JP2019063238A - Ophthalmologic apparatus - Google Patents

Abstract

To provide an ophthalmologic apparatus capable of appropriately performing an objective inspection on a state on an eye position.SOLUTION: An ophthalmologic apparatus comprising an anterior eye part imaging unit 50, a fixed visual target presentation unit, and a control unit 71 images an anterior eye part picture of at least one of a left eye and right eye of a subject. The fixed visual target presentation unit presents a fixed visual target on the at least one of the left eye and right eye of the subject. The control unit 71 processes the anterior eye part picture imaged by the anterior eye part imaging unit 50 to measure an eye position of the subject's eye. The control unit 71 generates eye position state information showing a state of the eye position of the subject's eye, on the basis of eye position measurement results at at least two points of timing including timing after presentation switching time at which presentation and non-presentation of the fixed visual target to the at least one of the left eye and right eye are switched and timing before the presentation switching time.SELECTED DRAWING: Figure 2

Description

  The present disclosure relates to an ophthalmologic apparatus that inspects a visual function of a subject.

  Conventionally, various ophthalmologic apparatuses for inspecting the visual function of a subject are known. For example, in the subjective optometry apparatus described in Patent Document 1, a correction optical system capable of correcting the refractive power is individually disposed in front of the subject's eye, and the test target is placed on the subject via the correction optical system. Project light onto the fundus. The examiner receives the response of the subject and measures the refractive power of the subject's eye by adjusting the correction optical system until the subject can properly view the target. Moreover, the subjective-type optometry apparatus described in Patent Document 2 forms the test target image through the correction optical system in front of the subject's eye, thereby arranging the correction optical system in front of the subject's eye Measure the refractive power. The visual function of the subject also has a function related to the eye position which is the direction in which the eye is facing, in addition to the refractive power.

JP-A-5-176893 U.S. Pat. No. 3,874,774

  In the prior art, it is difficult to objectively inspect the condition regarding the eye position. For example, one of the states related to eye position is oblique. For example, a cover uncover test is known as a method of checking the presence or absence of an oblique position. In the cover uncover test, the cover covering the field of view of one eye is removed, and the examiner visually checks the movement of the eye at that time to check for the presence or absence of obliqueness. In this method, in addition to requiring examination for examination, it is also difficult to quantitatively show the examination results. In addition, there is also a method of performing an oblique test by adding a prism by an optometry apparatus, but since it is a subjective test, depending on the response of the subject, the test result may not be stable or the time for the test It may be necessary.

  The typical object of the present disclosure is to provide an ophthalmologic apparatus capable of appropriately performing an objective examination of an eye position-related condition.

  A first aspect of an ophthalmologic apparatus provided by an exemplary embodiment of the present disclosure is an ophthalmologic apparatus for examining a visual function of a subject, wherein at least one of the left eye and the right eye of the subject is An anterior segment imaging unit configured to capture an eye image, a fixation target presenting unit configured to present a fixation target to at least one of the left eye and the right eye of the subject, and a control unit that controls the ophthalmologic apparatus And the control unit measures at least one eye position of the left eye and the right eye of the subject by processing the anterior segment image photographed by the anterior segment photographing unit. And at least two timings including a timing after presentation switching when presentation and non-presentation of the fixation target to at least one of the left eye and right eye of the subject is switched, and a timing before the presentation switching. Position of eye to be examined at one timing Based on the measurement result, it generates the eye position status information indicating the status of the eye position of the eye being tested.

  A second aspect of an ophthalmologic apparatus provided by an exemplary embodiment of the present disclosure is an ophthalmologic apparatus used to perform an examination of a visual function of a subject, wherein the left eye and the right eye of the subject An anterior segment imaging unit configured to capture at least one anterior segment image, a fixation target presenting unit configured to present a fixation target to at least one of the left eye and the right eye of the subject, and control of the ophthalmologic apparatus A control unit to control the at least one of the left eye and the right eye of the subject by processing the anterior segment image captured by the anterior segment imaging unit. The position is measured at a plurality of timings, and data of an eye position change graph showing the relationship between the measured eye position and time is generated.

  According to the ophthalmologic apparatus according to the present disclosure, objective inspection of the state regarding the eye position is appropriately performed.

FIG. 1 is an external perspective view of an ophthalmologic apparatus 1; It is a figure which shows the structure of 7 L of measurement parts for left eyes. It is the schematic block diagram which looked at the inside of the ophthalmologic apparatus 1 of this embodiment from the front direction (A direction of FIG. 1). It is the schematic block diagram which looked at the inside of the ophthalmologic apparatus 1 of this embodiment from the right side surface direction (the B direction of FIG. 1). It is the schematic block diagram which looked at the inside of the ophthalmologic apparatus 1 of this embodiment from upper direction (C direction of FIG. 1). It is a figure which shows an example of the anterior ocular segment image 110 of a right eye of a subject. FIG. 17 is a schematic diagram showing the eye position before the presentation of the fixation target 31K to the eye to be examined is switched to non-presentation in the oblique examination. FIG. 18 is a schematic diagram showing the eye position after a sufficient time has elapsed since the presentation of the fixation target 31K to the test target eye was switched to non-presentation in the oblique examination. It is a figure which shows an example of an eye position change graph. It is the figure which compared the eye position change graph and the optical characteristic change graph in the same time zone. It is a histogram which shows the measurement frequency for every value of an eye position measurement result.

<Overview>
The ophthalmologic apparatus exemplified in the present disclosure includes an anterior segment imaging unit, a fixation target presenting unit, and a control unit. The anterior segment imaging unit captures an anterior segment image of at least one of the left eye and the right eye of the subject. The fixation target presenting unit causes the fixation target to be focused by presenting the fixation target to at least one of the left eye and the right eye of the subject. The control unit measures at least one eye position of the left eye and the right eye of the subject by processing the anterior segment image captured by the anterior segment imaging unit. The eye position is the direction in which the eyes turn. The control unit performs the examination at at least two timings including the timing after the presentation switching time when presentation and non-presentation of the fixation target to at least one of the left eye and the right eye is switched and the timing before the presentation switching time. Based on the measurement result of the eye position of the target eye, eye position state information indicating the state of the eye position of the eye to be examined is generated.

  According to the ophthalmologic apparatus exemplified in the present disclosure, eye position state information indicating the state of the eye position before and after the presentation switching of the fixation target is obtained based on the anterior segment image. Therefore, objective examination of the condition regarding eye position is appropriately performed.

  In addition, the specific method for measuring an eye position from an anterior ocular segment image can be selected suitably. For example, the control unit may detect the pupil position of the eye by processing the anterior segment image, and may measure the eye position based on the detected pupil position. In this case, the pupil position may be any part of the pupil. For example, at least one of the central position of the pupil and the position of the outer peripheral end of the pupil may be detected as the pupil position. Also, the eye position may be measured based on the interpupillary distance of the left eye and the right eye.

  The control unit may detect the corneal apex position of the eye by processing the anterior segment image, and may measure the eye position based on the detected corneal apex position. The corneal apex position may be detected based on, for example, the position of the detected target image by detecting the target image projected onto the eye. Also, the eye position may be measured based on the distance between the corneal apexes of the left eye and the right eye.

  The control unit may detect the pupil position and the corneal apex position of the eye by processing the anterior segment image and measure the eye position based on the detected pupil position and the corneal apex position. In this case, for example, the eye position may be measured based on the deviation between the pupil center position and the corneal apex position. Note that the absolute value of the eye position does not necessarily have to be measured, as long as at least a change in eye position can be determined based on the measurement result.

  The control unit may generate, as eye position information, data of an eye position change graph indicating at least the relationship between the eye position of the eye to be examined and the time after the presentation switching. In this case, the temporal change in the eye position of the examination target eye caused by switching between the presentation and non-presentation of the fixation target is appropriately grasped by the eye position change graph. In addition, the examiner can also make a diagnosis of the presence or absence of obliqueness or the like by looking at the eye position change graph. However, the ophthalmologic apparatus may generate only the eye position shift amount (described later) without generating the eye position change graph.

  The control unit may cause the display unit to display the eye position change graph. In this case, the control unit may continuously measure the eye position during the examination of the eye position of the eye to be examined, and display the eye position change graph on the display unit in real time during the examination. In addition, the control unit may generate data of the eye position change graph after the examination based on the anterior eye part images taken continuously during the examination.

  Further, the eye position change graph may be, for example, a graph in which measurement results of a plurality of eye positions are plotted at each measurement timing, or a graph of an approximate curve generated based on the measurement results of a plurality of eye positions. It may be.

  The control unit determines the amount of deviation between the measurement result of the eye position of at least one before switching timing before the presentation switching of the fixation target and the measurement result of the eye position of at least one after switching timing after the presentation switching. , Eye position information may be generated.

  In this case, the displacement amount of the eye position resulting from switching between the presentation and non-presentation of the fixation target is quantitatively grasped. Therefore, for example, diagnoses regarding the eye position such as the presence or absence of oblique position are performed more appropriately. However, the ophthalmologic apparatus may generate only the eye position change graph without generating the eye position shift amount.

  The control unit may generate the eye position deviation amount based on the measurement result of the eye position at at least one post-switching timing after the reference timing when the standby time has elapsed from the presentation switching time of the fixation target. The eye position in the presence of the oblique position tends to be stable with the passage of time after changing gradually after switching between the presentation and non-presentation of the fixation target. Therefore, when the measurement result of the eye position immediately after the display of the fixation target is switched to the non-presentation is used, the displacement amount of the generated eye position tends to be an inappropriate value. On the other hand, by using the measurement result of the eye position after the waiting time has elapsed, the accuracy of the generated eye position shift amount is improved. The length of the waiting time may be set longer than the time required for the change in the eye position of the eye to be examined to stabilize after switching between the presentation and non-presentation of the fixation target. In this case, the eye position shift amount is calculated based on the eye position in the stable state. In the ophthalmologic apparatus, one or more waiting times may be preset.

