 135-1 shown in FIG. 5-1 (FIG. 4A) according to the position FP11 of the OCT focus lens 135-1 shown in FIG. 5-1. Control to move to the reference position FP2 shown in FIG.

(2) As a second movement control of the OCT focus lens 135-1, the CPU 210 moves the OCT focus lens 135-1 away from the objective lens (or the eye E) by the movement amount ΔF2 shown in FIG. 5-1. It can control to move. Specifically, the CPU 210 performs control to move to the position FP22 of the OCT focus lens 135-1 shown in FIG. 5-1 according to the position FP11 of the OCT focus lens 135-1 shown in FIG. 5-1. This second movement control is to focus the OCT focus within the movable range FR2 of the OCT focus lens 135-1 according to the objective lens 121 of high magnification (narrow angle of view) while minimizing the automatic movement distance. It is movement control for arranging lens 135-1.

(3) As the third movement control of the OCT focus lens 135-1, the CPU 210 can perform movement control in which the movement of the OCT focus lens 135-1 is not performed first. However, when there is a movement input from the examiner to the movable range FR2 side (right side in FIG. 5-1) via the input unit 300, the CPU 210 generates the OCT focus lens 135-1 based on the movement input. Do the move. Also, when there is a movement input from the examiner to the side (left side in FIG. 5-1) moving away from the movable range FR2 via the input unit 300, the CPU 210 selects the OCT focus lens 135-based on the movement input. The move of 1 is not performed.

  In the first movement control and the second movement control described above with reference to FIG. 5-1, when the position of the OCT focus lens 135-1 is out of the range of the movable range FR2, the OCT focus lens 135-1 It is control to move 1 within the range of movable range FR2. Further, in the first movement control described above with reference to FIG. 5-1, when the position of the OCT focus lens 135-1 is positioned outside the movable range FR2, the OCT focus lens 135-1 can be moved. It is control to move to the reference position FP2 within the range of the range FR2. Then, when performing the first movement control and the second movement control described above, the CPU 210 controls so that the position of the OCT focus lens 135-1 remains within the range of the movable range FR2.

Next, an example of movement control of the reference mirror 132-3 will be described.
FIGS. 5-2 is a figure which shows the 1st Embodiment of this invention, and shows the example of movement control of the reference mirror 132-3 shown in FIG. Specifically, FIG. 5-2 is a diagram showing an example of movement control of the reference mirror 132-3 in step S9 of FIG. In FIG. 5-2, the same components as those shown in FIG. 4 are denoted by the same reference numerals.

  5-2 (a) is a figure which shows the position of the reference mirror 132-3 at the time of the objective lens 111 of low magnification (wide angle of view) being arrange | positioned in the position facing the to-be-tested eye E. FIG. FIG. 5-2 (b) is a diagram showing the position of the reference mirror 132-3 when the objective lens 121 having a magnification (narrow angle of view) higher than that of the objective lens 111 is disposed at a position facing the eye E to be examined. It is.

  First, in FIG. 5-2 (a), the position of the reference mirror 132-3 when the objective lens 111 with low magnification (wide angle of view) is disposed is the position GP11 (the reference position GP1 shown in FIG. 4 (a)) Shall have been Then, when the low magnification (wide angle of view) objective lens 111 is replaced with the high magnification (narrow angle of view) objective lens 121, the CPU 210 makes three references shown in (1) to (3) below. The movement control of the mirror 132-3 can be performed.

(1) As a first movement control of the reference mirror 132-3, the CPU 210 moves the reference mirror 132-3 away from the objective lens (or the eye E) by the movement amount ΔG1 shown in FIG. 5-2. It can control. At this time, the movement amount ΔG1 is, for example, a value that can be calculated by design, and the value is the same as ΔG = WD2-WD1 shown in FIG. This value is stored in advance in the memory 230. In the first movement control, the CPU 210 responds to the position GP11 of the reference mirror 132-3 shown in FIG. 5-2 to show the position GP21 of the reference mirror 132-3 shown in FIG. Control to move to the reference position GP2) is performed.

(2) As second movement control of the reference mirror 132-3, the CPU 210 moves the reference mirror 132-3 away from the objective lens (or the eye E) by the movement amount ΔG2 shown in FIG. 5-2. It can control. Specifically, the CPU 210 performs control to move to the position GP22 of the reference mirror 132-3 shown in FIG. 5-2 according to the position GP11 of the reference mirror 132-3 shown in FIG. 5-2. In this second movement control, the reference mirror 132 is moved within the movable range GR2 of the reference mirror 132-3 according to the high magnification (narrow angle of view) objective lens 121 while minimizing the automatic movement distance. It is movement control for arranging -3.