  The control unit may receive an input of an instruction to specify the reference timing, and set the reference timing in accordance with the input instruction. In this case, the examiner can set the reference timing to a desired timing according to various circumstances (for example, his / her experience, the condition of the subject's eye, etc.).

  In addition, the specific method for receiving the designation | designated instruction | indication of a reference | standard timing can be selected suitably. For example, the control unit may receive the designation instruction of the reference timing by causing the user (for example, an examiner) to designate the length of the standby time from the presentation switching time of the fixation target to the reference timing. In addition, in the case where the designation instruction of the reference timing is received in real time during the inspection, the control unit may set the timing when the designation instruction is input as the reference timing.

  In addition, the control unit may receive input of a reference timing designation instruction in a state in which the eye position change graph is displayed on the display unit. In this case, the examiner can specify the reference timing as the appropriate timing after grasping the state of the change in eye position by the eye position change graph. The display of the eye position change graph and the setting of the reference timing may be performed in real time during the examination, or may be performed after the examination. When the display of the eye position change graph and the setting of the reference timing are performed after the examination, the control unit may receive the input of the reference timing designation instruction by causing the user to specify the desired timing on the eye position change graph. .

  Further, when the designated timing is set as the reference timing, a period may be provided in which the setting of the reference timing is prohibited. For example, after switching between presentation and non-presentation of a fixation target, a reference time is elapsed until the minimum waiting time (for example, one second or more) necessary for the change in the eye position of the examination target eye to stabilize. It may be a period during which setting of timing is prohibited. In this case, the examiner can designate the reference timing only after the minimum waiting time necessary for stabilizing the change in eye position has elapsed. Therefore, the eye position shift amount is easily calculated based on the eye position in the stable state.

  The control unit detects a timing at which the eye position of the eye to be examined is stable after the presentation switching time based on the measurement results of the eye positions at a plurality of post-switching timings, and sets the detected timing as a reference timing. It is also good. In this case, the appropriate reference timing is automatically set by the ophthalmologic apparatus.

  In addition, the specific method for detecting the timing in which the eye position was stabilized can be selected suitably.

  For example, the control unit may detect the fluctuation of the measurement result from the measurement results of the eye position at the plurality of post-switching timings. The control unit may detect the timing at which the detected fluctuation is equal to or less than the threshold as the timing at which the eye position is stabilized. For the fluctuation of the measurement result, for example, at least one of the standard deviation of the plurality of measurement results in the unit time, the difference between the maximum value and the minimum value of the plurality of measurement results in the unit time, and the frequency of the fluctuating measurement result You may use. In this case, the timing at which the eye position is stabilized is appropriately detected based on the fluctuation of the detection result. The control unit may output information on fluctuation of the detected measurement result as eye position state information. In this case, the examiner can more appropriately determine the state of the eye position of the eye to be examined.

  Further, the control unit may generate data of an approximate curve indicating the relationship between the eye position and the time from the measurement results of the eye position at the plurality of post-switching timings. The control unit may detect the timing at which the slope of the approximate curve becomes equal to or less than the threshold as the timing at which the eye position is stabilized. In this case, the timing at which the eye position is stabilized is appropriately detected based on the approximate curve that indicates the change in eye position. As described above, the control unit may output data of the generated approximate curve as eye position information.

  The ophthalmologic apparatus may include an objective measurement unit. The objective measurement unit emits measurement light to the examination target eye and receives the reflected light to objectively measure the optical characteristics of the examination target eye. The control unit detects a timing at which the eye position of the test target eye after the presentation switch is stabilized based on the measurement results of the optical characteristics of the test target eye measured at a plurality of post-switching timings, and detects the detected timing as a reference timing. It may be set as When the eye position is stabilized, the optical characteristics of the eye to be examined are easily stabilized. Therefore, by setting the timing at which the optical characteristics of the eye to be examined are stabilized as the reference timing, the appropriate reference timing is automatically set.

  In addition, the specific method for detecting the timing which the eye position was stabilized based on the measurement result of an optical characteristic can also be selected suitably.

  For example, from the measurement results of the optical characteristics at a plurality of post-switching timings, the control unit may cause fluctuations in the measurement results (for example, standard deviations of a plurality of measurement results in a unit time and maximum values of a plurality of measurement results in a unit time). The difference between the minimum values and / or the frequency of the fluctuating measurement result may be detected. The control unit may detect the timing at which the detected fluctuation is equal to or less than the threshold as the timing at which the eye position is stabilized. The control unit may output information on fluctuation of the measurement result of the optical characteristic.

  Further, the control unit may generate data of an approximate curve indicating the relationship between the optical characteristic and the time from the measurement results of the optical characteristic at the plurality of post-switching timings. The control unit may detect the timing at which the slope of the approximate curve becomes equal to or less than the threshold as the timing at which the eye position is stabilized. Note that the control unit may output data of an approximate curve indicating a change in the measurement result of the optical characteristic.

  For example, the refractive power of the eye to be examined may be used as the optical characteristic used to detect the stability of the eye position. The eye position stability may be detected by objective measurement results other than the refractive power (for example, the size of the pupil of the eye to be examined). In addition, the stability of the eye position may be detected based on both the measurement result of the eye position and the measurement result of the optical property.

  When the control unit detects timing at which the eye position is stable (hereinafter referred to as “eye position stabilization timing”) based on the measurement result of at least one of the eye position and the optical characteristics, the control unit Information on the time until the eye position stabilization timing may be output. In this case, the examiner can grasp the state of the eye position of the eye to be examined more appropriately.

  The control unit specifies an average value, an intermediate value between the maximum value and the minimum value, or a mode value with the highest measurement frequency from a plurality of eye position measurement results measured at a plurality of post-switching timings after the reference timing. May be The control unit may calculate, as eye position state information, the specified value and the deviation amount of the eye position measurement result at the timing before switching. In this case, the eye position shift amount is calculated while the influence of eye position change is further suppressed.

  It is needless to say that an average value, an intermediate value or a mode value of a plurality of eye position measurement results may be used as the measurement result of the pre-switching timing before the presentation switching time of the fixation target. The eye position shift amount may be calculated based on at least one of the eye position measurement result at one post-switching timing and the eye position measurement result at one pre-switching timing.

  The control unit uses the plurality of eye position measurement results at the plurality of pre-switching timings and the first mode value having the highest frequency measured before the presentation switching time from the plurality of eye position measurement results at the plurality of post-switching timings. The second mode may be specified that has the highest frequency measured after the presentation switching time. The control unit may calculate the deviation amount between the first mode value and the second mode value as eye position state information. In this case, the shift amount between the eye position in the stable state before the presentation switching of the fixation target and the eye position in the stable state after the presentation switching of the fixation target is appropriately calculated. Thus, the accuracy of the generated (calculated) eye position shift amount is improved.

  The control unit may acquire the presentation switching time when the fixation target is switched between presentation and non-presentation, and may generate eye position state information based on the acquired presentation switching time. In this case, highly accurate eye position information based on the presentation switching time is generated.

  In addition, the specific method for acquiring presentation switching time can be selected suitably. For example, the control unit may acquire the presentation switching time by receiving an input of an instruction from the user for specifying the presentation switching time. When the visible light blocking member is switched between presentation and non-presentation of the fixation target, the control unit changes the intensity of invisible light received by the anterior segment imaging unit due to insertion and removal of the visible light blocking member The presentation switching time may be acquired by detecting the point in time of the display by image processing or the like. The ophthalmologic apparatus may include a sensor that detects that the visible light blocking member has been inserted or removed. In addition, control is performed when switching means for switching between presentation and non-presentation of fixation targets (for example, a display capable of presenting fixation targets, or an actuator for driving a target plate including fixation targets, etc.) is provided. The unit may acquire, as the presentation switching time, a point in time when the switching means switches between presentation and non-presentation of the fixation target.

  The anterior segment imaging unit may capture an anterior segment image by receiving invisible light. Further, the visible light blocking member may be inserted and removed in front of the eye to switch between presenting and not presenting the fixation target. The visible light blocking member transmits at least a part of the invisible light received by the anterior segment imaging unit and blocks visible light presented by the fixation target.

  In this case, the anterior segment imaging unit uses the invisible light that passes through the visible light blocking member to measure the eye position of the eye that switches between presenting and not presenting the fixation target. The anterior segment can be photographed appropriately before and after the presentation switching of the target. Furthermore, when stopping the presentation of the fixation target, the visible light blocking member is inserted in front of the eye. Therefore, unlike the case where the presentation of the fixation target is blocked inside the ophthalmologic apparatus, the possibility that the subject's eye gazes at a part of the apparatus after the presentation stop is low. Therefore, after the presentation of the fixation target is stopped, the fixation is properly released.

  In addition, it is also possible to change the method of switching between presentation and non-presentation of fixation targets. For example, the ophthalmologic apparatus may switch between presentation and non-presentation of a fixation target by controlling a display capable of displaying the fixation target and switching between display and deletion of the fixation target on the display. In addition, the ophthalmologic apparatus may switch between presentation and non-presentation of a fixation target by driving a target plate provided with the fixation target by an actuator (for example, a motor or the like). The ophthalmologic apparatus may switch between presentation and non-presentation of the fixation target by a polarization element provided in the presentation light path of the fixation target. Also, instead of inserting and removing the visible light blocking member in front of the eye, the display and non-presentation of the fixation target may be switched by inserting and removing the translucent member transmitting only a part of the visible light in front of the eye . Even when the translucent member is inserted in front of the eye, the fixation target seen from the subject's eye is blurred, so the presentation and non-presentation of the fixation target can be appropriately switched.