(3) As the third movement control of the reference mirror 132-3, the CPU 210 can perform movement control in which the movement of the reference mirror 132-3 is not performed first. However, when there is a movement input from the examiner to the movable range GR2 side (right side in FIG. 5B) via the input unit 300, the CPU 210 moves the reference mirror 132-3 based on the movement input. I do. In addition, when there is a movement input from the examiner to the side (left side in FIG. 5B) moving away from the movable range GR2 via the input unit 300, the CPU 210 selects the reference mirror 132-3 based on the movement input. Does not move.

  In the first movement control and the second movement control described above with reference to FIG. 5B, when the position of the reference mirror 132-3 is positioned outside the movable range GR2, the reference mirror 132-3 is used. It is control to move within the range of movable range GR2. In the first movement control described above with reference to FIG. 5B, when the position of the reference mirror 132-3 is located outside the movable range GR2, the reference mirror 132-3 can be moved within the movable range GR2 Control to move to the reference position GP2 within the range of Then, when performing the first movement control and the second movement control described above, the CPU 210 performs control so that the position of the reference mirror 132-3 remains within the range of the movable range GR2.

In the example shown in FIG. 4, when the objective lens 111 of low magnification (wide angle of view) is changed to the objective lens 121 of high magnification (narrow angle of field), the reference of the reference mirror 132-3 accompanying the change The amount of change ΔG in position was set as WD2-WD1 which is the amount of change in the distance between the objective lens and the eye to be examined E accompanying the change. Then, in the first movement control described above with reference to FIG. 5B, the reference mirror 132-3 is an objective lens with a movement amount ΔG1 (that is, ΔG = WD2−WD1 shown in FIG. 4) shown in FIG. The example which performs control which moves in the direction away from (or eye E to be examined) was explained. However, the present embodiment is not limited to this aspect. For example, the following aspects are also applicable to the present embodiment.
FIG. 7 is a view showing the first embodiment of the present invention and showing an example of a tomographic image of the fundus oculi Ef of the eye E to be examined. FIG. 7A is a view showing an example of a tomographic image of the fundus oculi Ef captured by the low magnification (wide angle of view) objective lens 111. While the tomographic image of the fundus oculi Ef shown in FIG. 7A is acquired, the objective lens 121 with high magnification (narrow angle of view) is changed to the first movement control described above with reference to FIG. As a result, aliasing occurs on the left and right as in the tomographic image shown in FIG. Therefore, when the objective lens 111 with low magnification (wide angle of view) is changed to the objective lens 121 with high magnification (small angle of field), the CPU 210 performs control to make the movement amount ΔG of the reference mirror smaller than WD2-WD1. Do. At this time, the CPU 210 can set, for example, the amount of change of the reference position of the reference mirror smaller than WD2-WD1. By performing control in this manner, it is possible to acquire a tomographic image without aliasing as shown in FIG. 7C.

  In the first embodiment, a mode is shown in which both the OCT focus lens 135-1 and the reference mirror 132-3 in the OCT optical system 130 are controlled, but the present embodiment is limited to this mode. It is not a thing. For example, a mode in which only one of the OCT focus lens 135-1 and the reference mirror 132-3 is controlled is also included in the present embodiment.

In the ophthalmologic apparatus 10 according to the first embodiment, the CPU 210 acquires the magnification of the objective lens disposed at the position facing the eye E (S2 in FIG. 6). Then, the CPU 210 changes and controls the position of the movable range of the OCT focus lens 135-1 of the OCT optical system 130 according to the acquired magnification of the objective lens (S6 in FIG. 6).
According to this configuration, it is possible to easily perform focus adjustment for obtaining a suitable tomographic image according to the magnification of the objective lens. Thereby, when performing magnification of the eye E to be examined and performing optical coherence tomography, the adjustment load of the position of the OCT focus lens 135-1 of the OCT optical system 130 can be reduced, and the operation burden on the examiner is reduced. It is possible to

Further, in the ophthalmologic apparatus 10 according to the first embodiment, the CPU 210 changes and controls the position of the movable range of the reference mirror 132-3 of the OCT optical system 130 according to the acquired magnification of the objective lens ( S8 in FIG.
According to this configuration, it is possible to easily adjust the reference optical path length for obtaining a suitable tomographic image according to the magnification of the objective lens (the working distance based on the magnification of the objective lens). Thereby, when performing magnification of the eye E to be examined and performing optical coherence tomography, the adjustment load of the position of the OCT focus lens 135-1 of the OCT optical system 130 can be reduced, and the operation burden on the examiner is reduced. It is possible to

Second Embodiment
Next, a second embodiment of the present invention will be described.