  The control unit may store the data of the anterior segment image used for the measurement of the eye position in the storage unit. The control unit may receive an input of an instruction to specify the imaging timing of the anterior segment image captured in the past, and may cause the display unit to display the anterior segment image captured at the designated imaging timing. In this case, the examiner can easily compare the measurement result of the eye position at the desired timing with the anterior segment image used for the measurement of the eye position. Therefore, the examiner can make an appropriate determination after confirming the anterior segment image used for the measurement of the eye position, for example, when there is a question about the measurement result of the eye position.

  The ophthalmologic apparatus may adopt only a part of the plurality of techniques exemplified in the present disclosure. For example, the ophthalmologic apparatus may create eye position change graph data indicating the relationship between eye position and time regardless of the presentation and non-presentation of the fixation target. Specifically, the ophthalmologic apparatus may create an eye position change graph during presentation of the fixation target, or may create an eye position change graph after a predetermined time has elapsed from the stop of presentation of the fixation target. Good. Even in this case, the examiner can appropriately grasp the temporal change of the eye position by the eye position change graph.

Embodiment
Hereinafter, one of the typical embodiments of the present disclosure will be described with reference to the drawings. As an example, in the present embodiment, in addition to the objective examination of the state regarding the eye position of the subject's eye, subjective and objective measurements of optical characteristics (for example, refractive power etc.) of the subject's eye are also performed The ophthalmologic apparatus 1 which can be illustrated is illustrated. However, at least a part of the techniques exemplified in the present disclosure can also be applied to, for example, an ophthalmologic apparatus that performs only an objective examination of a state related to eye position, and one of subjective measurement and objective measurement of optical characteristics. It is applicable also to the ophthalmologic apparatus which does not have the structure for implementing. The ophthalmologic apparatus may also be able to test visual functions other than the functions related to the eye position and the optical characteristics among the visual functions of the subject.

(Schematic configuration)
The schematic configuration of the ophthalmologic apparatus 1 of the present embodiment will be described with reference to FIG. The ophthalmologic apparatus 1 according to the present embodiment includes a housing 2, a presentation window 3, a touch panel (an operation unit and a display unit) 4, a chin 5, a base 6, an imaging optical system 100 and the like. The housing 2 accommodates various members inside. For example, inside the housing 2, a measurement unit 7 (a measurement unit 7L for the left eye and a measurement unit 7R for the right eye) described later is provided. The presentation window 3 is used to present a target to a subject. For example, target luminous fluxes emitted from the left-eye measurement unit 7L and the right-eye measurement unit 7R are projected onto the subject's eye through the presentation window 3.

  The touch panel 4 displays an image and is operated by the user. That is, in the present embodiment, the touch panel 4 doubles as an operation unit that a user (for example, an examiner or the like) operates to input various instructions and a display unit (display) that displays an image. However, it goes without saying that the operation unit and the display unit may be provided separately. The operation unit outputs a signal corresponding to the input operation instruction to a control unit 70 (see FIG. 2) described later. For the operation unit, for example, at least one of a mouse, a joystick, and a keyboard may be used. The display unit may be mounted on the main body of the ophthalmologic apparatus 1 or may be provided separately from the ophthalmologic apparatus 1. For example, various data (for example, an eye position change graph to be described later, an eye position shift amount, and the like) may be displayed on the display of a personal computer (hereinafter, referred to as "PC") connected to the ophthalmologic apparatus 1. Multiple display units may be used in combination.

  The jaw base 5 supports the subject's jaw. Since the jaw of the subject is placed on the chin 5, the distance between the eye of the subject and the ophthalmologic apparatus 1 is kept constant, and the movement of the face of the subject is suppressed. Instead of the jaw base 5, a forehead or a face may be used. A jaw base 5 and a housing 2 are fixed to the base 6. The photographing optical system 100 includes a photographing element and a lens (not shown). The photographing optical system 100 can photograph the face of a subject.

(Measurement section)
The configuration of the measurement unit 7 will be described with reference to FIG. In the present embodiment, the configuration of the left-eye measurement unit 7L and the configuration of the right-eye measurement unit 7R are substantially the same. Therefore, in the following, the left eye measurement unit 7L will be described, and the description of the right eye measurement unit 7R will be omitted. The left-eye measurement unit 7L includes a subjective measurement unit 25, an objective measurement unit 10, a first index projection optical system 45, a second index projection optical system 46, and an anterior segment imaging unit 50.

(Aware sense type measurement part)
The subjective measurement unit 25 is used to measure the optical characteristics of the subject's eye in response to the subject's response. That is, the optical characteristic of the subject's eye is subjectively measured by the subjective type measurement unit 25. In the present embodiment, as one example, among the optical characteristics (eye refractive power, contrast sensitivity, binocular vision function, etc.) of the subject's eye, the eye refractive power is measured by the subjective measurement unit 25. The subjective measurement unit 25 of the present embodiment includes a projection optical system (target projection system) 30, a correction optical system 60, and a correction optical system 90.

  The projection optical system 30 projects the target luminous flux toward the subject's eye. The light projecting optical system 30 of the present embodiment includes a display 31, a light projecting lens 33, a light projecting lens 34, a reflecting mirror 36, a dichroic mirror 35, a dichroic mirror 29, and an objective lens 14. The target luminous flux is emitted from the display 31, and then passes through the respective optical members in the order of the light projection lens 33, the light projection lens 34, the reflection mirror 36, the dichroic mirror 35, the dichroic mirror 29, and the objective lens 14. It is projected to the subject's eye.

  The display 31 displays, for example, a test target such as a Landolt ring target, and a fixation target for fixing the subject's eye (used at eye position measurement and objective measurement described later), etc. Ru. The target luminous flux emitted from the display 31 is projected toward the subject's eye. That is, the display 31 and the light projecting optical system 30 of the present embodiment are an example of a fixation target presenting unit that presents a fixation target to the subject's eye. For the display 31, for example, various display devices such as an LCD can be used. In addition, it is also possible to change the configuration and method for presenting a fixation target to the subject's eye. For example, in the present embodiment, the light flux of the fixation target is projected separately to the left eye and the right eye of the subject. However, the ophthalmologic apparatus 1 may present one fixation target to both the left eye and the right eye. The ophthalmologic apparatus 1 may present the fixation target to the subject's eye by positioning the fixation target provided on the target plate on the optical path.

  The correction optical system 60 includes an astigmatism correction optical system 63 and a drive mechanism 39. The astigmatism correction optical system 63 is disposed between the light projection lens 33 and the light projection lens 34. In the present embodiment, the astigmatic correction optical system 63 is used to correct the cylindrical power, cylindrical axis, and the like of the subject's eye. For example, the astigmatism correction optical system 63 includes two positive cylindrical lenses 61a and 61b having equal focal lengths. The cylindrical lenses 61a and 61b are independently rotated about the optical axis L2 by being driven by each of the rotation mechanisms 62a and 62b. It is also possible to change the configuration of the astigmatism correction optical system 63. For example, the cylindrical power and the like may be corrected by inserting and removing the correcting lens into the light path of the light projecting optical system 30.

  The drive mechanism 39 includes a motor and a slide mechanism, and moves the display 31 in the direction of the optical axis L2. For example, by moving the display 31 at the time of subjective measurement, the presentation position (presentation distance) of the visual target with respect to the subject's eye is optically changed. As a result, the spherical power is corrected. In addition, when the display 31 is moved at the time of objective measurement, the subject's eye is fogged. In addition, it is also possible to change the configuration for correcting the spherical power. For example, the spherical power may be corrected by inserting and removing the optical element in the optical path. In addition, the spherical power may be corrected by moving the lens disposed in the optical path in the optical axis direction.

  In the present embodiment, the correction optical system 60 that corrects the spherical power, the cylindrical power, and the cylindrical axis is illustrated. However, the correction optical system may correct other optical characteristics (for example, a prism value etc.). Correcting the prism value allows the target luminous flux to be properly projected onto the subject's eye even if the subject's eye is an oblique eye.

  Further, in the present embodiment, the astigmatism correction optical system 63 for correcting the cylindrical power and the cylindrical axis, and the drive mechanism 39 for correcting the spherical power are separately provided. However, spherical power, cylindrical power, and cylindrical axis may be corrected by the same configuration. For example, spherical power, cylindrical power, and cylindrical axes may be corrected by an optical system that modulates the wavefront. In addition, a lens disc having a plurality of optical elements (for example, at least one of a spherical lens, a cylindrical lens, and a dispersion prism) disposed on the same circumference, and an actuator for rotating the lens disc are used as a correction optical system. It may be done. In this case, various optical characteristics are corrected by rotating the lens disc and switching the optical element located on the optical axis L2. In addition, an optical element (for example, at least one of a cylindrical lens, a cross cylinder lens, a rotary prism, and the like) disposed on the optical axis L2 may be rotated by the actuator.

  The correction optical system 90 is disposed between the objective lens 14 and a deflection mirror 81 (see FIG. 3 etc.) described later. The correction optical system 90 may be used, for example, to correct an optical aberration generated in the subjective measurement unit 25. The correction optical system 90 may also be used to correct astigmatism in the optical aberration. The correction optical system 90 of the present embodiment includes two positive cylindrical lenses 91 a and 91 b having equal focal lengths. The cylindrical lenses 91a and 91b are independently rotated about the optical axis L3 by being driven by each of the rotation mechanisms 92a and 92b. The correction optical system 90 can correct astigmatism by adjusting the cylindrical power and the cylindrical axis. It is also possible to change the configuration of the correction optical system 90. For example, the optical aberration may be corrected by inserting or removing the correction lens into the optical path LE. The correction optical system 60 may also be used as the correction optical system 90. In this case, the correction optical system 60 is driven by considering the amount of astigmatism in addition to the cylindrical power and the cylindrical axis.

(Objective measurement unit)
The objective measurement unit 10 is used to objectively measure the optical characteristics of the subject's eye. The objective measurement unit 10 may measure, for example, at least one of an eye refractive power, an eye axial length, and a corneal shape as optical characteristics of the subject's eye. As an example, in the present embodiment, an objective type measurement unit 10 for measuring the eye refractive power of the subject's eye is described as an example.

  The objective measurement unit 10 includes a projection optical system (light projection optical system) 10 a, a light receiving optical system 10 b, and a correction optical system 90. As an example, the projection optical system 10a of the present embodiment projects spot-like measurement light onto the fundus of the subject's eye via the pupil center of the subject's eye. In addition, the light receiving optical system 10b of the present embodiment takes out the reflected light of the measurement light reflected from the fundus in a ring shape through the pupil peripheral portion, and takes a ring-shaped fundus reflected image by the two-dimensional imaging element 22 .

  The projection optical system 10 a of the present embodiment includes a measurement light source 11, a relay lens 12, a hole mirror 13, a prism 15, a drive unit (motor) 23, a dichroic mirror 35, a dichroic mirror 29, and an objective lens 14. The prism 15 is a light beam deflection member. The drive unit 23 rotationally drives the prism 15 about the optical axis L1. The light source 11 is in a conjugate relationship with the fundus of the subject's eye. The hole portion of the hole mirror 13 is in a conjugate relationship with the pupil of the subject's eye. The prism 15 is disposed at a position deviated from a position that is conjugate with the pupil of the subject's eye, and decenters the passing light beam with respect to the optical axis L1. In addition, it is also possible to change the structure of a light beam deflection | deviation member. For example, in place of the prism 15, a plane parallel plate disposed obliquely to the optical axis L1 may be used as the light beam deflection member.

  The dichroic mirror 35 causes the optical axis L2 of the subjective measurement unit 25 and the optical axis L1 of the objective measurement unit 10 to be coaxial. The beam splitter 29 reflects the luminous flux in the subjective measurement unit 25 and the luminous flux in the objective measurement unit 10 and guides the reflected light to the subject's eye.

  The light receiving optical system 10b shares the objective lens 14, the dichroic mirror 29, the dichroic mirror 35, the prism 15, and the hole mirror 13 with the projection optical system 10a. The light receiving optical system 10 b further includes a relay lens 16, a mirror 17, a light receiving diaphragm 18, a collimator lens 19, a lens lens 20, and a two-dimensional imaging element 22 on the optical path in the reflection direction of the hole mirror 13. The light receiving diaphragm 18 and the two-dimensional imaging element 22 have a conjugate relationship with the fundus of the subject's eye. The ring lens 20 includes a lens portion formed in a ring shape and a light shielding portion provided in an area other than the lens portion. The ring lens 20 is in a conjugate relationship with the pupil of the subject's eye. The output from the two-dimensional imaging device 22 is input to the control unit 70.

  The reflected light of the measurement light emitted from the projection optical system 10a and reflected by the fundus of the subject's eye is reflected by the dichroic mirror 29, further reflected by the dichroic mirror 35, and guided to the light receiving optical system 10b. Further, the dichroic mirror 29 transmits the anterior eye imaging light and the alignment light, which will be described later, and guides the light to the anterior eye imaging unit 50.

  In the present embodiment, the measurement light source 11 of the projection optical system 10a, the light receiving stop 18 of the light receiving optical system 10b, the collimator lens 19, the ring lens 20, and the two-dimensional imaging element 22 move integrally in the optical axis direction. Can. As an example, in the present embodiment, a drive unit 95 including the display 31, the measurement light source 11 of the projection optical system 10a, the light receiving stop 18 of the light receiving optical system 10b, the collimator lens 19, the ring lens 20, and the two-dimensional imaging element 22. Are integrally moved in the direction of the optical axis L1 by the drive mechanism 39. However, at least a part of the plurality of configurations described above may be moved by a configuration different from the drive mechanism 39. The drive unit 95 is moved in the optical axis direction such that the outer ring luminous flux is incident on the two-dimensional imaging element 22 in each longitudinal direction. That is, the spherical refraction error is corrected by moving a part of the objective measurement unit 10 in the direction of the optical axis L1 according to the spherical refraction error (spherical power) of the subject's eye, and the measurement light source 11, the light receiving stop 18, and the two-dimensional imaging element 22 are in a conjugate relationship with the fundus of the subject's eye. The movement position of the drive unit 95 is detected by a potentiometer (not shown). The hole mirror 13 and the ring lens 20 are disposed so as to be conjugate with the pupil of the subject's eye at a constant magnification, regardless of the amount of movement of the drive unit 95.

  In the present embodiment, the measurement light emitted from the measurement light source 11 passes through the relay lens 12, the hole mirror 13, the prism 15, the dichroic mirror 35, the dichroic mirror 29, and the objective lens 14 onto the fundus of the subject's eye. A spot-like point light source image is formed. During this time, the pupil projected image (projected light flux on the pupil) of the hole portion of the hole mirror 13 is eccentrically rotated at high speed by the prism 15 which rotates around the optical axis L1. The point light source image projected onto the fundus is reflected and scattered and emitted from the subject's eye. The light emitted from the subject's eye is collected by the objective lens 14 and is positioned at the light receiving diaphragm 18 via the dichroic mirror 29, the dichroic mirror 35, the prism 15, the hole mirror 13, the relay lens 16 and the mirror 17. It will be collected again. Next, a ring-shaped image is formed on the two-dimensional imaging element 22 by the collimator lens 19 and the ring lens 20.

  The prism 15 is disposed in a common optical path of the projection optical system 10a and the light receiving optical system 10b. Therefore, both the projection light (measurement light) emitted from the projection optical system 10 a and the reflected light from the fundus pass through the prism 15. As a result, the reflected light from the fundus is reverse scanned as if there was no decentering of the projection light and the reflected light on the pupil. Further, in the present embodiment, the correction optical system 90 is shared between the objective measurement unit 10 and the subjective measurement unit 25. Needless to say, the correction optical system used in the objective measurement unit 10 and the correction optical system used in the subjective measurement unit 25 may be separately provided.

  Note that it is also possible to change the configuration of the objective measurement unit 10 in the present embodiment. For example, the objective measurement unit projects a ring-shaped measurement index from the periphery of the pupil to the fundus, extracts the fundus reflection light from the center of the pupil, and causes the two-dimensional imaging element 22 to receive the ring-shaped fundus reflection image. May be provided. In addition, the objective type measurement unit may include a Shack-Hartmann sensor, or may have a configuration of a phase difference type that projects a slit.

(First index projection optical system / second index projection optical system)
The first index projection optical system 45 and the second index projection optical system 46 are, for example, disposed between the correction optical system 90 and the deflection mirror 81 (see FIG. 3 etc.). However, it is also possible to change the first index projection optical system 45 and the second index projection optical system 46. The first index projection optical system 45 includes an infrared light source arranged in a ring around the optical axis L3. The first index projection optical system 45 emits near-infrared light for projecting the alignment index onto the cornea of the subject's eye. The second index projection optical system 46 includes a ring-shaped infrared light source disposed at a position different from the infrared light source of the first index projection optical system 45. (In FIG. 2, for convenience, only a part (cross section) of the ring-shaped infrared light source in the first index projection optical system 45 and the second index projection optical system 46 is illustrated.) The index projection optical system 45 projects an alignment index at infinity onto the cornea of the subject's eye. In addition, the second index projection optical system 46 projects an alignment index at a finite distance onto the cornea of the subject's eye. The alignment light emitted from the second index projection optical system 46 is also used as anterior eye imaging light for imaging the anterior eye of the subject's eye by the anterior eye imaging unit 50. The light sources of the first index projection optical system 45 and the second index projection optical system 46 are not limited to ring-shaped light sources, and may be plural point-shaped light sources or line-shaped light sources.

(Anterior eye photography department)
The anterior segment imaging unit 50 shares the objective lens 14 and the dichroic mirror 29 with the subjective measurement unit 25 and the objective measurement unit 10. The anterior segment imaging unit 50 also includes an imaging lens 51 and a two-dimensional imaging element 52. The two-dimensional imaging element 52 has an imaging surface disposed at a position that is in a substantially conjugate relationship with the anterior segment of the subject's eye. The output from the two-dimensional imaging device 52 is input to the control unit 70. The two-dimensional imaging device 52 captures an anterior eye image of the subject's eye by receiving invisible light (near infrared light in the present embodiment). The anterior segment imaging unit 50 also captures an alignment index image formed on the cornea of the subject's eye by the first index projection optical system 45 and the second index projection optical system 46. The position of the alignment index image is detected by the control unit 70.

  It is also possible to change the configuration of the anterior segment imaging unit 50. For example, in the present embodiment, the anterior segment imaging unit 50 of the left-eye measurement unit 7L captures the anterior segment of the left eye, and the anterior-segment imaging unit 50 of the right-eye measurement unit 7R captures the anterior segment of the right eye The department is photographed. That is, the left eye and the right eye of the subject are photographed by different anterior eye imaging units 50. However, the left eye and the right eye of the subject may be photographed by one anterior segment imaging unit. For example, the left eye and the right eye of the subject may be photographed by the photographing optical system 100 (see FIG. 1) described above.