  The overall configuration of the ophthalmologic apparatus according to the second embodiment is the same as the overall configuration of the ophthalmologic apparatus 10 according to the first embodiment shown in FIG. The internal configurations of the inspection unit 100 and the base unit 600 of the ophthalmologic apparatus 10 according to the second embodiment are the same as the internal configurations of the inspection unit 100 and the base unit 600 in the first embodiment shown in FIG. The internal configuration of the control / processing unit 200 of the ophthalmologic apparatus 10 according to the second embodiment is the same as the internal configuration of the control / processing unit 200 in the second embodiment shown in FIG.

  FIG. 8 is a view showing an example of the change control of the position of the OCT optical system 130 accompanying the magnification change of the objective lens in the ophthalmologic apparatus 10 according to the second embodiment of the present invention. In FIG. 8, the same components as those shown in FIG. 2 are denoted by the same reference numerals. Specifically, FIG. 8 illustrates only a part of the inspection unit 100 of FIG. 2 (more specifically, a part of the OCT optical system 130).

  In FIG. 8A, the inspection unit 100 (more specifically, the OCT optical system 130 when the objective lens 111 with a low magnification (short focal length and wide angle of view) is disposed at a position facing the eye E to be examined. Is a diagram showing the position of. FIG. 8B shows the inspection unit 100 (more specifically, in the case where the objective lens 121 having a higher magnification (long focal length and narrow angle of view) than the objective lens 111 is disposed at a position facing the eye E to be examined. , OCT optical system 130). More specifically, FIGS. 8A and 8B mainly show the position and the reference position of the movable range in the case constituting the inspection unit 100.

  In FIG. 8A, the working distance WD1 is the distance between the eye E and the objective lens 111, which is determined according to the focal length of the low magnification objective lens 111. The reference position SP1 is a reference position on the optical axis of the housing constituting the inspection unit 100 when the low-power objective lens 111 is mounted. The reference position SP1 is, for example, a position at which the beam diameter at the pupil position of the eye to be examined E becomes minimum. The movable range SR1 is a movable range (a movable range) of a housing constituting the inspection unit 100 when the low-magnification objective lens 111 is mounted. By moving the casing for calibrating the inspection unit 100 within the movable range SR1, it is also possible to adjust the inspection unit 100 to the different positions in the longitudinal direction of the eye which are different depending on the subject. It is also possible to adjust the inspection unit 100 against the unexpected back and forth movement of the eye to be examined inside.

  In FIG. 8B, the working distance WD2 is the distance between the eye E and the objective lens 121, which is determined according to the focal length of the high magnification objective lens 121. The reference position SP2 is a reference position on the optical axis of the housing constituting the inspection unit 100 when the high magnification objective lens 121 is mounted. The reference position SP2 is, for example, a position at which the beam diameter at the pupil position of the eye to be examined E becomes minimum. The movable range SR2 is a movable range (a movable range) of a housing constituting the inspection unit 100 when the high magnification objective lens 121 is mounted. By moving the casing for calibrating the inspection unit 100 within the movable range SR2, it is also possible to adjust the inspection unit 100 to the different positions in the longitudinal direction of the eye which are different depending on the subject. It is also possible to adjust the inspection unit 100 against the unexpected back and forth movement of the eye to be examined inside. Further, in FIG. 8B, a focus correction lens 135-1a which is inserted / retracted with respect to the light path L1 of the OCT optical system under the control of the CPU 210 is provided.

  In the present embodiment, objective lenses 111 and 121 of different magnifications that can be disposed at positions facing the eye E, and various parameters shown in FIG. 8 (reference position SP1 and movable range SR1, and reference position SP2 and It is assumed that table information indicating the correspondence with the movable range SR2 is stored in the memory 230 in advance. Then, the CPU 210 acquires various parameters shown in FIG. 8 corresponding to the magnification of the objective lens from the memory 230 according to the magnification of the objective lens detected by the objective lens detection unit 131, and via the stage unit 500 Control is performed to change the position of the movable range and the reference position in the case constituting the inspection unit 100.