(Controller unit)
The control unit 70 includes a CPU (processor) 71, a non-volatile memory 72, a RAM, a ROM, and the like. The CPU 71 controls the ophthalmologic apparatus 1. The non-volatile memory 72 is a non-transitory storage medium capable of retaining stored contents even when the supply of power is shut off. For the non-volatile memory 72, for example, at least one of a hard disk drive, a flash ROM, and a removable USB memory may be used. The non-volatile memory 72 stores various data (for example, data of an eye position change graph to be described later, data of an eye position shift amount, and the like) generated by the CPU 71. Further, in the non-volatile memory 72, a control program for controlling the control of the ophthalmologic apparatus 1 is stored. The RAM temporarily stores various information. The ROM stores various programs, initial values, and the like. In the present embodiment, the operation of the ophthalmologic apparatus 1 is controlled by one CPU 71 provided inside the ophthalmologic apparatus 1. However, the control unit that controls the ophthalmologic apparatus 1 may be provided in a device (for example, a PC or the like) different from the ophthalmologic apparatus 1. Also, the operation of the ophthalmologic apparatus 1 may be controlled by a plurality of control units.

(Internal configuration of ophthalmologic apparatus)
The internal configuration of the ophthalmologic apparatus 1 of the present embodiment will be described with reference to FIGS. 3 to 5. FIG. 3 is a schematic configuration view of the inside of the ophthalmologic apparatus 1 of the present embodiment as viewed from the front direction (direction A in FIG. 1). FIG. 4 is a schematic configuration view of the inside of the ophthalmologic apparatus 1 of the present embodiment as viewed from the right side direction (direction B in FIG. 1). FIG. 5 is a schematic configuration view of the inside of the ophthalmologic apparatus 1 of the present embodiment as viewed from above (direction C in FIG. 1). In FIG. 3, for convenience, the illustration of the optical axis showing the reflection of the half mirror 84 (see FIGS. 4 and 5) is omitted. In FIG. 4 and FIG. 5, only the optical axis of the measurement means 7L for left eyes is illustrated for convenience.

  The ophthalmologic apparatus 1 of the present embodiment includes a measuring unit 7 (left-eye measuring unit 7L, right-eye measuring unit 7R), a moving unit 9 (left moving unit 9L, right moving unit 9R), a deflection mirror 81 (left deflection mirror) 81 L, right deflection mirror 81 R), drive unit 82 (left drive unit 82 L, right drive unit 82 R), drive unit 83 (left drive unit 83 L, right drive unit 83 R), half mirror 84, and concave mirror 85. However, the configuration of the ophthalmologic apparatus 1 can also be changed. For example, part of the above configuration may be omitted.

  The left moving unit 9L can move the left-eye measurement unit 7L in the left-right direction (X direction). The right moving unit 9R can move the right-eye measuring unit 7R in the X direction. By moving the left-eye measuring unit 7L and the right-eye measuring unit 7R, the distance between the deflecting mirrors 81L and 81R is changed, and the presenting position of the target light beam in the front-rear direction (Z direction) changes. . Therefore, by moving the left-eye measurement unit 7L and the right-eye measurement unit 7R, an image of the target luminous flux corrected by the correction optical system 60 (see FIG. 2) is formed on the fundus of the subject's eye. So can be adjusted.

  The left deflection mirror 81L is disposed on the optical path between the correction optical system 60 of the right-eye measurement unit 7L and the left eye of the subject. The right deflection mirror 81R is disposed on the optical path between the correction optical system of the right-eye measurement unit 7R and the right eye of the subject. Preferably, the left deflection mirror 81L and the left deflection mirror 81R are disposed at the pupil conjugate position of the subject's eye. The left deflection mirror 81L reflects the light beam emitted from the left-eye measurement unit 7L and guides the light beam to the left-eye EL, and reflects the reflected light reflected by the left-eye EL to the left-eye measurement unit 7L. Guide light. Similarly, the right deflection mirror 81R reflects the light flux emitted from the right-eye measurement unit 7R and guides the light flux to the right eye ER, and reflects the reflected light reflected by the right eye ER to measure the right eye Guide light to the unit 7R. Note that, instead of the deflection mirror 81, another deflection member (for example, at least one of a prism and a lens) may be used.

  The left drive unit 82L drives the left deflection mirror 81L, and the right drive unit 82R drives the right deflection mirror 81R. The drive unit 82 rotates the deflection mirror 81. In detail, the drive unit 82 of the present embodiment can rotate the deflection mirror 81 about a rotation axis extending in the horizontal direction (X direction), and centers the rotation axis extending in the vertical direction (Y direction). The deflection mirror 81 can be rotated as The number of rotation axes of the deflection mirror 81 may be one. Further, each of the left deflection mirror 81L and the right deflection mirror 81R may be provided with a plurality of mirrors having different rotation axes. By rotating the deflecting mirror 81, it is possible to deflect an apparent luminous flux in order to form an image in front of the eye of the subject. As a result, the formation position of the image is optically corrected.

  The left drive unit 83L drives the left deflection mirror 81L, and the right drive unit 83R drives the right deflection mirror 81R. The drive unit 83 can move the deflection mirror 81 in the X direction. By moving the left deflection mirror 81L and the right deflection mirror 81R, the distance between the left deflection mirror 81L and the right deflection mirror 81R changes. For example, the CPU 71 changes the distance between the left deflecting mirror 81L and the right deflecting mirror 81R according to the interpupillary distance of the subject so that the X direction between the optical path for the left eye and the optical path for the right eye The distance at can be adjusted.

  The concave mirror 85 guides the visual standard light flux that has passed through the correction optical system 60 to the subject's eye, and forms an image of the visual standard light flux in front of the subject's eye. In addition, the reflected light emitted from the objective measurement unit 10 and reflected by the subject's eye is reflected by the concave mirror 85 and is guided to the light receiving optical system 10 b of the objective measurement unit 10. In the present embodiment, the concave mirror 85 is shared by the left-eye measurement unit 7L and the right-eye measurement unit 7R. However, the concave mirror disposed in the optical path for the left eye and the concave mirror disposed in the optical path for the right eye may be separately provided. Note that, instead of the concave mirror 85, at least one of optical members such as a lens and a plane mirror may be used. Also, a configuration may be used in which the reflected light of the measurement light by the objective measurement unit 10 is guided to the light receiving optical system 10B without passing through the concave mirror 85.

  Hereinafter, the optical path of the subjective measurement by the subjective measurement unit 25 will be described. The target luminous flux emitted from the measurement unit 7 is reflected by the deflection mirror 81 and travels to the half mirror 84, and is reflected by the half mirror 84 and travels to the concave mirror 85. The target luminous flux reflected by the concave mirror 85 is transmitted through the half mirror 84 and reaches the subject's eye. The concave mirror 85 reflects the target luminous flux used for subjective measurement as a substantially parallel luminous flux. Therefore, in the subject's eye, it appears that the visual target image is present farther than the actual distance from the subject's eye to the display 31. The visual target image is formed on the fundus of the subject's eye based on the spectacle wearing position of the subject's eye (e.g., a position of about 12 mm in front of the corneal apex). The subject responds to the examiner while looking at the target in a state of natural vision. The correction by the correction optical system 60 is performed until the subject can properly view the target, whereby the optical characteristics of the subject's eye are subjectively measured.

  Next, an optical path of objective measurement by the objective measurement unit 10 will be described. The measurement light emitted from the measurement unit 7 is reflected by the deflection mirror 81 and travels to the half mirror 84, and is reflected by the half mirror 84 and travels to the concave mirror 85. The measurement light reflected by the concave mirror 85 passes through the half mirror 84 to reach the subject's eye, and forms an image on the fundus of the subject's eye. At this time, the pupil projected image of the hole portion of the hole mirror 13 (projected light beam on the pupil) is eccentrically rotated by the prism 15. The light of the image formed on the fundus of the subject's eye is reflected and scattered, emitted from the subject's eye, and travels back to the hole mirror 13 in the optical path through which the measurement light has passed. The reflected light is reflected by the hole mirror 13, condensed again by the aperture of the light receiving diaphragm 18, and made into a substantially parallel light beam (in the case of an emmetropic eye) by the collimator lens 19. Thereafter, the reflected light is extracted as a ring-shaped luminous flux by the ring lens 20 and received by the two-dimensional imaging element 22. By analyzing the ring image captured by the two-dimensional imaging element 22, the optical characteristics of the eye to be examined are objectively measured.

(Measurement of eye position)
An example of a method of measuring the eye position (the direction in which the subject's eye points) will be described with reference to FIG. The ophthalmologic apparatus 1 according to the present embodiment can measure eye position of a subject's eye and can generate eye position state information indicating a state of eye position. The ophthalmologic apparatus 1 of the present embodiment can also execute the measurement of the eye position of the subject's eye and the objective measurement of the optical specification of the subject's eye in parallel.

  The ophthalmologic apparatus 1 measures the eye position of the subject's eye based on the anterior segment image 110 (see FIG. 6) captured by the anterior segment imaging unit 50 (see FIG. 2). A ring index image R1, a ring index image R2, and a pupil P appear in the anterior-eye portion image 110 of the right eye shown in FIG. The ring index image R1 appears by the infrared light source of the first index projection optical system 45. The ring index image R2 appears by the infrared light source of the second index projection optical system 46. In the example shown in FIG. 6, the ring index image R2 is located inside the ring index image R1.

  As an example, the CPU 71 of the ophthalmologic apparatus 1 according to the present embodiment performs image processing on the captured anterior eye image 110 to detect the positions of the pupil P and the visual target image (for example, ring index image R2). Do. The detection of the position of the pupil P may be performed, for example, by detecting the rise and fall of the luminance value and detecting the edge position of the pupil P. The same applies to the detection of the position of the visual target image. The CPU 71 detects the pupil center position PC based on the position of the pupil P. The pupil center position PC may be detected, for example, by finding the position of the center of the substantially circular pupil P. Further, the CPU 71 detects the corneal apex position C based on the position of the visual target image. The corneal apex position C may be detected, for example, by finding the position of the center of the ring index image R2. Of course, the corneal apex position C may be detected based on the position of the ring index image R1 or may be detected based on the positions of both the ring index image R1 and the ring index image R2. In addition, even when a plurality of point-like light sources are used instead of the ring-like light source, the corneal apex position C is detected by finding the positions of the centers of the plurality of index images.

  In the present embodiment, the CPU 71 measures the displacement amount ΔX of the pupil center position PC and the corneal apex position C and the direction of the displacement as the eye position of the subject's eye. As the deviation of the direction of the line of sight of the subject's eye with respect to the imaging optical axis of the anterior segment imaging unit 50 increases, the deviation amount ΔX tends to increase. Therefore, the eye position can be appropriately measured by calculating the displacement amount ΔX. Note that the measured eye position may not be an absolute value. However, even in this case, changes in the eye position can be appropriately grasped by continuously measuring the eye position.

  In addition, it is also possible to change the measurement method of an eye position. For example, only one of the displacement amount ΔX and the displacement direction may be measured as the eye position. Also, the eye position may be measured based on only one of the position of the pupil P and the corneal apex position C. The eye position may be measured based on the edge position of the pupil P instead of the pupil center position PC. The eye position may be measured based on other information (eg, information on the distance between the left eye and the right eye). When measuring the eye position taking into consideration the direction of displacement, the direction to be considered may be a two-dimensional direction (upper, lower, left, right) or one-dimensional (for example, the upper, lower, left, right, Or in the oblique direction).

(Measurement of oblique position)
An example of a method of inspecting the posture of a subject will be described with reference to FIGS. 7 and 8. The ophthalmologic apparatus 1 of the present embodiment can perform an oblique examination of a subject. 7 and 8 are diagrams schematically showing the optical axis and the like of the light flux of the fixation target 31K at the time of the oblique inspection, and the reflection of the light flux of the fixation target 31K by the concave mirror 85 is shown in the figure. Absent. Moreover, FIG. 7 and FIG. 8 are schematic diagrams when left eye EL is an examination object eye among left eye EL and right eye ER of a subject.

  First, as shown in FIG. 7, the ophthalmologic apparatus 1 presents the fixation target 31K to both the left eye EL and the right eye ER of the subject. In the state shown in FIG. 7, the line of sight of the left eye EL and the line of sight of the right eye ER both coincide with the optical axis of the light flux of the fixation target 31K, and there is no deviation of the eye position.

  Then, as shown in FIG. 8, the presentation of the fixation target 31K to the left eye EL as the examination target eye is stopped (that is, the presentation of the fixation target 31K to the left eye EL is switched to non-presentation) . In the case where the left eye EL has an external oblique position, the line of sight of the left eye EL faces outward when a sufficient time has elapsed from the presentation switching time of the fixation target 31K. According to the ophthalmologic apparatus 1, the eye position of the eye to be examined (left eye EL) measured before (the state of FIG. 7) the display switching time of the fixation target 31K and after the display switching (the state of FIG. 8) An oblique examination of the eye to be examined is objectively performed based on the measured eye position of the eye to be examined.

  The ophthalmologic apparatus 1 presents the fixation target 31K to the left eye and the right eye so that the fixation target 31K can be seen in the near direction, and then stops presenting the fixation target 31K to the examination target eye. It is also possible to conduct a near-side oblique examination.

  Moreover, in FIG. 7 and FIG. 8, it illustrated about the case where there exists exoclitus in the test object eye. However, it is needless to say that the examination of the inner oblique position, the upper oblique position, the lower oblique position and the like can also be performed objectively by the ophthalmic apparatus 1.

  The ophthalmologic apparatus 1 can also execute eye position examinations other than the eye position examinations shown in FIGS. 7 and 8. For example, the ophthalmologic apparatus 1 may switch the presentation state of the fixation target 31K to the examination target eye (one of the left eye EL and the right eye ER) from non-presentation to presentation. The ophthalmologic apparatus 1 has the eye position of the examination target eye measured before the presentation switching time of the fixation target 31K (that is, while the fixation target 31K is not presented) and after the presentation switching time (that is, solid) Eye position information may be generated based on the eye position of the examination target eye measured after the presentation of the visual target 31K is started. Further, the ophthalmologic apparatus 1 may generate eye position information with the eye on the side opposite to the eye that switches between presentation and non-presentation of the fixation target 31K among the left eye and the right eye as the examination target eye. In the following, the operation of the ophthalmologic apparatus 1 when the eye position examination shown in FIGS. 7 and 8 is performed will be described as an example.

(Display switching method of fixation target)
An example of a method for switching between presentation and non-presentation of the fixation target 31K to the subject's eye will be described. For example, in the example shown in FIG. 8, the visible light blocking member (for example, IR filter etc.) 111 is in front of the subject's eye (in the present embodiment, the presentation window 3 of the housing 2 (see FIG. 1) Between the presentation and non-presentation of the fixation target 31K to the subject's eye. The visible light blocking member 111 transmits anterior eye imaging light (in the present embodiment, near infrared light which is invisible light in the present embodiment) for the anterior eye imaging portion 50 to image the anterior eye, and fixation Block the visible light presenting the marker 31K. In this case, the anterior segment imaging unit 50 can appropriately capture the anterior segment of the subject's eye before and after the presentation switch of the fixation target 31K. Moreover, when stopping presentation of the fixation target 31K, the visible light blocking member 111 is inserted in front of the eye of the subject. Therefore, the possibility that the subject's eye gazes at a part of the ophthalmologic apparatus 1 after the presentation stop is low. Therefore, after the presentation of the fixation target 31K is stopped, the fixation of the subject's eye is released properly.

  The visible light blocking member 111 may be inserted and removed in front of the subject's eye manually by an examiner or the like. In addition, the ophthalmologic apparatus 1 may include an insertion and removal drive unit that inserts and removes the visible light blocking member 111 on the optical path of the fixation target 31 K between the subject's eye and the housing 2. The insertion / removal drive unit may be provided, for example, in the housing 2 or the jaw base 5 or the like. The CPU 71 may switch between presentation and non-presentation of the fixation target 31K to the subject's eye by controlling the drive (for example, a motor or a solenoid) of the insertion / removal drive unit. Also, instead of the visible light blocking member 111, a semitransparent member that transmits only a part of visible light may be used.

  In addition, it is also possible to change the method of switching between presentation and non-presentation of the fixation target 31K. For example, the CPU 71 may switch between presentation and non-presentation of the fixation target 31K by switching between display and deletion of the fixation target 31K on the display 31. Further, the CPU 71 may switch between presentation and non-presentation of the fixation target by driving the target plate provided with the fixation target 31 K by the actuator. In addition, the CPU 71 may stop the presentation of the fixation target 31K by blocking the presented light flux of the fixation target 31K inside the ophthalmologic apparatus. Presentation and non-presentation may be switched by a polarization member provided in the presentation light path of the fixation target 31K.

(Obtaining at the time of presentation switching of fixation target)
In the present embodiment, the CPU 71 can acquire presentation switching time in which presentation and non-presentation of the fixation target to the subject's eye are switched. For example, the CPU 71 may acquire the presentation switching time by receiving an input of an instruction from the user for specifying the presentation switching time. The designation instruction at the time of presentation switching may be input by operating the operation unit (for example, the touch panel 4) or may be input by voice. For example, in the case where the visible light blocking member 111 is manually inserted and removed in front of the eye to switch between presentation and non-presentation of a fixation target, the user may input a designation instruction when the visible light blocking member 111 is inserted and removed in front of the eye Good. In this case, the CPU 71 may acquire the point in time when the instruction is input as the presentation switching time. In addition, the user may input the designation instruction later than the time of presentation switching.

  In addition, the CPU 71 detects a point in time when the intensity of anterior eye imaging light received by the anterior eye imaging unit 50 changes due to insertion and removal of the visible light blocking member 111 by image processing or the like on the anterior eye image 130. The presentation switching time may be acquired. The CPU 71 may detect the point in time at which the visible light blocking member 111 is inserted and removed in front of the eye (that is, at the time of presentation switching) based on the image captured by the imaging optical system 100. In addition, the ophthalmologic apparatus 1 may include a sensor that detects that the visible light blocking member 111 is inserted into or removed from the presenting light path of the fixation target. In this case, the CPU 71 may acquire the presentation switching time based on the detection result by the sensor.

  In addition, when the CPU 71 controls the drive of an actuator (for example, an actuator of the insertion / removal drive unit, or an actuator for driving a target plate, etc.) to switch between presentation and non-presentation of a fixation target, presentation and non-presentation are The point in time at which the actuator is driven to switch may be acquired as the presentation switching time. In addition, when the display and the non-presentation of the fixation target are switched by controlling the display and the deletion of the fixation target on the display 31, the CPU 71 obtains, as the presentation switching time, the time when the display and the deletion of the fixation target are switched. You may

(Data generation of eye position change graph)
The data of the eye position change graph that can be generated by the CPU 71 will be described with reference to FIG. In the present embodiment, the CPU 71 can generate eye position change graph data based on eye position measurement results at a plurality of timings measured based on the anterior segment image 110. The data of the eye position change graph is one of eye position state information indicating the eye position state of the eye to be examined. The CPU 71 changes the eye position change graph illustrated in FIG. 9 based on a plurality of eye position measurement results intermittently measured at a predetermined time interval (eg, every frame of a moving image of the anterior eye segment image 110). Generate data. The control unit that measures the eye position and the control unit that generates data of the eye position change graph based on the measurement result may be different.