  For example, as shown in FIG. 8, when the objective lens disposed at the position facing the eye E is changed from the low power objective lens 111 to the high power objective lens 121, the CPU 210 arranges the objective lens 111. The position of the movable range SR2 of the casing constituting the inspection unit 100 when the objective lens 121 is disposed is the position of the eye E to be examined than the position of the movable range SR1 of the casing constituting the inspection unit 100 at the time of Control to change in the direction away from.

  In addition, although the example mentioned above demonstrated only the change control of the position of the movable range of the housing | casing which comprises the test | inspection part 100, and a reference (standard) position, this embodiment is not limited to this aspect. For example, in addition to the control of changing the position of the movable range of the casing configuring the inspection unit 100 described above and the reference position, the OCT focus lens 135-1 and / or the reference mirror 132 described in the first embodiment The aspect which performs change control of the position of 3 movable ranges, and a reference position is also applicable to this embodiment.

In the ophthalmologic apparatus 10 according to the second embodiment, as in the first embodiment, the CPU 210 acquires the magnification of the objective lens disposed at the position facing the eye E (S2 in FIG. 6). Then, the CPU 210 changes and controls the position of the movable range of the casing constituting the inspection unit 100 including the objective lens and the OCT optical system 130 according to the obtained magnification of the objective lens.
According to this configuration, it is possible to maintain a working distance suitable for each of the plurality of objective lenses with different magnifications. Thereby, when performing magnification of the eye E to be examined and performing optical coherence tomography, it is possible to reduce the adjustment load of the position of the inspection unit 100 including the objective lens and the OCT optical system 130, and the operation load of the examiner It is possible to reduce. Furthermore, according to the ophthalmologic apparatus 10 according to the second embodiment, since the position where the beam diameter is narrowed can be made to coincide with the pupil position of the eye to be examined E, vignetting of the measurement light by the pupil can be prevented.

(Other embodiments)
In the first embodiment and the second embodiment described above, the description has been made using two objective lenses 111 and 121 as a plurality of objective lenses having different magnifications for the sake of simplicity of the description and the like. Is not limited to this. For example, a form using three or more objective lenses as a plurality of objective lenses having different magnifications is also applicable to the present invention. In this case, as in the first and second embodiments described above, a change control of the position of the movable range and the reference position is performed for each objective lens.

The present invention supplies a program that implements one or more functions of the above-described embodiments to a system or apparatus via a network or storage medium, and one or more processors in a computer of the system or apparatus read and execute the program. Can also be realized. It can also be implemented by a circuit (eg, an ASIC) that implements one or more functions.
The program and a computer readable storage medium storing the program are included in the present invention.

  The embodiments of the present invention described above are merely examples of implementation for carrying out the present invention, and the technical scope of the present invention should not be interpreted limitedly by these. It is. That is, the present invention can be implemented in various forms without departing from the technical concept or the main features thereof.

103: optical coupler, 105-1, 105-2: fiber end, 111: low magnification objective lens, 121: high magnification objective lens, 132-3: reference mirror, 134: OCT scanning means, 135-1: OCT Focus lens 135-1a: focus correction lens 135-2, 135-3: lens 137: dispersion compensation glass E: eye to be examined Ef: fundus, WD1, WD2: working distance, FR1, FR2: OCT focus Movable range of lens, FP1, FP2: Reference position of OCT focus lens, GR1, GR2: Movable range of reference mirror, GP1, GP2: Reference position of reference mirror

Claims (17)