  The CPU 71 may cause the display unit (for example, the touch panel 4) to display the eye position change graph. Further, the CPU 71 may output the data of the generated eye position change graph to an external device, or may output the data to a storage unit (for example, a non-volatile memory or the like) for storage. The CPU 71 may cause the display unit to display an eye position change graph in real time during the eye position examination. In addition, the CPU 71 may generate data of the eye position change graph after the examination based on the plurality of anterior eye part images 110 captured continuously during the examination.

  The data of the eye position change graph illustrated in FIG. 9 includes data of a plurality of points 120 in which a plurality of eye position measurement results are plotted at each measurement timing. The data of the eye position change graph illustrated in FIG. 9 also includes the data of the approximate curve 121 generated based on the plurality of plotted points 120. However, the CPU 71 may generate only one of the data of the plurality of points 120 and the data of the approximate curve 121. Also, data of other types of graphs (eg, bar graphs, etc.) may be generated.

  In the present embodiment, the CPU 71 generates eye position change graph data based on the eye position measurement result at the timing before display switching of the fixation target and the eye position measurement result at the timing after the display switching. Do. In other words, the CPU 71 of this embodiment generates data of the eye position change graph at least after the presentation switching time of the fixation target. Therefore, the temporal change of the eye position due to the switching between the presentation of the fixation target and the non-presentation is appropriately grasped by the eye position change graph. In addition, when data of the eye position change graph of the eye to be examined in the oblique position test is generated, the examiner makes a diagnosis of the presence or absence of the oblique position of the eye to be examined more appropriately by the eye position change graph. be able to.

  Note that the CPU 71 may detect the timing at which the eye to be examined blinks by processing the anterior segment image 110 captured by the anterior segment imaging unit 50. The CPU 71 may include, in the data of the eye position change graph, information on the timing at which the examination target eye blinks. The CPU 71 may display the timing at which the examination target eye blinks on the display unit together with the eye position change graph. The position of the eye immediately after the blink is likely to be unstable. Therefore, the examiner can grasp the state regarding the eye position more appropriately by observing the eye position change graph after grasping the timing at which the blink was performed.

(Display of anterior segment image of eye position measurement timing)
The CPU 71 can store data of the anterior segment image 110 used for measuring the eye position in the storage unit. The CPU 71 receives an input of an instruction for specifying the imaging timing of the anterior segment image 110 captured in the past. The CPU 71 can cause the display unit to display the anterior segment image 110 captured at the designated imaging timing. Therefore, the user can easily compare the eye position measurement result at the desired timing with the anterior eye image 110 used for the measurement. The input of the designation instruction of the photographing timing may be performed by the operation of the operation unit, or may be performed by voice or the like. When the eye position change graph is displayed on the display unit, the user may input a designation instruction of photographing timing by specifying a desired timing on the eye position change graph. In this case, the eye position measurement result and the anterior segment image 110 can be compared more easily.

(Calculation of eye position shift amount)
The CPU 71 measures the eye position at the timing before the presentation switching of the fixation target (hereinafter referred to as “timing before switching”) and the eye at the timing after the presentation switching (hereinafter referred to as “timing after switching”) The shift amount of the position measurement result can be generated (calculated) as eye position state information. Therefore, the eye position shift amount resulting from the switching between the presentation and non-presentation of the fixation target is appropriately grasped. FIG. 9 shows an example of the calculated eye position shift amount. The eye position shift amount may be calculated during the eye position examination, or may be calculated after the eye position examination.

(Reference timing)
As shown in FIG. 9, the timing at which the waiting time has elapsed from the time of presentation switching of the fixation target is taken as the reference timing. The CPU 71 according to the present embodiment calculates the eye position shift amount based on the eye position measurement result at the post-switching timing after the reference timing among the post-switching timings. As shown in the eye position change graph illustrated in FIG. 9, the eye position in the presence of the oblique position tends to be stable with the passage of time after gradually changing from the presentation switching time of the fixation target. Therefore, by using the eye position measurement result after the reference timing, the accuracy of the calculated eye position shift amount is improved.

  The length of the waiting time from the presentation switching of the fixation target to the reference timing may be set in advance. In this case, the length of the waiting time is set to a length (for example, “5 seconds” or more) longer than the time required for the eye position of the eye to be examined to be stabilized from the presentation switching time. As a result, the eye position shift amount is calculated based on the eye position in the stable state.

(Specification of reference timing by user)
The CPU 71 can set the reference timing in accordance with the instruction input by the user. Therefore, the user can set the reference timing to a desired timing according to various circumstances (for example, experience, the state of the eye to be examined, etc.). The CPU 71 may cause the user to specify the reference timing by causing the user to specify the length of the standby time from the presentation switching of the fixation target to the reference timing. Further, during the eye position examination, the CPU 71 may set the timing when the instruction is input as the reference timing.

  In addition, the CPU 71 may allow the user to specify the reference timing in a state in which the eye position change graph (see FIG. 9) is displayed on the display unit. In this case, the user can designate the reference timing as the appropriate timing after grasping the state of the change in eye position by the eye position change graph. The CPU 71 may specify the reference timing by causing the user to specify a desired timing on the eye position change graph.

  In addition, when setting the timing designated by the user as a reference | standard timing, the period which prohibits the setting of a reference | standard timing may be provided. For example, during the display switching of the fixation target, during the minimum waiting time required to stabilize the eye position of the eye to be examined (for example, 1 second from the display switching), the reference timing is set. It may be a prohibited period. In this case, the possibility that the eye position shift amount is calculated based on the unstable eye position is reduced.

(Automatic setting of reference timing)
The CPU 71 can also automatically set the reference timing. Hereinafter, a method for automatically setting the reference timing will be exemplified.

  First, a method of setting reference timing based on a plurality of eye position measurement results will be described. The CPU 71 uses the eye position measurement results at a plurality of timings subsequent to the fixation target presentation switching time to stabilize the eye position later than the presentation switching time (hereinafter referred to as “eye position stabilization timing”) Can be detected. The CPU 71 can set the eye position stabilization timing as the reference timing.

  A specific method for detecting eye position stabilization timing from a plurality of eye position measurement results can also be selected as appropriate. For example, the CPU 71 can detect fluctuations in measurement results from eye position measurement results at a plurality of post-switching timings. The CPU 71 can detect the timing at which the detected fluctuation is equal to or less than the threshold as the eye position stabilization timing. For the fluctuation of the measurement result, for example, at least one of the standard deviation of the plurality of measurement results in the unit time, the difference between the maximum value and the minimum value of the plurality of measurement results in the unit time, and the frequency of the fluctuating measurement result It can be adopted. The CPU 71 may output fluctuation information of the eye position measurement result as eye position state information. Further, the CPU 71 can generate data of the approximate curve 121 (see FIG. 9) indicating the relationship between the eye position and the time from the eye position measurement results at a plurality of post-switching timings. The CPU 71 can detect the timing at which the slope of the approximate curve 121 is equal to or less than the threshold as eye position stabilization timing.

  Next, with reference to FIG. 10, a method of setting the reference timing based on the objective measurement result of the optical characteristic of the eye to be examined will be described. In FIG. 10, the eye position change graph and the optical characteristic change graph of the eye to be examined in the same time zone are compared. The optical characteristic change graph is a graph showing the relationship between time and the optical characteristic of the eye to be inspected which is objectively measured by the objective type measurement unit 10 at a plurality of timings. As an example, in FIG. 10, the eye refractive power of the eye to be examined is used as the objectively measured optical characteristic. The data of the optical characteristic change graph illustrated in FIG. 10 includes data of a plurality of points 220 in which measurement results of a plurality of optical characteristics are plotted at each measurement timing. Further, the data of the optical characteristic change graph illustrated in FIG. 10 also includes the data of the approximate curve 221 generated based on the plurality of plotted points 220. However, only one of the data of the plurality of points 220 and the data of the approximate curve 221 may be generated, or data of other types of graphs may be generated. The CPU 71 may output data of the optical characteristic change graph, or may display the optical characteristic change graph on the display unit.

  As shown in FIG. 10, when the eye position of the examination target eye is stable, the optical characteristics of the examination target eye tend to be stable. Therefore, it is possible to detect the timing at which the optical characteristics of the eye to be examined are stabilized as the eye position stabilization timing. The CPU 71 can detect the eye position stabilization timing based on the objective measurement results of the optical characteristics at a plurality of timings after the presentation switching of the fixation target. The CPU 71 can set the detected eye position stabilization timing as a reference timing.

  A specific method for detecting the eye position stabilization timing from the measurement results of the plurality of optical characteristics can also be appropriately selected. For example, the CPU 71 can detect the fluctuation of the measurement result from the measurement results of the optical characteristics at a plurality of post-switching timings. The CPU 71 can detect the timing at which the detected fluctuation is equal to or less than the threshold as the eye position stabilization timing. As the fluctuation of the measurement result of the optical characteristics, at least one of the standard deviation, the difference between the maximum value and the minimum value, and the frequency can be adopted as in the fluctuation of the eye position measurement result. The CPU 71 may output information on fluctuation of the measurement result of the optical characteristic. In addition, the CPU 71 may detect, as the eye position stabilization timing, the timing at which the slope of the approximate curve 221 is equal to or less than the threshold.

  In addition, CPU71 may output the information of the time from the presentation switching time of a fixation target to eye position stabilization timing, when eye position stabilization timing is detected. In this case, the user can more appropriately grasp the state of the eye position of the eye to be examined by referring to the output time.

(Calculation of eye position shift amount based on multiple eye position measurement results)
The CPU 71 can identify an average value of measurement results, an intermediate value between the maximum value and the minimum value, or a mode value with the highest frequency of measurement from eye position measurement results at a plurality of timings after the reference timing. . The CPU 71 can calculate the amount of deviation between the identified value and the eye position measurement result before the presentation switching time of the fixation target. In this case, the eye position shift amount is calculated while the influence of eye position fluctuation is further suppressed.

  The CPU 71 may specify an average value, an intermediate value, or a mode value of a plurality of eye position measurement results also in the eye position measurement results before the time of presentation switching of the fixation target. In this case, the influence of the change in eye position before the presentation switching of the fixation target is also suppressed.

(Calculation of eye position shift amount based on measurement frequency)
The CPU 71 is a first mode value which is the eye position measurement result with the highest frequency measured before the presentation switching time, from the plurality of eye position measurement results during the period before and after the presentation switching time of the fixation target; The second mode value, which is the result of eye position measurement with the highest frequency measured after presentation switching, may be specified. The CPU 71 may calculate the amount of deviation between the first mode and the second mode as the eye position deviation amount.

  FIG. 11 is an example of a histogram showing the measurement frequency for each value of eye position measurement results. For example, when there is an oblique position in the eye to be examined, etc., as shown in FIG. 11, the mode value of the eye position measurement result before the presentation switch time of the fixation target and the eye position after the presentation switching time The mode values of the measurement results appear separately. Further, the eye position during fixation target presentation tends to be smaller than the eye position after the stop of presentation. Therefore, when the eye position examination shown in FIGS. 7 and 8 is performed, the mode having the smaller eye position among the two mode values can be determined as the first mode before the presentation switching time, The mode with the larger eye position can be determined as the second mode after the presentation switching time. The CPU 71 can calculate the eye position shift amount in which the influence of the eye position fluctuation is suppressed by calculating the eye position shift amount between the first mode value and the second mode value. In this case, the CPU 71 can calculate an appropriate eye position shift amount without acquiring the reference timing described above.

  The CPU 71 may create histogram data indicating the measurement frequency for each value of eye position measurement results from the eye position measurement results at a plurality of timings. The CPU 71 may output data of the created histogram. The CPU 71 may also display a histogram on the display unit. When the histogram is displayed on the display unit, the CPU 71 uses two values (values of eye position before display switching of the fixation target and eyes after display switching) used to calculate the eye position shift amount. The value of the order) may be determined based on the input designation instruction. In this case, the user can appropriately designate two values for calculating the eye position shift amount by looking at the histogram.

  As described above, the ophthalmologic apparatus 1 according to the present embodiment is based on the measurement results of the eye position at at least two timings including the timing before the presentation switching of the fixation target and the timing before the presentation switching. And generate eye position information. Therefore, changes in the eye position state associated with switching between presenting and not presenting the fixation target are objectively and appropriately examined.

  The techniques disclosed in the above embodiments are merely examples. Therefore, it is also possible to change at least a part of the technology exemplified in the above embodiment. For example, the data of the eye position change graph generated in the above embodiment is data from before the presentation switching of the fixation target to after the presentation switching. However, the CPU 71 may create eye position change graph data regardless of the switching of the fixation target presentation. Even in this case, the user can appropriately grasp the state regarding the eye position of the eye to be examined by the eye position change graph.

  In the ophthalmologic apparatus 1 of the said embodiment, various measurements are performed in the state in which the front of a test subject's eye was open. That is, in the ophthalmologic apparatus 1 of the said embodiment, the structure of the correction | amendment optical system 60 grade | etc., Is incorporated in the housing | casing 2 arrange | positioned in the position away from the to-be-tested eye. However, at least a part of the techniques exemplified in the above embodiment can be applied to an ophthalmologic apparatus having a configuration different from the configuration of the above embodiment. For example, the ophthalmologic apparatus may incorporate the configuration of the correction optical system 60 or the like in a housing disposed in front of the eye of the subject. In addition, the ophthalmologic apparatus may be an eye refractive power measurement apparatus or the like provided with a configuration for capturing an anterior ocular segment of a subject's eye.

DESCRIPTION OF SYMBOLS 1 Ophthalmic apparatus 7L Measurement part 7R for the left eye Measurement part 10 for the right eye Objective-type measurement part 31 Display 31 K Fixation mark 50 Front eye part photographing part 71
72 Non-Volatile Memory 110 Front Eye Image 111 Visible Light Blocking Member

Claims (12)

An ophthalmologic apparatus for inspecting the visual function of a subject, the ophthalmologic apparatus comprising:
An anterior segment imaging unit configured to capture an anterior segment image of at least one of the left eye and the right eye of the subject;
A fixation target presenting unit which presents a fixation target to at least one of the left eye and the right eye of the subject;
A control unit that controls the operation of the ophthalmologic apparatus;
Equipped with
The control unit
By processing the anterior segment image photographed by the anterior segment photographing unit, at least one eye position of the left eye and the right eye of the subject is measured,
At least two timings including a timing after the presentation switching time when presentation and non-presentation of the fixation target is switched to at least one of the left eye and the right eye of the subject and a timing before the presentation switching time An ophthalmic apparatus comprising: eye position state information indicating a state of an eye position of the eye to be inspected based on a measurement result of the eye position of the eye to be inspected at timing. An ophthalmologic apparatus according to claim 1, wherein
The control unit
An ophthalmologic apparatus, wherein data of an eye position change graph indicating at least a relationship between an eye position of the eye to be examined and time after the presentation switching time is generated as the eye position state information. An ophthalmologic apparatus according to claim 1 or 2,
The control unit
Measurement result of eye position of the examination target eye of at least one before switching timing before the presentation switching time and measurement result of eye position of the examination target eye of at least one after switching timing after the presentation switching time An ophthalmologic apparatus characterized by generating a shift amount of the eye position as the eye position state information. An ophthalmologic apparatus according to claim 3, wherein
The control unit
An ophthalmologic apparatus, wherein the shift amount is generated based on a measurement result of an eye position at at least one post-switching timing after a reference timing which is a timing when a standby time has elapsed from the presentation switching time. The ophthalmologic apparatus according to claim 4,
The control unit
While accepting input of an instruction to specify the reference timing,
An ophthalmologic apparatus, wherein the reference timing is set according to the input instruction. The ophthalmologic apparatus according to claim 4,
The control unit
Based on the measurement results of the eye position of the examination target eye at a plurality of post-switching timings, the timing at which the eye position of the examination target eye is stable after the presentation switching time is detected. An ophthalmologic apparatus characterized by being set as timing. The ophthalmologic apparatus according to claim 4,
Objective measurement unit for objectively measuring the optical characteristics of the eye to be examined by emitting measurement light to the eye to be examined and receiving the reflected light of the measurement light reflected by the eye to be examined And further
The control unit
The timing at which the eye position of the eye to be examined becomes stable after the presentation switching time based on the measurement results of the optical characteristics of the eye to be examined measured by the objective measurement unit at a plurality of post-switching timings An ophthalmologic apparatus, wherein the detected timing is set as the reference timing. An ophthalmologic apparatus according to any one of claims 4 to 7, wherein
The control unit
From the measurement results of the plurality of eye positions measured at the plurality of post-switching timings after the reference timing, the average value of the measurement results, the intermediate value between the maximum value and the minimum value of the measurement results, or the measured frequency is the most An ophthalmologic apparatus characterized by specifying a large number of mode values and calculating the amount of deviation using the specified values. An ophthalmologic apparatus according to claim 3, wherein
The control unit
The first mode with the highest frequency measured before the presentation switching time from the measurement results of the plurality of eye positions at the plurality of pre-switching timings and the measurement results of the plurality of eye positions at the plurality of post-switching timings And identifying a second mode with the highest frequency measured after the presentation switching time,
An ophthalmologic apparatus, wherein a shift amount between the first mode value and the second mode value is calculated as the eye position information. An ophthalmologic apparatus according to any one of the preceding claims, wherein
The control unit
Acquiring the presentation switching time when presentation and non-presentation of the fixation target are switched;
An ophthalmologic apparatus, wherein the eye position state information is generated based on the acquired presentation switching time. An ophthalmologic apparatus according to any one of claims 1 to 10, wherein
The anterior segment imaging unit captures the anterior segment image by receiving invisible light, and
The fixation can be achieved by inserting and removing a visible light blocking member that transmits at least a part of the invisible light received by the anterior segment imaging unit and blocks visible light presenting the fixation target in front of the eye. An ophthalmologic apparatus characterized in that presentation and non-presentation of a mark are switched. An ophthalmologic apparatus used to test the visual function of a subject, comprising:
An anterior segment imaging unit configured to capture an anterior segment image of at least one of the left eye and the right eye of the subject;
A fixation target presenting unit which presents a fixation target to at least one of the left eye and the right eye of the subject;
A control unit that controls the operation of the ophthalmologic apparatus;
Equipped with
The control unit
By processing the anterior segment image photographed by the anterior segment photographing unit, at least one eye position of the left eye and the right eye of the subject is measured at a plurality of timings,
An ophthalmic apparatus, comprising: data of an eye position change graph indicating a relationship between measured eye position and time.

Images