An ophthalmologic apparatus in which a plurality of objective lenses having different magnifications are exchangeably configured as an objective lens disposed at a position facing an eye to be examined.
Acquisition means for acquiring the magnification of the objective lens disposed at a position facing the eye to be examined;
A control unit that performs control to change the position of the movable range of the optical system related to optical coherence tomography of the subject's eye according to the acquired magnification of the objective lens;
An ophthalmologic apparatus comprising: The optical system is
A branching member that branches light from a light source into reference light and measurement light;
A focus adjustment member provided between the light source and the objective lens and adjusting the focus of the measurement light with respect to the eye to be examined;
And a reference beam adjusting member for adjusting the optical path length of the reference beam.
The ophthalmologic apparatus according to claim 1, wherein the control unit performs control to change the position of the movable range of the focus adjustment member.   When the objective lens arranged at a position facing the eye to be examined is changed from a first objective lens to a second objective lens having a magnification higher than that of the first objective lens, the control means may The position of the movable range of the focus adjusting member when the second objective lens is arranged is greater than the position of the movable range of the focus adjusting member when the objective lens of 1 is arranged from the objective lens The ophthalmologic apparatus according to claim 2, characterized in that it changes in a direction away from it.   When the objective lens arranged at a position facing the eye to be examined is changed from a first objective lens to a second objective lens having a magnification higher than that of the first objective lens, the control means may Change in which the size of the movable range of the focus adjusting member when the second objective lens is arranged is larger than the size of the movable range of the focus adjusting member when the objective lens 1 is arranged The ophthalmologic apparatus according to claim 2 or 3, further comprising: The optical system is
A branching member that branches light from a light source into reference light and measurement light;
A focus adjustment member provided between the light source and the objective lens and adjusting the focus of the measurement light with respect to the eye to be examined;
And a reference beam adjusting member for adjusting the optical path length of the reference beam.
The ophthalmologic apparatus according to any one of claims 1 to 4, wherein the control unit performs control to change the position of the movable range of the reference light adjustment member.   When the objective lens arranged at a position facing the eye to be examined is changed from a first objective lens to a second objective lens having a magnification higher than that of the first objective lens, the control means may The position of the movable range of the reference light adjustment member when the second objective lens is arranged is the position of the movable range of the reference light adjustment member when the second objective lens is arranged rather than the position of the movable range of the reference light adjustment member when the one objective lens is arranged. The ophthalmologic apparatus according to claim 5, characterized in that it changes in a direction away from the lens. A housing including the objective lens and the optical system is configured;
The ophthalmologic apparatus according to any one of claims 1 to 6, wherein the control unit performs control to change the position of the movable range of the housing.   When the objective lens arranged at a position facing the eye to be examined is changed from a first objective lens to a second objective lens having a magnification higher than that of the first objective lens, the control means may The direction in which the position of the movable range of the housing when the second objective lens is disposed is away from the eye to be examined than the position of the movable range of the housing when the one objective lens is disposed. The ophthalmologic apparatus according to claim 7, wherein   The control means performs control to move the optical system within the range of the movable range when the position of the optical system is located outside the range of the movable range. The ophthalmologic apparatus according to any one of to 8.   The ophthalmologic apparatus according to any one of claims 1 to 9, wherein the control means sets a reference position of the optical system within a range of the movable range.   The control means performs control to move the optical system to the reference position within the range of the movable range when the position of the optical system is located outside the range of the movable range. The ophthalmologic apparatus according to claim 10.   11. The ophthalmologic apparatus according to claim 9, wherein the control means controls the position of the optical system to stay within the movable range. The control means sets a reference position of the reference light adjustment member within the movable range.
When the objective lens disposed at the position facing the eye to be examined is changed, the amount of change in the reference position of the reference light adjustment member according to the change corresponds to the objective lens and the eye to be examined according to the change The ophthalmologic apparatus according to claim 5, wherein the ophthalmologic apparatus is smaller than a change amount in the distance of.   When the objective lens arranged at a position facing the eye to be examined is changed from a first objective lens to a second objective lens having a magnification higher than that of the first objective lens, the control means may The reference position of the reference light adjusting member when the second objective lens is arranged is changed to a direction away from the objective lens when the second objective lens is arranged than the reference position of the reference light adjusting member when the objective lens 1 is arranged. The ophthalmologic apparatus according to claim 13, characterized in that: The control means sets a reference position of the focus adjustment member within the movable range.
The optical system further includes a focus correction member provided in an optical path of the measurement light so that a reference position of the focus adjustment member does not change with respect to a specific diopter of the eye to be inspected. The ophthalmologic apparatus according to any one of claims 2 to 4, wherein: It is a control method of an ophthalmologic apparatus in which a plurality of objective lenses having different magnifications can be replaced as an objective lens disposed at a position facing an eye to be examined.
An acquiring step of acquiring a magnification of the objective lens disposed at a position facing the eye to be examined;
A control step of performing control of changing a position of a movable range of an optical system related to optical coherence tomography of the subject's eye according to the acquired magnification of the objective lens;
And a control method of an ophthalmologic apparatus. A program for causing a computer to execute a control method of an ophthalmologic apparatus in which a plurality of objective lenses having different magnifications are exchangeably configured as an objective lens disposed at a position facing an eye to be examined.
An acquiring step of acquiring a magnification of the objective lens disposed at a position facing the eye to be examined;
A control step of performing control of changing a position of a movable range of an optical system related to optical coherence tomography of the subject's eye according to the acquired magnification of the objective lens;
A program to make a computer run.